CA2234055C - Gas pressured needle-less injection device - Google Patents
Gas pressured needle-less injection device Download PDFInfo
- Publication number
- CA2234055C CA2234055C CA002234055A CA2234055A CA2234055C CA 2234055 C CA2234055 C CA 2234055C CA 002234055 A CA002234055 A CA 002234055A CA 2234055 A CA2234055 A CA 2234055A CA 2234055 C CA2234055 C CA 2234055C
- Authority
- CA
- Canada
- Prior art keywords
- chamber
- needle
- injector device
- gas
- actuating member
- 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.)
- Expired - Fee Related
Links
Classifications
-
- 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
- A61M5/30—Syringes for injection by jet action, without needle, e.g. for use with replaceable ampoules or carpules
-
- 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
- A61M2005/2006—Having specific accessories
- A61M2005/2013—Having specific accessories triggering of discharging means by contact of injector with patient body
-
- 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
- A61M2005/2073—Automatic syringes, e.g. with automatically actuated piston rod, with automatic needle injection, filling automatically preventing premature release, e.g. by making use of a safety lock
-
- 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
- A61M5/24—Ampoule syringes, i.e. syringes with needle for use in combination with replaceable ampoules or carpules, e.g. automatic
- A61M2005/2418—Ampoule syringes, i.e. syringes with needle for use in combination with replaceable ampoules or carpules, e.g. automatic comprising means for damping shocks on ampoule
-
- 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
- A61M2005/3103—Leak prevention means for distal end of syringes, i.e. syringe end for mounting a needle
- A61M2005/3104—Caps for syringes without needle
-
- 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
- A61M2005/3117—Means preventing contamination of the medicament compartment of a syringe
- A61M2005/3118—Means preventing contamination of the medicament compartment of a syringe via the distal end of a syringe, i.e. syringe end for mounting a needle cannula
-
- 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
- A61M2005/3123—Details having air entrapping or venting means, e.g. purging channels in pistons
-
- 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
- A61M5/315—Pistons; Piston-rods; Guiding, blocking or restricting the movement of the rod or piston; Appliances on the rod for facilitating dosing ; Dosing mechanisms
- A61M5/31511—Piston or piston-rod constructions, e.g. connection of piston with piston-rod
- A61M2005/31516—Piston or piston-rod constructions, e.g. connection of piston with piston-rod reducing dead-space in the syringe barrel after delivery
-
- 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
- A61M5/2046—Media being expelled from injector by gas generation, e.g. explosive charge
-
- 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
- A61M5/28—Syringe ampoules or carpules, i.e. ampoules or carpules provided with a needle
- A61M5/285—Syringe ampoules or carpules, i.e. ampoules or carpules provided with a needle with sealing means to be broken or opened
- A61M5/286—Syringe ampoules or carpules, i.e. ampoules or carpules provided with a needle with sealing means to be broken or opened upon internal pressure increase, e.g. pierced or burst
-
- 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
- A61M5/30—Syringes for injection by jet action, without needle, e.g. for use with replaceable ampoules or carpules
- A61M5/3007—Syringes for injection by jet action, without needle, e.g. for use with replaceable ampoules or carpules with specially designed jet passages at the injector's distal end
-
- 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
- A61M5/3129—Syringe barrels
-
- 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
- A61M5/315—Pistons; Piston-rods; Guiding, blocking or restricting the movement of the rod or piston; Appliances on the rod for facilitating dosing ; Dosing mechanisms
- A61M5/31511—Piston or piston-rod constructions, e.g. connection of piston with piston-rod
-
- 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
- A61M5/315—Pistons; Piston-rods; Guiding, blocking or restricting the movement of the rod or piston; Appliances on the rod for facilitating dosing ; Dosing mechanisms
- A61M5/31525—Dosing
-
- 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
- A61M5/315—Pistons; Piston-rods; Guiding, blocking or restricting the movement of the rod or piston; Appliances on the rod for facilitating dosing ; Dosing mechanisms
- A61M5/31533—Dosing mechanisms, i.e. setting a dose
-
- 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
- A61M5/315—Pistons; Piston-rods; Guiding, blocking or restricting the movement of the rod or piston; Appliances on the rod for facilitating dosing ; Dosing mechanisms
- A61M5/31533—Dosing mechanisms, i.e. setting a dose
- A61M5/31535—Means improving security or handling thereof, e.g. blocking means, means preventing insufficient dosing, means allowing correction of overset dose
Abstract
An improved medication delivery device is a pen sized instrument that is powered by compressed inert gas. The needle-less injector device contains pre-filled and pre-measured medication dosages. The injector device has a pre-filled and self-contained compressed gas for providing pressure to inject the medication into the skin surface without th e use of a needle. The injector device has a pressure sensitive deployment mechanism which insures proper seating of the injector face again st the skin surface before medication delivery is accomplished. The needle-less injector device assures safe use by inexperienced operators (including children) under adverse conditions.
Description
TITT .F
GAS PRESSURED NEEDLE-LESS INJECTION DEVICE AND METHOD
This invention relates to a gas pressured needle-less injection device and method of manufacture, and in particular, embodiments to a single use device.
BACKGROUND OF THE INVENTION
Typically, needle-less medication injections are performed with "permanent gun"
instruments, generally referred to as "jet injectors". These devices use either a compression spring or a compressed inert gas to propel the fluid medication (via a push rod plunger) through a small orifice (an injector nozzle) which rests perpendicular to and against the injection site. The fluid medication is generally accelerated at a high rate to a speed of between about 800 feet per second (fps) and 1,200 fps (approximately 244 and 366 meters per second, respectively). This causes the fluid to pierce through the skin surface without the use of a needle, resulting in the medication being deposited in a flower pattern under the skin surface. This method of medication delivery is referred to as a subcutaneous injection.
Conventional jet injectors are cumbersome and awkward to use. Preparing a typical, reusable jet injector for administering an injection requires several steps.
For example, prior to each injection, the injector nozzle must be sterilized. The operator removes the delivery nozzle from the jet injector and boils the nozzle in water to assure a reasonable degree of sterilization. After the nozzle is cleaned, the user replaces it on the instrument and prepares the instrument for loading the medication which is to be injected into the skin. A concern often associated with the nozzle in these reusable systems is that, due to a relatively small opening (approximately .004" (0.0001 m) or less), the nozzle has a tendency to clog up if the device is left unused for a period of time or if the user does not clean the instrument each time after being used and prior to its reuse.
In addition, loading known jet injectors with medication is a time consuming and delicate operation. First, an adaptor which contains a needle is placed through the rubber AMENDED SHEET, a septum of the medication vial. The nozzle of the jet injector is then mated to the needle adaptor in the medication vial. The operator then proceeds to draw up medication into the delivery chamber of the jet injector. This operation may be repeated several times, until the trapped air in the delivery chamber is removed. When this pre-injection operation is complete, the operator selects an injection site and administers the injection.
However, a used and worn delivery orifice can slow down the delivery speed of the injected fluid, which results in inadequate penetration and causes bruising of the skin at the injection site. In addition, the improper use of jet injectors creates bruising (subdermal hematoma) when the nozzle is not firmly pressed against the injection site.
Bruising also may occur if the nozzle opening (orifice) is partially clogged or worn out.
Conventional jet injectors are also somewhat dangerous to use, since they can be discharged without being placed against the skin surface. With a fluid delivery speed of about 800 fps (243.8 m/s) or higher, a jet injector could injure a person's eye at a distance of up to 15 feet (4.57 m). It should also be noted that jet injectors which have not been properly sterilized are notorious for creating infections at the injection site. In addition, if a jet injector is not positioned properly against the injection site, the injection can be short of the measured dosage, thereby creating wetting on the skin surface, which Leads to additional problems associated with improper dosage amounts.
Moreover, it should also be noted that compression spring propelled jet injectors do not offer linear delivery speeds (constant speed of the fluid being injected).
In addition to this problem, spring propelled jet injectors with weak (e.g., deteriorated) springs often slow the fluid delivery speed down while the fluid is being administered into the skin which can result in improper fluid penetration. Reduced speed of the fluid can cause improper dosing and bruising at the injection site (referred to as subdermal hematoma).
WO-A-95/03844 and US-A-5,009,637 are representative of devices known in the art.
GAS PRESSURED NEEDLE-LESS INJECTION DEVICE AND METHOD
This invention relates to a gas pressured needle-less injection device and method of manufacture, and in particular, embodiments to a single use device.
BACKGROUND OF THE INVENTION
Typically, needle-less medication injections are performed with "permanent gun"
instruments, generally referred to as "jet injectors". These devices use either a compression spring or a compressed inert gas to propel the fluid medication (via a push rod plunger) through a small orifice (an injector nozzle) which rests perpendicular to and against the injection site. The fluid medication is generally accelerated at a high rate to a speed of between about 800 feet per second (fps) and 1,200 fps (approximately 244 and 366 meters per second, respectively). This causes the fluid to pierce through the skin surface without the use of a needle, resulting in the medication being deposited in a flower pattern under the skin surface. This method of medication delivery is referred to as a subcutaneous injection.
Conventional jet injectors are cumbersome and awkward to use. Preparing a typical, reusable jet injector for administering an injection requires several steps.
For example, prior to each injection, the injector nozzle must be sterilized. The operator removes the delivery nozzle from the jet injector and boils the nozzle in water to assure a reasonable degree of sterilization. After the nozzle is cleaned, the user replaces it on the instrument and prepares the instrument for loading the medication which is to be injected into the skin. A concern often associated with the nozzle in these reusable systems is that, due to a relatively small opening (approximately .004" (0.0001 m) or less), the nozzle has a tendency to clog up if the device is left unused for a period of time or if the user does not clean the instrument each time after being used and prior to its reuse.
In addition, loading known jet injectors with medication is a time consuming and delicate operation. First, an adaptor which contains a needle is placed through the rubber AMENDED SHEET, a septum of the medication vial. The nozzle of the jet injector is then mated to the needle adaptor in the medication vial. The operator then proceeds to draw up medication into the delivery chamber of the jet injector. This operation may be repeated several times, until the trapped air in the delivery chamber is removed. When this pre-injection operation is complete, the operator selects an injection site and administers the injection.
However, a used and worn delivery orifice can slow down the delivery speed of the injected fluid, which results in inadequate penetration and causes bruising of the skin at the injection site. In addition, the improper use of jet injectors creates bruising (subdermal hematoma) when the nozzle is not firmly pressed against the injection site.
Bruising also may occur if the nozzle opening (orifice) is partially clogged or worn out.
Conventional jet injectors are also somewhat dangerous to use, since they can be discharged without being placed against the skin surface. With a fluid delivery speed of about 800 fps (243.8 m/s) or higher, a jet injector could injure a person's eye at a distance of up to 15 feet (4.57 m). It should also be noted that jet injectors which have not been properly sterilized are notorious for creating infections at the injection site. In addition, if a jet injector is not positioned properly against the injection site, the injection can be short of the measured dosage, thereby creating wetting on the skin surface, which Leads to additional problems associated with improper dosage amounts.
Moreover, it should also be noted that compression spring propelled jet injectors do not offer linear delivery speeds (constant speed of the fluid being injected).
In addition to this problem, spring propelled jet injectors with weak (e.g., deteriorated) springs often slow the fluid delivery speed down while the fluid is being administered into the skin which can result in improper fluid penetration. Reduced speed of the fluid can cause improper dosing and bruising at the injection site (referred to as subdermal hematoma).
WO-A-95/03844 and US-A-5,009,637 are representative of devices known in the art.
AMENDED SHEEP
WO 97113537 PCT/i1S96/16172 It is an object of an embodiment of the present invention to provide an improved disposable jet injector with simplified operating and safety features, that obviates for practical purposes, the above-mentioned limitations.
According to an embodiment of the present invention, a needle-less injector suitable for injecting liquid medication through a skin surface of a patient include a housing, a driver and a trigger. The housing contains the liquid medication to be injected into the patient. The driver forces the medication out of the housing at a sufficient speed to pierce the skin surface of the patient. The resistance sensitive trigger is coupled to the driver and is used to activate the driver to force the liquid medication out of the housing. The resistance sensitive trigger is activated upon application of a predetermined amount of pressure to the resistance sensitive trigger that is opposed by a predetermined amount of resistance from the skin surface of the patient. The predetermined amount of resistance results from the housing having contact with the skin surface of the patient, and when this predetermined amount of _ resistance is reached the liquid medication is forced out of the housing by the driver to pierce the skin surface of the patient.
In further embodiments, the housing of the needle-less injector includes a face that is adapted to align the housing to produce the predetermined amount of resistance to allow for activation of the resistance sensitive trigger. Also, the resistance sensitive trigger is preferably coupled to the housing to permit axial movement of the resistance sensitive trigger along the housing. However, the fit tolerances between the housing and the resistance sensitive trigger are selected to permit activation of the resistance sensitive trigger when the housing is aligned between 0 and 10 degrees off an axis perpendicular to the skin surface of the patient. In addition, the resistance sensitive trigger is preferably positioned to be between the skin surface of the patient and an activating appendage (such as an hand, arm or the like) of a user when activating the driver the force the medication out from the housing.
In particular embodiments, the resistance sensitive trigger includes a resistance element that activates at a lower amount of pressure than the predetermined amount of resistance by the skin surface of the patient. For example, the resistance sensitive trigger includes a cap that is slidably attached to the housing and the resistance element includes a spring coupled between the housing and the cap. Thus, upon application of the predetermined amount of pressure to the cap of the resistance sensitive trigger, the spring r compresses when the opposing resistance from the skin surface of the patient reaches the predetermined amount of resistance to activate the driver to force the liquid medication out of the housing to pierce the skin surface of the patient.
According to further embodiments of the present invention, a compressed gas activated needle-less injector device is suitable for injecting liquid medication through the skin surface. The housing of the needle-less injector includes a main body portion, a valve and a chamber housing portion. The main body portion includes a first gas chamber, a passageway and a second gas chamber which is in gaseous communication with the first gas chamber through the passageway. The first gas chamber contains a pre-filled compressed gas, such as inert gas, that exits through the passageway. The second gas chamber partially contains the driver. The pressure of the compressed gas is sufficiently high to accelerate the - liquid medication at a speed sufficient to pierce through the skin surface.
The valve is detachably mounted to block the passageway to prevent the flow of the compressed gas from the first gas chamber until needed. The valve is positioned in between the first gas chamber and the second gas chamber. The chamber housing portion is securely coupled to the main body portion and includes a liquid chamber and an orifice. In preferred embodiments, the liquid chamber holds the pre-filled and pre-measured liquid medication and is in fluid communication with the driver. The driver can be formed by a piston disposed and movable within the liquid chamber, and a plunger disposed and movable within the liquid chamber along with the piston to force the liquid medication out from the liquid chamber through the orifice. The orifice is formed in one end of the chamber housing portion and is in fluid communication with the liquid chamber. In operation, the compressed gas, when released from the first gas chamber, pushes the liquid forcing assembly, which in turn pushes the liquid medication out through the orifice to pierce the skin surface of the user.
In the embodiment discussed above, the piston has a head which is disposed within <
the second gas chamber. The head creates an air and fluid tight seal so that the compressed gas released from the first gas chamber is trapped in the second gas chamber.
In a further embodiment, the injector device is equipped with a lever for breaking the valve. In particular embodiments, the lever is slidably mounted through a side wall of the main body adjacent to the valve so that when one end of the lever is pushed in, the other end of the lever breaks off the valve, thus releasing the compressed gas into the second gas J
chamber. The resistance sensitive trigger may include an incline ramp surface that pushes the lever inward when the resistance sensitive trigger is depressed. In preferred embodiments, a coil spring is positioned between the resistance sensitive trigger and the main body portion to bias the resistance sensitive trigger in an un-depressed state. A
retainer, such as a retainer ring, may be used to couple the resistance sensitive trigger to the main body portion, and a protective cover, such as a screw-on cap may be used to cover the orifice to maintain sterility of the injection device.
Other features and advantages of the invention will become apparent from the following detailed description, taken in conjunction with the accompanying drawings which _ illustrate, by way of example, various features of embodiments of the invention.
BRIEF DESCRIPTION OF THE DRAWINGS
A detailed description of embodiments of the invention will be made with reference to the accompanying drawings, wherein like numerals designate corresponding parts in the several figures.
FIG. 1 is a cross-sectional diagram of an injector device according to an embodiment of the invention;
FIG. 2 is an exploded view of an actuating member according to an embodiment of the invention;
FIG. 3 is an external side view of an injector device;
FIG. 4 is an external front view of an injector device;
FIG. 5 is an external rear view of an injector device;
FIG. 6 is an external view of an injector device with a safety cap.
DETAILED DESGiZTPTION OF THE P FFFRRFT~ FMRnr~I~NTc As shown in the drawings for purposes of illustration, the invention is embodied in a needle-less injector. In preferred embodiments of the present invention, the a gas powered needle-lee injector device that is pre-loaded with medication and is adapted for a single use.
Preferably, the needle-less injector is for use with human beings. However, it will be Y
recognized that further embodiments of the invention may be used on animals or in other applications requiring needle-less injection, such as passing injectable substances through a porus membrane or the like. In addition, the needle-less injector may uses springs, pyrotechnic charges or the like instead of gas power as the injection delivering force.
As shown in the drawings, a needle-less injection device according to an embodiment of the invention is embodied in a pen sized device. The needle-less injector device 10 according to an embodiment of the invention is useful for hypodermic injection of medication without piercing the skin (non-invasive) with a needle and represents an improvement over known devices. The device 10 may be used as a single dose disposable - injector to deliver a dosage of fluid medication. The preferred embodiment ensures precise delivery through an orifice with the diameter of approximately .0032"
(approximately 0.08 mm). However, larger or smaller diameters may be used, as long as accurate penetration of the skin and delivery of the medication can be maintained. The fluid is linearly accelerated via pneumatic propulsion. Safety is maintained and inadvertent activation of the injection device 10 is avoided via a pressure (e.g., resistance) sensitive triggering feature which allows for proper tensioning of the nozzle and orifice at the injection site prior to automatic medication deployment. For example, activation of the injector device 10 will not occur until the injector is properly positioned to provide the required resistance from the skin surface of the patient to allow for sufficient tension and pressure to be applied to a trigger of the injector device 10 to activate it to deliver the dosage of medication.
Improper positioning resulting in insufficient resistance by the skin surface of the patient will prevent the injector device from being inadvertently activated. For example, tight tolerances between a trigger cap and a housing will prevent the cap from sliding along the housing to trigger the device 10, if the device 10 is more than 10 degrees off of an axis perpendicular to the skin surface of the patient.
The device utilizes prepackaging and precisely measured dosages for a variety of medical applications. However, alternative embodiments may be loaded prior to injection.
- The injector device 10 can be manufactured in various custom sizes for precise medication delivery over a wide range of medication types and dosage amounts. Preferred embodiments allow for a single injection in amounts that range from about 1/20th of one cubic centimeter(cc) to 1.0 cc. The type of injector device 10 is typically used on human patients.
However, in alternative embodiments, a larger injector device with larger medication capacity may be constructed and used on animals, such as livestock or the like.
FIG. 1 shows a needle-less injector device 10 according to an embodiment of the invention. The injector device 10 has a main body 12, a chamber housing 40, a cap 60, a piston 50, an actuating member 20, and a first gas chamber I 8. The main body 12 includes a first body portion 13 integrally connected to a second body portion 19 (main body 12, first body portion 13, and second body portion 19 may be a single unit in design and manufacturing). In the preferred embodiment of the device, the second body portion 19 has a slightly larger diameter than that of the first body portion 13. A flange 27 is formed due to a larger diameter of the second body portion 19. The first body portion 13 and the second body portion 19 each has an elongated cylindrical shape. However, in alternative embodiments, other shapes such as rectangular, triangular or the like may be used. The main body 12 also has an elongated cavity 17 centrally disposed along the length of the first body portion 13 and partially along the length of the second body portion 19. The elongated cavity 17 forms an opening which is located on the end of the main body 12, opposite of the second body portion 19. The elongated cavity 17 has a cylindrical shape with substantially the same diameter. However, in alternative embodiments, other shapes such as rectangular, triangular or the like may be used. The diameter of the elongated cavity 17 gradually tapers off as the elongated cavity 17 nears the second body portion 19. The smaller diameter portions of the elongated cavity 17 limits the backward movement of the piston 50 and tends to increase the rate of acceleration when the jet injection device 10 is first activated.
The second body portion 19 includes a lever passageway 74 and the first gas chamber I 8 for storing compressed inert gas, such as carbon dioxide. However, alternative embodiments may use other gases or a gas/liquid combination. The elongated cavity 17 (i.e., containing a second gas chamber 14) and the first gas chamber 18 are coupled together to provide gaseous communication with each other through a passageway 30. The first gas chamber 18 of the second body portion 19 has an opening on the opposite end of the passageway 30, through which compressed gas is pre-filled into the first gas chamber 18. A
retention groove 28 ( preferably ring shaped) is formed around the inner diameter of the first gas chamber I 8 near the end of the large opening in the first gas chamber. A
chamber plug 26 is disposed within the opening of the first gas chamber 18 to seal in the compressed inert I 0 gas, once the gas has been loaded. The chamber plug 26 forms an air tight seal in the first gas chamber I 8 by engaging the retention groove 28. The retention groove 28 also prevents the chamber plug 26 from detaching itself from the second body portion 19 due to the presence of compressed gas in the first gas chamber 18. The chamber plug 26 is configured and sized to firmly fit into the opening of the first gas chamber 18. In alternative embodiments, instead of the retention groove 28, the inner surface of the first gas chamber may be threaded so that the chamber plug 26 (with corresponding outer threads) may be screwed into the first gas chamber 18. Alternatively, the first gas chamber 18 may be a sealed compartment in which compressed gas is injected through a valve. A seal may be obtained by using an adhesive or other suitable materials. The chamber plug 26 may be made of any suitable rigid materials, such as plastic, rubber, ceramic, metal, composites and the like. Although the main body 12 may be made of plastic by, such process as an injection molding, other suitable materials, such as ceramic, glass, metal, composites or the like, may be used. In addition, the first body portion 13 and the second body portion 19 may be formed together as one injection mold or may be formed from separate portions coupled together by adhesives, welding, snap fits or the like. In preferred embodiments, the chamber plug 26 would be plastic welded, glued or otherwise secured in the first gas chamber 18 immediately after the first gas chamber is filled with gas.
Inside the elongated cavity 17, a release tab 16 (or valve) is attached to the wall to block of~'and seal the passageway 30. In its normal position, the release tab 16 blocks the gas flow from the first gas chamber 18 into the elongated cavity 17. When the release tab 16 is detached or broken off from its original position, the compressed gas from the first gas chamber 18 is released into the elongated cavity 17. More specifically, the compressed gas is released into a second gas chamber I 4, which is a part of the elongated cavity 17. The release tab 16 is preferably sufficiently large to fully cover the opening in the passageway 30, thus preventing any gas leak. In the preferred embodiment, the release tab 16 may be molded with the main body 12. Alternatively, the release tab 16 may be attached to the wall by any suitable process, such as using an adhesive, welding or the like. The release tab 16 is preferably detached or broken off by applying force on its side, but it should be attached firmly enough to withstand the pressure exerted by the compressed air in the first gas chamber I 8 or a shock from a drop. In addition, the release tab 16 should resist being sheared off until the injector device 10 is placed in contact with the skin of a patient and sufficient resistance is encountered to permit the injector device 10 to be activated by applying sufficient pressure to shear off the release tab 16.
- The lever passageway 74 is typically formed on the side wall of the main body 12 and extends from the outer to the inner surface of the second body portion 19 at a slightly slanted angle. However, other configurations may be used. The lever passageway 74 is adapted and configured to hold a lever 70 which protrudes through the lever passageway 74.
In the preferred embodiment, the lever 70 is a cylindrical rod with a rounded end 72. The rounded end 72 protrudes out of the second body portion 19. The lever 70 has preferably the sufficiently same cross-section and diameter as the lever passageway 74 to firmly fit inside the passageway 74 to provide a sufficiently tight air and fluid seal to not hinder with the effective performance of the injection device 10. However, there may be some clearance between the lever 70 and the passageway 74 to bleed-out excess gas pressure over a time period once the injector device 10 has been used. In an alternative embodiment, there may be a plurality of levers 70 disposed through a plurality of lever passageways 74 to ensure the removal of a release tab 16. For example, the main body 12 may accommodate two levers at a 90 degree angle to each other so that the combined force of those levers ensure proper detachment of the release tab 16. In addition, the lever 70 and the passageway 74 may be formed of a rectangular rod shape or other suitable shapes. The lever 70 may be made of resilient plastic or other suitable materials.
The chamber housing 40 includes an elongated tubular body 43, a neck portion and a liquid chamber 41 for storing and holding, for example, liquid medication (not shown).
The chamber housing 40 has an orifice 42 (or nozzle) at one end and has an opening configured to receive the piston 50 at the other end. The orifice 42 is centrally positioned on an injector face 49. The injector face 49 has a flat surface, except that the center region around the orifice 42 is raised slightly. The raised surface around the orifice 42 provides firm contact against a receiving surface, such as the skin surface (not shown). This helps to insure that the injector is properly positioned and will not be activated until sufficient pressure is applied to the injector device 10.
The outer diameter of the neck portion 45 is smaller than the outer diameter of the elongated tubular body 43 which forms a shoulder portion 47 where the two parts join together. The shoulder portion 47 rests on the surface of the opening formed by the elongated cavity 17 of the main body 12. However, the outer diameter of the neck portion 45 is substantially the same as the inner diameter of the elongated cavity 17 of the main body 12 so that the neck portion 45 firmly fits inside the elongated cavity 17. To firmly engage the neck portion 45 of the chamber housing 40 with the elongated cavity 17 of the main body, the middle section of the neck portion 45 may have a slightly larger outer diameter that fits into a groove 15 formed inside the elongated cavity 17. Once coupled together, the chamber housing 40 cannot be released from the main body 12, unless extreme force is applied. In alternative embodiments, the raised outer diameter of the neck portion is altered to form threads on the outer diameter of the neck portion 45 and matching threads are formed inside the elongated cavity 17 to screw-in the chamber housing 40. This provides the advantage of being able to assemble the device 10 when needed or just prior to giving an injection. This assembly option allows the user to select a variety of different medications or dosages while minimizing the number of complete injectors 10 that must be carried or stocked. It would also facilitate manufacture of the device 10 since the injector 10 and the chamber housing 40 , may be manufactured at different times. Further, the main body 12 and the chamber housing 40 may be attached and sealed together by any suitable method, such as adhesives, welding or the like. A ring joint 48, in the form of a plastic weld fillet, is also used to further reinforce the attachment of the chamber housing 40 to the main body 12. In the preferred embodiment, the ring joint 48 abuts against the shoulder portion 47 and the opening surface of the elongated cavity 17. The ring joint 48 provides additional strength to securely hold the chamber housing 40 in the main body 12. Although not shown in the drawings, an O-ring may be placed between the shoulder portion 47 of the chamber housing 40 and the opening surface of the elongated cavity 17 to provide an additional air and fluid tight seal.
For easy measuring and observation of the amount of medication in the liquid chamber 41, the elongated tubular body 43 includes graduations so that the user can determine the amount of medication contained in the injector device 10. The chamber housing 40 can be formed of glass or other suitable materials, such as plastic, ceramic, polycarbonate or the Like. In the preferred embodiment, the chamber housing 40 is transparent so that the liquid medication and the various moving parts in the liquid chamber 4I can be visually examined. Also, the chamber housing 40 is disposable, however the chamber housing may be recycled, if desired.
A cap 60 may be mounted on the end of the chamber housing 40 to cover the orifice 42. The cap 60 provides and maintains sterility of the injection device 10 and prevents an accidental discharge of the liquid medication disposed inside the liquid chamber 41 from shock, evaporation or seepage. Threads 44 for mounting the cap 60 are on the outer surface of the end portion of the chamber housing 40. The cap 60 has matching threads 62 on the inner surface so that the cap 60 can be screwed-on at the end portion of the chamber housing 40. Once screwed-on, the cap 60 provides an air and fluid tight seal around the orifice to prevent any foreign material from being introduced into the liquid chamber 41.
In alternative embodiments, the cap 60 and the end portion of the chamber housing 40 can be configured so that the cap 60 is snapped-on instead of screwed-on. The cap 60 may be made of any suitably rigid material, such as plastic polymers, rubber, ceramic or the like.
The piston 50 has an elongated cylindrical body S I with an indented front surface 52 at one end and a head 54 at the opposite end. The head 54 includes a rear surface 55, which is preferably concave. In alternative embodiments, the front and rear surfaces may be flat, or have other suitable shapes. The elongated cylindrical body 51 of the piston 50 is disposed inside the liquid chamber 41 for sliding movement along its length. In preferred embodiments the elongated cylindrical body 51 has substantially the same outer diameter as the diameter of the liquid chamber 41 to provide free sliding movement along the length of the liquid chamber 41. Due to an air and fluid tight seal around a plunger 56, the air and fluid tight seal around the piston 50 may not be necessary. The head 54 of the piston 50 has substantially the same outer diameter as the inner diameter of the elongated cavity 17 to form an air and fluid tight seal with a minimal friction between the head 54 and the walls of the elongated cavity 17. The space defined between the head 54 and the back wall of the elongated cavity 17 is the second gas chamber 14. The head 54 is disposed inside the elongated cavity 17 so that the compressed gas introduced in the second gas chamber 14 expands the head 54 against the wall surface of elongated cavity 17, providing an additional seal, so that the compressed gas introduced into the second gas chamber 14 pushes the piston 50 forward.
Where the lower portion 82 of the head 54 makes contact with the neck portion 45 of the chamber housing 40, the shapes of both portions may be configured to match each other.
In the preferred embodiment, the end surface 80 of the neck portion 45 forms a concave surface while the lower portion 82 of the head 54 forms a convex surface. The matching shapes assist in delivering substantially all of the medication to the injection site. However, in alternative embodiments, other suitable shapes, such as a flat surface, may be used, and the piston 50 may be made of any suitable material such as plastic, glass, ceramic, metal, composites or the like.
Also disposed inside the liquid chamber 41 is a plunger 56. The plunger 56 has an outer diameter which is substantially the same as the inner diameter of the liquid chamber 41 to form an air and fluid tight seal. The plunger 56 is disposed between the piston 50 and the orifice 42. The medication is situated in front of the plunger 56 (i.e., between the orifice 42 and the plunger 56) so that the forward movement of the plunger 56 forces the liquid , medication toward the orifice 42. The front surface of the plunger 56 may be configured to match the opening defined by an orifice guide 46. In preferred embodiments, the front surface of the plunger 56 has a convex surface to match the concave shape of the orifice guide 46, whose vertex is the orifice 42. The shape of the orifice guide 46 focuses and increases the speed of liquid medication as it exits the orifice 42. The matching shapes of the orifice guide 46 and the plunger 56 tend to minimize the waste of medication, since most of the medication is forced out through the orifice 42. The shape of the rear surface of the plunger 56 matches the front surface 52 of the piston 50. The similarly shaped configuration provides for an even distribution of the pressure on the rear of the plunger 56 when the piston 50 moves forward. This tends to minimize jams or distortion as the plunger 56 is driven forward. The plunger 56 is generally made of rubber or other suitable materials, such as plastic, composites or the like. In alternative embodiments, the plunger 56 and the piston 50 formed as and integrated piece either by attaching the plunger 56 to the piston 50 or by molding the piston assembly to include the plunger 56.
A resistance sensitive trigger includes an actuating member 20 that is an elongated tubular member that slides over the second body portion 19 of the main body 12. The actuating member 20 has a trigger portion 22, a raised rail 76 (see FIG. 2), and a retainer slot 25. The actuating member 20 is enclosed at one end and has an opening at the other end. On the inner surface of the enclosed end, there is a spring surface 23 for holding or mounting a coil spring 24. The resistance sensitive trigger also includes a coil spring 24 that is positioned between a spring surface 23 and the chamber plug 26 and provides a resilient bias toward the rear end. The proper use of the injection device 10 requires that the injector device 10 be positioned substantially perpendicular to the skin surface before the medication is injected into the injection site. Therefore, the tension strength of the coil spring 24 should be sufficiently strong to prevent accidental triggering when the injection device 10 is not properly positioned. Typically, a minimum applied pressure of 2.2 lbs/in2 ( 1.0 kg/2.5 cmz) is required to discharge the injector. However, slight lower or higher minimums may be required depending on the skin of the patient or where the injection is to be administered. In alternative embodiments, alternate resistance elements may be used instead of the coil spring 24, such as deformable rubber or plastic, strain gauges or the like.
In the front opening of the actuating member 20, there is a retainer slot 25 for mounting a retainer 75. The retainer slot 25 is formed around the inner circumference of the actuating member 20, extending from one side of the raised rail 76 to the other side. The retainer 75, which is in a form of a thin circular rod, is mounted into the retainer slot 25. The circumferential length of the retainer 75 is substantially equal to that of the retainer slot 25.
When the actuating member 20 is installed onto the second body portion 19, the retainer 75 generally rests against the flange 27. This prevents the actuating member 20 from detaching itself from the second body portion 19 due to rearward force exerted by the coil spring 24.
The retainer 75 may be made of plastic or other suitable materials such as metal or the like.
In alternative embodiments, the retainer 75 and the actuating member 20 may be formed as one integral member by molding process or other suitable processes. The actuating member is typically made of plastic or other suitably rigid and resilient materials, such as glass, composite, ceramic or metal. The trigger portion 22 is on the outer end surface of the actuating member 20. It preferably forms a concave surface and is coated with a textured 15 material to prevent depressing force, such as from a thumb, from slipping.
FIG. 2 shows an exploded view of the actuating member 20 of the resistance sensitive trigger. As shown in FIG. 2, the raised rail 76 extends along the length of the outer surface of the actuating member 20. A conduit 78 is formed along the length of the raised rail 76. The cross-sectional shape and dimension of the conduit is configured to 20 accommodate the protruding portion of the lever 70. The raised rail 76 has a thickness which varies along its length. The thickness of the raised rail 76 is thinner near the opening of the actuating member 20. Toward the rear portion of the actuating member 20 where a lever 70 is situated, a gradually inclined region 21 is formed on the inner surface of the raised rail 76.
When the actuating member 20 is not depressed, the lever 70 rests on the flat thinner inner surface of the raised rail 76. This is the normal state of the injection device 10 prior to injection. When the actuating member 20 is depressed, the actuating member 20 moves forward, and the inclined region 21 forces the lever 70 toward the center of the second body portion 19. The inward movement of the lever tears (or breaks off) the release tab 16 and , consequently releases the compressed gas in the first gas chamber 18. The raised rail 76 can be formed as integral part of the actuating member by a molding process or other suitable processes.
As shown in Figs. 1, 2 and 4, the second body portion 19 includes three splines 100 and the actuating member 20 includes corresponding three spline slots 102 adapted to slidably receive the splines 100 of the second body portion 19. The splines 100 and spline slots 102 are provided to assist the actuating member 20 to slide along the second body portion as the actuating member 20 is depressed to deliver an injection. The splines 100 and spline slots 102 substantially prevent the actuator member 20 from rotating about the second body portion 19 to avoid jamming of the actuating member 20 during an injection. The splines 100 and spline slots 102 also prevent rotational movement of the actuating member about the second body portion 19 when the cap 60 is removed or threaded onto the chamber housing 40. This limits the amount of torsional stress placed on the lever 70 in the passageway 74 during an injection or when removing or threading the cap 60 onto the chamber housing 40. In alternative embodiments, a different number of splines and spline 15 slots may be used. Also, if the lever 70 is sufficiently strong enough the splines and spline slots may be eliminated. In further alternatives, the splines 100 and/or spline slots 102 may be coated with a lubricant or formed from materials with low frictional coefficients to facilitate sliding movement of the actuating member 20 along the second body portion 19. In preferred embodiments, the splines 100 and splines 102 have a rectangular cross-section.
20 However, in alternative embodiments, the splines and spline slots may have other cross-sections, such as triangular, saw tooth, dove tail or the like, to resist rotational movement of the actuating member 20 about the second body portion 19.
The operation of the needle-less injector device according to the preferred embodiment will now be discussed. Initially at the manufacturing facility, the injection device is pre-filled with medication in the liquid chamber 41 and is pre-filled with compressed gas in the first gas chamber 18. The user (or an operator) unscrews (or unsnaps) the cap 60 from the main body 12, thus revealing the orifice 42 of the injector device 10.
The user then positions the injector device 10 perpendicularly against the skin surface to provide firm and secure contact of the orifice 42 against the skin surface.
The injector device requires the device 10 to be properly oriented and in contact with the skin of the patient, since the injector device 10 is designed so that it cannot be activated or discharged without ' the device 10 being placed against the skin surface. Otherwise,. with a fluid delivery speed of about 800 fps (243.8 m/s) or higher, a jet injector could injure a person's eye or other part of 5 the body. In addition, if the jet injector were not positioned properly against the injection site, and the injection device were activated, the dosage can be short of the measured dosage, thereby creating wetting on the skin surface, which leads to additional problems associated with improper dosage amounts.
As the trigger portion 22 of the actuating member 20 is depressed, the skin surface of 10 the patient resists the pressure being applied to the actuating member 20 of the resistance senitive trigger and the coil spring 24 is compressed between the chamber plug 26 and the spring surface 23. Sufficient pressure (generally a minimum of 2.2 Ibs/in' ( 1.0 kg/2.5 cmZ)) must be applied at the trigger portion 22 to overcome the tension of the coil spring 24.
Concurrently, as the inclined region 21 pushes against the lever 70, the lever 70 is pushed inward toward the center axis of the main body 12. As the actuating member 20 is pressed further against the skin surface, the lever 70 pushes against the side of the release tab 16, tearing (or breaking off) the release tab 16. This exposes the opening of the passageway 30, and the compressed gas stored in the first gas chamber 18 is released into second gas chamber 14. When sufficient pressure is built up inside the second gas chamber 14, the piston 50 is pushed forward so that it slides forward in the liquid chamber 41. The seal around the head 54 of the piston 50 substantially prevents any gas from leaking into the other parts of the elongated cavity. The forward movement of the piston 50 causes the front surface 52 of the piston 50 to make contact with the rear surface of the plunger 56, to move the plunger 56 forward. As the plunger 56 moves forward, the liquid medication exits from the orifice 42 at a high speed and penetrates the skin surface at the injection site.
Figs. 3 through 5 show external views of a side, a front and a rear of the injector device 10, respectively. As shown in these figures, the injection device 10 according to an embodiment of invention is compact and therefore easy to carry. Also, the graduations shown on the surface of the chamber housing 40 in FIG. 3 provides an indication of how AMENDED SI-fEET
much medication is stored in the injector device 10.
FIG. 6 shows an external view of the injector device 10 with a safety cap 90.
The safety cap 90 provides accidental discharge of the injector device 10 by preventing the forward movement of the actuating member 20. The safety cap 90 may be equipped with a S pocket clip so that the injector device 10 can be conveniently transported in a shirt pocket.
When the safety cap 90 is initially installed on the injector device 10, a seal, such as a plastic hot gun seal or the like, may be placed at multiple points around the joint formed by the safety cap 90 and the actuating member 20. The seal evidences any tempering of the injector device 10. The safety cap 90 may be made of similar materials as used in other parts of the injector device 10, such as plastic, fiberglass, polycarbonate, or the like While the description above refers to particular embodiments of the present invention, it will be understood that many modifications may be made without departing from the spirit thereof. The accompanying claims are intended to cover such modifications as would fall within the true scope and spirit of the present invention.
The presently disclosed embodiments are therefore to be considered in all respects as illustrative and not restrictive, the scope of the invention being indicated by the appended claims, rather than the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein.
WO 97113537 PCT/i1S96/16172 It is an object of an embodiment of the present invention to provide an improved disposable jet injector with simplified operating and safety features, that obviates for practical purposes, the above-mentioned limitations.
According to an embodiment of the present invention, a needle-less injector suitable for injecting liquid medication through a skin surface of a patient include a housing, a driver and a trigger. The housing contains the liquid medication to be injected into the patient. The driver forces the medication out of the housing at a sufficient speed to pierce the skin surface of the patient. The resistance sensitive trigger is coupled to the driver and is used to activate the driver to force the liquid medication out of the housing. The resistance sensitive trigger is activated upon application of a predetermined amount of pressure to the resistance sensitive trigger that is opposed by a predetermined amount of resistance from the skin surface of the patient. The predetermined amount of resistance results from the housing having contact with the skin surface of the patient, and when this predetermined amount of _ resistance is reached the liquid medication is forced out of the housing by the driver to pierce the skin surface of the patient.
In further embodiments, the housing of the needle-less injector includes a face that is adapted to align the housing to produce the predetermined amount of resistance to allow for activation of the resistance sensitive trigger. Also, the resistance sensitive trigger is preferably coupled to the housing to permit axial movement of the resistance sensitive trigger along the housing. However, the fit tolerances between the housing and the resistance sensitive trigger are selected to permit activation of the resistance sensitive trigger when the housing is aligned between 0 and 10 degrees off an axis perpendicular to the skin surface of the patient. In addition, the resistance sensitive trigger is preferably positioned to be between the skin surface of the patient and an activating appendage (such as an hand, arm or the like) of a user when activating the driver the force the medication out from the housing.
In particular embodiments, the resistance sensitive trigger includes a resistance element that activates at a lower amount of pressure than the predetermined amount of resistance by the skin surface of the patient. For example, the resistance sensitive trigger includes a cap that is slidably attached to the housing and the resistance element includes a spring coupled between the housing and the cap. Thus, upon application of the predetermined amount of pressure to the cap of the resistance sensitive trigger, the spring r compresses when the opposing resistance from the skin surface of the patient reaches the predetermined amount of resistance to activate the driver to force the liquid medication out of the housing to pierce the skin surface of the patient.
According to further embodiments of the present invention, a compressed gas activated needle-less injector device is suitable for injecting liquid medication through the skin surface. The housing of the needle-less injector includes a main body portion, a valve and a chamber housing portion. The main body portion includes a first gas chamber, a passageway and a second gas chamber which is in gaseous communication with the first gas chamber through the passageway. The first gas chamber contains a pre-filled compressed gas, such as inert gas, that exits through the passageway. The second gas chamber partially contains the driver. The pressure of the compressed gas is sufficiently high to accelerate the - liquid medication at a speed sufficient to pierce through the skin surface.
The valve is detachably mounted to block the passageway to prevent the flow of the compressed gas from the first gas chamber until needed. The valve is positioned in between the first gas chamber and the second gas chamber. The chamber housing portion is securely coupled to the main body portion and includes a liquid chamber and an orifice. In preferred embodiments, the liquid chamber holds the pre-filled and pre-measured liquid medication and is in fluid communication with the driver. The driver can be formed by a piston disposed and movable within the liquid chamber, and a plunger disposed and movable within the liquid chamber along with the piston to force the liquid medication out from the liquid chamber through the orifice. The orifice is formed in one end of the chamber housing portion and is in fluid communication with the liquid chamber. In operation, the compressed gas, when released from the first gas chamber, pushes the liquid forcing assembly, which in turn pushes the liquid medication out through the orifice to pierce the skin surface of the user.
In the embodiment discussed above, the piston has a head which is disposed within <
the second gas chamber. The head creates an air and fluid tight seal so that the compressed gas released from the first gas chamber is trapped in the second gas chamber.
In a further embodiment, the injector device is equipped with a lever for breaking the valve. In particular embodiments, the lever is slidably mounted through a side wall of the main body adjacent to the valve so that when one end of the lever is pushed in, the other end of the lever breaks off the valve, thus releasing the compressed gas into the second gas J
chamber. The resistance sensitive trigger may include an incline ramp surface that pushes the lever inward when the resistance sensitive trigger is depressed. In preferred embodiments, a coil spring is positioned between the resistance sensitive trigger and the main body portion to bias the resistance sensitive trigger in an un-depressed state. A
retainer, such as a retainer ring, may be used to couple the resistance sensitive trigger to the main body portion, and a protective cover, such as a screw-on cap may be used to cover the orifice to maintain sterility of the injection device.
Other features and advantages of the invention will become apparent from the following detailed description, taken in conjunction with the accompanying drawings which _ illustrate, by way of example, various features of embodiments of the invention.
BRIEF DESCRIPTION OF THE DRAWINGS
A detailed description of embodiments of the invention will be made with reference to the accompanying drawings, wherein like numerals designate corresponding parts in the several figures.
FIG. 1 is a cross-sectional diagram of an injector device according to an embodiment of the invention;
FIG. 2 is an exploded view of an actuating member according to an embodiment of the invention;
FIG. 3 is an external side view of an injector device;
FIG. 4 is an external front view of an injector device;
FIG. 5 is an external rear view of an injector device;
FIG. 6 is an external view of an injector device with a safety cap.
DETAILED DESGiZTPTION OF THE P FFFRRFT~ FMRnr~I~NTc As shown in the drawings for purposes of illustration, the invention is embodied in a needle-less injector. In preferred embodiments of the present invention, the a gas powered needle-lee injector device that is pre-loaded with medication and is adapted for a single use.
Preferably, the needle-less injector is for use with human beings. However, it will be Y
recognized that further embodiments of the invention may be used on animals or in other applications requiring needle-less injection, such as passing injectable substances through a porus membrane or the like. In addition, the needle-less injector may uses springs, pyrotechnic charges or the like instead of gas power as the injection delivering force.
As shown in the drawings, a needle-less injection device according to an embodiment of the invention is embodied in a pen sized device. The needle-less injector device 10 according to an embodiment of the invention is useful for hypodermic injection of medication without piercing the skin (non-invasive) with a needle and represents an improvement over known devices. The device 10 may be used as a single dose disposable - injector to deliver a dosage of fluid medication. The preferred embodiment ensures precise delivery through an orifice with the diameter of approximately .0032"
(approximately 0.08 mm). However, larger or smaller diameters may be used, as long as accurate penetration of the skin and delivery of the medication can be maintained. The fluid is linearly accelerated via pneumatic propulsion. Safety is maintained and inadvertent activation of the injection device 10 is avoided via a pressure (e.g., resistance) sensitive triggering feature which allows for proper tensioning of the nozzle and orifice at the injection site prior to automatic medication deployment. For example, activation of the injector device 10 will not occur until the injector is properly positioned to provide the required resistance from the skin surface of the patient to allow for sufficient tension and pressure to be applied to a trigger of the injector device 10 to activate it to deliver the dosage of medication.
Improper positioning resulting in insufficient resistance by the skin surface of the patient will prevent the injector device from being inadvertently activated. For example, tight tolerances between a trigger cap and a housing will prevent the cap from sliding along the housing to trigger the device 10, if the device 10 is more than 10 degrees off of an axis perpendicular to the skin surface of the patient.
The device utilizes prepackaging and precisely measured dosages for a variety of medical applications. However, alternative embodiments may be loaded prior to injection.
- The injector device 10 can be manufactured in various custom sizes for precise medication delivery over a wide range of medication types and dosage amounts. Preferred embodiments allow for a single injection in amounts that range from about 1/20th of one cubic centimeter(cc) to 1.0 cc. The type of injector device 10 is typically used on human patients.
However, in alternative embodiments, a larger injector device with larger medication capacity may be constructed and used on animals, such as livestock or the like.
FIG. 1 shows a needle-less injector device 10 according to an embodiment of the invention. The injector device 10 has a main body 12, a chamber housing 40, a cap 60, a piston 50, an actuating member 20, and a first gas chamber I 8. The main body 12 includes a first body portion 13 integrally connected to a second body portion 19 (main body 12, first body portion 13, and second body portion 19 may be a single unit in design and manufacturing). In the preferred embodiment of the device, the second body portion 19 has a slightly larger diameter than that of the first body portion 13. A flange 27 is formed due to a larger diameter of the second body portion 19. The first body portion 13 and the second body portion 19 each has an elongated cylindrical shape. However, in alternative embodiments, other shapes such as rectangular, triangular or the like may be used. The main body 12 also has an elongated cavity 17 centrally disposed along the length of the first body portion 13 and partially along the length of the second body portion 19. The elongated cavity 17 forms an opening which is located on the end of the main body 12, opposite of the second body portion 19. The elongated cavity 17 has a cylindrical shape with substantially the same diameter. However, in alternative embodiments, other shapes such as rectangular, triangular or the like may be used. The diameter of the elongated cavity 17 gradually tapers off as the elongated cavity 17 nears the second body portion 19. The smaller diameter portions of the elongated cavity 17 limits the backward movement of the piston 50 and tends to increase the rate of acceleration when the jet injection device 10 is first activated.
The second body portion 19 includes a lever passageway 74 and the first gas chamber I 8 for storing compressed inert gas, such as carbon dioxide. However, alternative embodiments may use other gases or a gas/liquid combination. The elongated cavity 17 (i.e., containing a second gas chamber 14) and the first gas chamber 18 are coupled together to provide gaseous communication with each other through a passageway 30. The first gas chamber 18 of the second body portion 19 has an opening on the opposite end of the passageway 30, through which compressed gas is pre-filled into the first gas chamber 18. A
retention groove 28 ( preferably ring shaped) is formed around the inner diameter of the first gas chamber I 8 near the end of the large opening in the first gas chamber. A
chamber plug 26 is disposed within the opening of the first gas chamber 18 to seal in the compressed inert I 0 gas, once the gas has been loaded. The chamber plug 26 forms an air tight seal in the first gas chamber I 8 by engaging the retention groove 28. The retention groove 28 also prevents the chamber plug 26 from detaching itself from the second body portion 19 due to the presence of compressed gas in the first gas chamber 18. The chamber plug 26 is configured and sized to firmly fit into the opening of the first gas chamber 18. In alternative embodiments, instead of the retention groove 28, the inner surface of the first gas chamber may be threaded so that the chamber plug 26 (with corresponding outer threads) may be screwed into the first gas chamber 18. Alternatively, the first gas chamber 18 may be a sealed compartment in which compressed gas is injected through a valve. A seal may be obtained by using an adhesive or other suitable materials. The chamber plug 26 may be made of any suitable rigid materials, such as plastic, rubber, ceramic, metal, composites and the like. Although the main body 12 may be made of plastic by, such process as an injection molding, other suitable materials, such as ceramic, glass, metal, composites or the like, may be used. In addition, the first body portion 13 and the second body portion 19 may be formed together as one injection mold or may be formed from separate portions coupled together by adhesives, welding, snap fits or the like. In preferred embodiments, the chamber plug 26 would be plastic welded, glued or otherwise secured in the first gas chamber 18 immediately after the first gas chamber is filled with gas.
Inside the elongated cavity 17, a release tab 16 (or valve) is attached to the wall to block of~'and seal the passageway 30. In its normal position, the release tab 16 blocks the gas flow from the first gas chamber 18 into the elongated cavity 17. When the release tab 16 is detached or broken off from its original position, the compressed gas from the first gas chamber 18 is released into the elongated cavity 17. More specifically, the compressed gas is released into a second gas chamber I 4, which is a part of the elongated cavity 17. The release tab 16 is preferably sufficiently large to fully cover the opening in the passageway 30, thus preventing any gas leak. In the preferred embodiment, the release tab 16 may be molded with the main body 12. Alternatively, the release tab 16 may be attached to the wall by any suitable process, such as using an adhesive, welding or the like. The release tab 16 is preferably detached or broken off by applying force on its side, but it should be attached firmly enough to withstand the pressure exerted by the compressed air in the first gas chamber I 8 or a shock from a drop. In addition, the release tab 16 should resist being sheared off until the injector device 10 is placed in contact with the skin of a patient and sufficient resistance is encountered to permit the injector device 10 to be activated by applying sufficient pressure to shear off the release tab 16.
- The lever passageway 74 is typically formed on the side wall of the main body 12 and extends from the outer to the inner surface of the second body portion 19 at a slightly slanted angle. However, other configurations may be used. The lever passageway 74 is adapted and configured to hold a lever 70 which protrudes through the lever passageway 74.
In the preferred embodiment, the lever 70 is a cylindrical rod with a rounded end 72. The rounded end 72 protrudes out of the second body portion 19. The lever 70 has preferably the sufficiently same cross-section and diameter as the lever passageway 74 to firmly fit inside the passageway 74 to provide a sufficiently tight air and fluid seal to not hinder with the effective performance of the injection device 10. However, there may be some clearance between the lever 70 and the passageway 74 to bleed-out excess gas pressure over a time period once the injector device 10 has been used. In an alternative embodiment, there may be a plurality of levers 70 disposed through a plurality of lever passageways 74 to ensure the removal of a release tab 16. For example, the main body 12 may accommodate two levers at a 90 degree angle to each other so that the combined force of those levers ensure proper detachment of the release tab 16. In addition, the lever 70 and the passageway 74 may be formed of a rectangular rod shape or other suitable shapes. The lever 70 may be made of resilient plastic or other suitable materials.
The chamber housing 40 includes an elongated tubular body 43, a neck portion and a liquid chamber 41 for storing and holding, for example, liquid medication (not shown).
The chamber housing 40 has an orifice 42 (or nozzle) at one end and has an opening configured to receive the piston 50 at the other end. The orifice 42 is centrally positioned on an injector face 49. The injector face 49 has a flat surface, except that the center region around the orifice 42 is raised slightly. The raised surface around the orifice 42 provides firm contact against a receiving surface, such as the skin surface (not shown). This helps to insure that the injector is properly positioned and will not be activated until sufficient pressure is applied to the injector device 10.
The outer diameter of the neck portion 45 is smaller than the outer diameter of the elongated tubular body 43 which forms a shoulder portion 47 where the two parts join together. The shoulder portion 47 rests on the surface of the opening formed by the elongated cavity 17 of the main body 12. However, the outer diameter of the neck portion 45 is substantially the same as the inner diameter of the elongated cavity 17 of the main body 12 so that the neck portion 45 firmly fits inside the elongated cavity 17. To firmly engage the neck portion 45 of the chamber housing 40 with the elongated cavity 17 of the main body, the middle section of the neck portion 45 may have a slightly larger outer diameter that fits into a groove 15 formed inside the elongated cavity 17. Once coupled together, the chamber housing 40 cannot be released from the main body 12, unless extreme force is applied. In alternative embodiments, the raised outer diameter of the neck portion is altered to form threads on the outer diameter of the neck portion 45 and matching threads are formed inside the elongated cavity 17 to screw-in the chamber housing 40. This provides the advantage of being able to assemble the device 10 when needed or just prior to giving an injection. This assembly option allows the user to select a variety of different medications or dosages while minimizing the number of complete injectors 10 that must be carried or stocked. It would also facilitate manufacture of the device 10 since the injector 10 and the chamber housing 40 , may be manufactured at different times. Further, the main body 12 and the chamber housing 40 may be attached and sealed together by any suitable method, such as adhesives, welding or the like. A ring joint 48, in the form of a plastic weld fillet, is also used to further reinforce the attachment of the chamber housing 40 to the main body 12. In the preferred embodiment, the ring joint 48 abuts against the shoulder portion 47 and the opening surface of the elongated cavity 17. The ring joint 48 provides additional strength to securely hold the chamber housing 40 in the main body 12. Although not shown in the drawings, an O-ring may be placed between the shoulder portion 47 of the chamber housing 40 and the opening surface of the elongated cavity 17 to provide an additional air and fluid tight seal.
For easy measuring and observation of the amount of medication in the liquid chamber 41, the elongated tubular body 43 includes graduations so that the user can determine the amount of medication contained in the injector device 10. The chamber housing 40 can be formed of glass or other suitable materials, such as plastic, ceramic, polycarbonate or the Like. In the preferred embodiment, the chamber housing 40 is transparent so that the liquid medication and the various moving parts in the liquid chamber 4I can be visually examined. Also, the chamber housing 40 is disposable, however the chamber housing may be recycled, if desired.
A cap 60 may be mounted on the end of the chamber housing 40 to cover the orifice 42. The cap 60 provides and maintains sterility of the injection device 10 and prevents an accidental discharge of the liquid medication disposed inside the liquid chamber 41 from shock, evaporation or seepage. Threads 44 for mounting the cap 60 are on the outer surface of the end portion of the chamber housing 40. The cap 60 has matching threads 62 on the inner surface so that the cap 60 can be screwed-on at the end portion of the chamber housing 40. Once screwed-on, the cap 60 provides an air and fluid tight seal around the orifice to prevent any foreign material from being introduced into the liquid chamber 41.
In alternative embodiments, the cap 60 and the end portion of the chamber housing 40 can be configured so that the cap 60 is snapped-on instead of screwed-on. The cap 60 may be made of any suitably rigid material, such as plastic polymers, rubber, ceramic or the like.
The piston 50 has an elongated cylindrical body S I with an indented front surface 52 at one end and a head 54 at the opposite end. The head 54 includes a rear surface 55, which is preferably concave. In alternative embodiments, the front and rear surfaces may be flat, or have other suitable shapes. The elongated cylindrical body 51 of the piston 50 is disposed inside the liquid chamber 41 for sliding movement along its length. In preferred embodiments the elongated cylindrical body 51 has substantially the same outer diameter as the diameter of the liquid chamber 41 to provide free sliding movement along the length of the liquid chamber 41. Due to an air and fluid tight seal around a plunger 56, the air and fluid tight seal around the piston 50 may not be necessary. The head 54 of the piston 50 has substantially the same outer diameter as the inner diameter of the elongated cavity 17 to form an air and fluid tight seal with a minimal friction between the head 54 and the walls of the elongated cavity 17. The space defined between the head 54 and the back wall of the elongated cavity 17 is the second gas chamber 14. The head 54 is disposed inside the elongated cavity 17 so that the compressed gas introduced in the second gas chamber 14 expands the head 54 against the wall surface of elongated cavity 17, providing an additional seal, so that the compressed gas introduced into the second gas chamber 14 pushes the piston 50 forward.
Where the lower portion 82 of the head 54 makes contact with the neck portion 45 of the chamber housing 40, the shapes of both portions may be configured to match each other.
In the preferred embodiment, the end surface 80 of the neck portion 45 forms a concave surface while the lower portion 82 of the head 54 forms a convex surface. The matching shapes assist in delivering substantially all of the medication to the injection site. However, in alternative embodiments, other suitable shapes, such as a flat surface, may be used, and the piston 50 may be made of any suitable material such as plastic, glass, ceramic, metal, composites or the like.
Also disposed inside the liquid chamber 41 is a plunger 56. The plunger 56 has an outer diameter which is substantially the same as the inner diameter of the liquid chamber 41 to form an air and fluid tight seal. The plunger 56 is disposed between the piston 50 and the orifice 42. The medication is situated in front of the plunger 56 (i.e., between the orifice 42 and the plunger 56) so that the forward movement of the plunger 56 forces the liquid , medication toward the orifice 42. The front surface of the plunger 56 may be configured to match the opening defined by an orifice guide 46. In preferred embodiments, the front surface of the plunger 56 has a convex surface to match the concave shape of the orifice guide 46, whose vertex is the orifice 42. The shape of the orifice guide 46 focuses and increases the speed of liquid medication as it exits the orifice 42. The matching shapes of the orifice guide 46 and the plunger 56 tend to minimize the waste of medication, since most of the medication is forced out through the orifice 42. The shape of the rear surface of the plunger 56 matches the front surface 52 of the piston 50. The similarly shaped configuration provides for an even distribution of the pressure on the rear of the plunger 56 when the piston 50 moves forward. This tends to minimize jams or distortion as the plunger 56 is driven forward. The plunger 56 is generally made of rubber or other suitable materials, such as plastic, composites or the like. In alternative embodiments, the plunger 56 and the piston 50 formed as and integrated piece either by attaching the plunger 56 to the piston 50 or by molding the piston assembly to include the plunger 56.
A resistance sensitive trigger includes an actuating member 20 that is an elongated tubular member that slides over the second body portion 19 of the main body 12. The actuating member 20 has a trigger portion 22, a raised rail 76 (see FIG. 2), and a retainer slot 25. The actuating member 20 is enclosed at one end and has an opening at the other end. On the inner surface of the enclosed end, there is a spring surface 23 for holding or mounting a coil spring 24. The resistance sensitive trigger also includes a coil spring 24 that is positioned between a spring surface 23 and the chamber plug 26 and provides a resilient bias toward the rear end. The proper use of the injection device 10 requires that the injector device 10 be positioned substantially perpendicular to the skin surface before the medication is injected into the injection site. Therefore, the tension strength of the coil spring 24 should be sufficiently strong to prevent accidental triggering when the injection device 10 is not properly positioned. Typically, a minimum applied pressure of 2.2 lbs/in2 ( 1.0 kg/2.5 cmz) is required to discharge the injector. However, slight lower or higher minimums may be required depending on the skin of the patient or where the injection is to be administered. In alternative embodiments, alternate resistance elements may be used instead of the coil spring 24, such as deformable rubber or plastic, strain gauges or the like.
In the front opening of the actuating member 20, there is a retainer slot 25 for mounting a retainer 75. The retainer slot 25 is formed around the inner circumference of the actuating member 20, extending from one side of the raised rail 76 to the other side. The retainer 75, which is in a form of a thin circular rod, is mounted into the retainer slot 25. The circumferential length of the retainer 75 is substantially equal to that of the retainer slot 25.
When the actuating member 20 is installed onto the second body portion 19, the retainer 75 generally rests against the flange 27. This prevents the actuating member 20 from detaching itself from the second body portion 19 due to rearward force exerted by the coil spring 24.
The retainer 75 may be made of plastic or other suitable materials such as metal or the like.
In alternative embodiments, the retainer 75 and the actuating member 20 may be formed as one integral member by molding process or other suitable processes. The actuating member is typically made of plastic or other suitably rigid and resilient materials, such as glass, composite, ceramic or metal. The trigger portion 22 is on the outer end surface of the actuating member 20. It preferably forms a concave surface and is coated with a textured 15 material to prevent depressing force, such as from a thumb, from slipping.
FIG. 2 shows an exploded view of the actuating member 20 of the resistance sensitive trigger. As shown in FIG. 2, the raised rail 76 extends along the length of the outer surface of the actuating member 20. A conduit 78 is formed along the length of the raised rail 76. The cross-sectional shape and dimension of the conduit is configured to 20 accommodate the protruding portion of the lever 70. The raised rail 76 has a thickness which varies along its length. The thickness of the raised rail 76 is thinner near the opening of the actuating member 20. Toward the rear portion of the actuating member 20 where a lever 70 is situated, a gradually inclined region 21 is formed on the inner surface of the raised rail 76.
When the actuating member 20 is not depressed, the lever 70 rests on the flat thinner inner surface of the raised rail 76. This is the normal state of the injection device 10 prior to injection. When the actuating member 20 is depressed, the actuating member 20 moves forward, and the inclined region 21 forces the lever 70 toward the center of the second body portion 19. The inward movement of the lever tears (or breaks off) the release tab 16 and , consequently releases the compressed gas in the first gas chamber 18. The raised rail 76 can be formed as integral part of the actuating member by a molding process or other suitable processes.
As shown in Figs. 1, 2 and 4, the second body portion 19 includes three splines 100 and the actuating member 20 includes corresponding three spline slots 102 adapted to slidably receive the splines 100 of the second body portion 19. The splines 100 and spline slots 102 are provided to assist the actuating member 20 to slide along the second body portion as the actuating member 20 is depressed to deliver an injection. The splines 100 and spline slots 102 substantially prevent the actuator member 20 from rotating about the second body portion 19 to avoid jamming of the actuating member 20 during an injection. The splines 100 and spline slots 102 also prevent rotational movement of the actuating member about the second body portion 19 when the cap 60 is removed or threaded onto the chamber housing 40. This limits the amount of torsional stress placed on the lever 70 in the passageway 74 during an injection or when removing or threading the cap 60 onto the chamber housing 40. In alternative embodiments, a different number of splines and spline 15 slots may be used. Also, if the lever 70 is sufficiently strong enough the splines and spline slots may be eliminated. In further alternatives, the splines 100 and/or spline slots 102 may be coated with a lubricant or formed from materials with low frictional coefficients to facilitate sliding movement of the actuating member 20 along the second body portion 19. In preferred embodiments, the splines 100 and splines 102 have a rectangular cross-section.
20 However, in alternative embodiments, the splines and spline slots may have other cross-sections, such as triangular, saw tooth, dove tail or the like, to resist rotational movement of the actuating member 20 about the second body portion 19.
The operation of the needle-less injector device according to the preferred embodiment will now be discussed. Initially at the manufacturing facility, the injection device is pre-filled with medication in the liquid chamber 41 and is pre-filled with compressed gas in the first gas chamber 18. The user (or an operator) unscrews (or unsnaps) the cap 60 from the main body 12, thus revealing the orifice 42 of the injector device 10.
The user then positions the injector device 10 perpendicularly against the skin surface to provide firm and secure contact of the orifice 42 against the skin surface.
The injector device requires the device 10 to be properly oriented and in contact with the skin of the patient, since the injector device 10 is designed so that it cannot be activated or discharged without ' the device 10 being placed against the skin surface. Otherwise,. with a fluid delivery speed of about 800 fps (243.8 m/s) or higher, a jet injector could injure a person's eye or other part of 5 the body. In addition, if the jet injector were not positioned properly against the injection site, and the injection device were activated, the dosage can be short of the measured dosage, thereby creating wetting on the skin surface, which leads to additional problems associated with improper dosage amounts.
As the trigger portion 22 of the actuating member 20 is depressed, the skin surface of 10 the patient resists the pressure being applied to the actuating member 20 of the resistance senitive trigger and the coil spring 24 is compressed between the chamber plug 26 and the spring surface 23. Sufficient pressure (generally a minimum of 2.2 Ibs/in' ( 1.0 kg/2.5 cmZ)) must be applied at the trigger portion 22 to overcome the tension of the coil spring 24.
Concurrently, as the inclined region 21 pushes against the lever 70, the lever 70 is pushed inward toward the center axis of the main body 12. As the actuating member 20 is pressed further against the skin surface, the lever 70 pushes against the side of the release tab 16, tearing (or breaking off) the release tab 16. This exposes the opening of the passageway 30, and the compressed gas stored in the first gas chamber 18 is released into second gas chamber 14. When sufficient pressure is built up inside the second gas chamber 14, the piston 50 is pushed forward so that it slides forward in the liquid chamber 41. The seal around the head 54 of the piston 50 substantially prevents any gas from leaking into the other parts of the elongated cavity. The forward movement of the piston 50 causes the front surface 52 of the piston 50 to make contact with the rear surface of the plunger 56, to move the plunger 56 forward. As the plunger 56 moves forward, the liquid medication exits from the orifice 42 at a high speed and penetrates the skin surface at the injection site.
Figs. 3 through 5 show external views of a side, a front and a rear of the injector device 10, respectively. As shown in these figures, the injection device 10 according to an embodiment of invention is compact and therefore easy to carry. Also, the graduations shown on the surface of the chamber housing 40 in FIG. 3 provides an indication of how AMENDED SI-fEET
much medication is stored in the injector device 10.
FIG. 6 shows an external view of the injector device 10 with a safety cap 90.
The safety cap 90 provides accidental discharge of the injector device 10 by preventing the forward movement of the actuating member 20. The safety cap 90 may be equipped with a S pocket clip so that the injector device 10 can be conveniently transported in a shirt pocket.
When the safety cap 90 is initially installed on the injector device 10, a seal, such as a plastic hot gun seal or the like, may be placed at multiple points around the joint formed by the safety cap 90 and the actuating member 20. The seal evidences any tempering of the injector device 10. The safety cap 90 may be made of similar materials as used in other parts of the injector device 10, such as plastic, fiberglass, polycarbonate, or the like While the description above refers to particular embodiments of the present invention, it will be understood that many modifications may be made without departing from the spirit thereof. The accompanying claims are intended to cover such modifications as would fall within the true scope and spirit of the present invention.
The presently disclosed embodiments are therefore to be considered in all respects as illustrative and not restrictive, the scope of the invention being indicated by the appended claims, rather than the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein.
Claims (13)
1. A pre-filled compressed gas activated needle-less injector device suitable for injecting liquid medication through the skin surface, the device comprising:
a main body having a first gas chamber, a passageway and a second gas chamber in gaseous communication with the first gas chamber through the passageway, wherein the first gas chamber contains a pre-filled compressed gas that exits through the pas-sageway and into the second chamber;
a valve detachably mounted to block the passageway to prevent the flow of the compressed gas from the first gas chamber until detached, wherein the valve is positioned in between the first gas chamber and the second gas chamber;
a chamber housing coupled to the main body, the chamber housing comprising:
a liquid chamber that holds the liquid medication;
a liquid forcing assembly disposed within the liquid chamber that forces the liquid medication out from the liquid chamber;
an orifice formed in one end of the chamber housing and in fluid communication with the liquid chamber, wherein when the valve is permanently detached from blocking the passageway, the compressed gas is released from the first gas chamber into the second gas chamber and the compressed gas pushes the liquid forcing assembly which in turn pushes the liquid medication out through the orifice and pierces the skin surface; and an actuating member mounted on the main body, to move longitudinally along the main body when depressed, to produce a lateral force that permanently detaches the valve to release the compressed gas when a predetermined pressure is applied to the actuating member.
a main body having a first gas chamber, a passageway and a second gas chamber in gaseous communication with the first gas chamber through the passageway, wherein the first gas chamber contains a pre-filled compressed gas that exits through the pas-sageway and into the second chamber;
a valve detachably mounted to block the passageway to prevent the flow of the compressed gas from the first gas chamber until detached, wherein the valve is positioned in between the first gas chamber and the second gas chamber;
a chamber housing coupled to the main body, the chamber housing comprising:
a liquid chamber that holds the liquid medication;
a liquid forcing assembly disposed within the liquid chamber that forces the liquid medication out from the liquid chamber;
an orifice formed in one end of the chamber housing and in fluid communication with the liquid chamber, wherein when the valve is permanently detached from blocking the passageway, the compressed gas is released from the first gas chamber into the second gas chamber and the compressed gas pushes the liquid forcing assembly which in turn pushes the liquid medication out through the orifice and pierces the skin surface; and an actuating member mounted on the main body, to move longitudinally along the main body when depressed, to produce a lateral force that permanently detaches the valve to release the compressed gas when a predetermined pressure is applied to the actuating member.
2. A needle-less injector device according to claim 1, wherein the liquid forcing assembly includes:
a piston disposed and movable within the liquid chamber;
and a plunger disposed and movable within the liquid chamber along with the piston to force the liquid medication out from the liquid chamber through the orifice.
a piston disposed and movable within the liquid chamber;
and a plunger disposed and movable within the liquid chamber along with the piston to force the liquid medication out from the liquid chamber through the orifice.
3. A needle-less injector device according to claim 2, wherein the piston includes a head disposed within the second gas chamber and creates an air and fluid tight seal so that the compressed gas released from the first gas chamber is trapped in the second gas chamber.
4. A needle-less injector device according to claim 1, wherein the liquid chamber is pre-filled with a pre-measured amount of the liquid medication.
5. A needle-less injector device according to claim 1, wherein the first gas chamber is pre-filled with compressed gas to a pressure sufficient to accelerate the liquid medication at a speed sufficient to pierce through the skin surface.
6. A needle-less injector device according to claim 1, wherein the compressed gas is inert gas.
7. A needle-less injector device according to claim 1, further com-prising a lever for detaching the valve that is coupled to the actuating member, wherein the lever is slidably mounted through a side wall of the main body adjacent to the valve so that when one end of the lever is pushed in by the actuating member, the other end of the lever permanently detaches the valve from block-ing the passageway thus releasing the compressed gas into the second gas chamber.
8. A needle-less injector device according to claim 7, further includ-ing an elastic member coupled to the actuating member mounted on the main body to bias the actuating member outward and resist depression of the actuating member, wherein the actuating mem-ber is shaped to force the lever inward as the actuating member is depressed and moves longitudinally along the main body.
9. A needle-less injector device according to claim 8, wherein the actuating assembly includes an inclined surface that pushes the lever inward as the actuating member is depressed.
10. A needle-less injector device according to claim 8, wherein the elastic member is a coil spring disposed between the actuating member and the main body to bias the actuating member in an un-depressed state.
11. A needle-less injector device according to claim 8, wherein the actuating member further has a retainer device coupled to the main body to mount the actuating member on the main body.
12. A needle-less injector device according to claim 1, wherein a protective cover covers the orifice defined by the chamber hous-ing.
13. A needle-less injector device according to claim 1, wherein the injector device is for a one-time use.
Applications Claiming Priority (5)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US54147095A | 1995-10-10 | 1995-10-10 | |
| US08/719,459 | 1996-09-25 | ||
| US08/541,470 | 1996-09-25 | ||
| US08/719,459 US5730723A (en) | 1995-10-10 | 1996-09-25 | Gas pressured needle-less injection device and method |
| PCT/US1996/016172 WO1997013537A1 (en) | 1995-10-10 | 1996-10-09 | Gas pressured needle-less injection device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2234055A1 CA2234055A1 (en) | 1997-04-17 |
| CA2234055C true CA2234055C (en) | 2005-02-08 |
Family
ID=27066714
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002234055A Expired - Fee Related CA2234055C (en) | 1995-10-10 | 1996-10-09 | Gas pressured needle-less injection device |
Country Status (9)
| Country | Link |
|---|---|
| US (5) | US5730723A (en) |
| EP (1) | EP0988074B1 (en) |
| JP (1) | JP2001515370A (en) |
| AT (1) | ATE262935T1 (en) |
| AU (1) | AU7397096A (en) |
| CA (1) | CA2234055C (en) |
| DE (1) | DE69632084T2 (en) |
| ES (1) | ES2216069T3 (en) |
| WO (1) | WO1997013537A1 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US8221347B2 (en) | 2004-12-01 | 2012-07-17 | Acushot, Inc. | Needle-free injector |
Families Citing this family (548)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6474369B2 (en) | 1995-05-26 | 2002-11-05 | Penjet Corporation | Apparatus and method for delivering a lyophilized active with a needle-less injector |
| US5730723A (en) | 1995-10-10 | 1998-03-24 | Visionary Medical Products Corporation, Inc. | Gas pressured needle-less injection device and method |
| US6223786B1 (en) | 1998-11-14 | 2001-05-01 | Pen Jet Corporation | Apparatus and method for mixing medication and filling an ampule of a needle-less injector |
| FR2739562B1 (en) * | 1995-10-09 | 1998-04-24 | Moreau Defarges Alain | JET INJECTION DEVICE WITHOUT NEEDLE, INCLUDING AN OVER-MOLDED CARTRIDGE |
| US6080130A (en) * | 1998-11-14 | 2000-06-27 | Castellano; Thomas P. | Gas power source for a needle-less injector |
| US6261281B1 (en) * | 1997-04-03 | 2001-07-17 | Electrofect As | Method for genetic immunization and introduction of molecules into skeletal muscle and immune cells |
| US6004287A (en) * | 1997-09-23 | 1999-12-21 | Loomis; Dale J | Biolistic apparatus for delivering substances into cells and tissues |
| DE19820172A1 (en) * | 1997-09-30 | 2005-01-27 | Wolfgang Wagner | Injection arrangement for inserting a diagnostic carrier or medicament beneath a patient's skin has a compressed gas source and a valve closure for controlling the release of the gas that is used to inject a substance |
| US6610042B2 (en) | 1997-12-05 | 2003-08-26 | Felton Medical, Inc. | Disposable unit-dose jet-injection syringe for pre-filled and/or transfilled liquid injectable medical drug or vaccine products and method thereof |
| US6156008A (en) * | 1998-05-04 | 2000-12-05 | Castellano; Thomas P. | Device for avoiding subdermal hematomas from an injection |
| EP1100566A4 (en) * | 1998-07-27 | 2002-03-20 | Medi Ject Corp | Loading mechanism for medical injector assembly |
| US6689093B2 (en) | 1998-11-18 | 2004-02-10 | Bioject, Inc. | Single-use needle-less hypodermic jet injection apparatus and method |
| US6783509B1 (en) | 1998-11-18 | 2004-08-31 | Bioject Inc. | Single-use needle-less hypodermic jet injection apparatus and method |
| US6264629B1 (en) | 1998-11-18 | 2001-07-24 | Bioject, Inc. | Single-use needle-less hypodermic jet injection apparatus and method |
| US6406455B1 (en) * | 1998-12-18 | 2002-06-18 | Biovalve Technologies, Inc. | Injection devices |
| DE19859137C1 (en) * | 1998-12-21 | 2000-05-18 | Ferton Holding Sa | High pressure medicinal injection unit includes piston advanced into pressure chamber by series of resilient impacts, forcing fluid out in series of impulses for precise low-volume dosing |
| US7060048B1 (en) * | 1999-04-16 | 2006-06-13 | Powerject Research Limited | Needleless syringe |
| AU4656000A (en) * | 1999-04-22 | 2000-11-10 | Gilbert Garitano | Needleless permanent makeup and tattoo device |
| US7192713B1 (en) | 1999-05-18 | 2007-03-20 | President And Fellows Of Harvard College | Stabilized compounds having secondary structure motifs |
| AU5595300A (en) * | 1999-06-02 | 2000-12-18 | Microheart, Inc. | Devices and methods for delivering a drug |
| US7147633B2 (en) * | 1999-06-02 | 2006-12-12 | Boston Scientific Scimed, Inc. | Method and apparatus for treatment of atrial fibrillation |
| US20010027293A1 (en) * | 1999-06-29 | 2001-10-04 | Ashok V. Joshi | Storage stable fluid injection device and associated process |
| US6626871B1 (en) | 1999-10-11 | 2003-09-30 | Felton International, Inc. | Method and apparatus for removing cap from medical device |
| US7074210B2 (en) * | 1999-10-11 | 2006-07-11 | Felton International, Inc. | Universal protector cap with auto-disable features for needle-free injectors |
| US6776776B2 (en) | 1999-10-14 | 2004-08-17 | Becton, Dickinson And Company | Prefillable intradermal delivery device |
| US6569123B2 (en) | 1999-10-14 | 2003-05-27 | Becton, Dickinson And Company | Prefillable intradermal injector |
| US6494865B1 (en) | 1999-10-14 | 2002-12-17 | Becton Dickinson And Company | Intradermal delivery device including a needle assembly |
| US20020193740A1 (en) | 1999-10-14 | 2002-12-19 | Alchas Paul G. | Method of intradermally injecting substances |
| US6569143B2 (en) | 1999-10-14 | 2003-05-27 | Becton, Dickinson And Company | Method of intradermally injecting substances |
| FI115664B (en) * | 1999-10-20 | 2005-06-15 | Uponor Innovation Ab | connecting portion |
| US6673035B1 (en) | 1999-10-22 | 2004-01-06 | Antares Pharma, Inc. | Medical injector and medicament loading system for use therewith |
| FR2800619B1 (en) * | 1999-11-05 | 2002-02-08 | Cross Site Technologies | NEEDLELESS SYRINGE WITH TEMPORARILY RETAINED PUSHING MEDIA |
| US6254579B1 (en) * | 1999-11-08 | 2001-07-03 | Allergan Sales, Inc. | Multiple precision dose, preservative-free medication delivery system |
| DE19955201A1 (en) * | 1999-11-16 | 2001-05-31 | Roesch Ag Medizintechnik | Injection device |
| US6770054B1 (en) | 1999-11-23 | 2004-08-03 | Felton International, Inc. | Injector assembly with driving means and locking means |
| AU1927701A (en) * | 1999-11-23 | 2001-06-04 | Needleless Ventures, Inc. | Injector assembly with driving means and locking means |
| US7887506B1 (en) | 1999-11-23 | 2011-02-15 | Pulse Needlefree Systems, Inc. | Safety mechanism to prevent accidental patient injection and methods of same |
| WO2001051109A1 (en) * | 2000-01-07 | 2001-07-19 | Biovalve Technologies, Inc. | Injection device |
| US6210359B1 (en) | 2000-01-21 | 2001-04-03 | Jet Medica, L.L.C. | Needleless syringe |
| FR2804869B1 (en) * | 2000-02-11 | 2002-05-17 | Poudres & Explosifs Ste Nale | NEEDLELESS SYRINGE FOR THE INJECTION OF A LIQUID CONTAINED IN A PRE-FILLED BULB |
| AU2001247721A1 (en) * | 2000-03-23 | 2001-10-03 | Antares Pharma, Inc. | Single use disposable jet injector |
| FR2809626B1 (en) * | 2000-05-30 | 2003-03-07 | Poudres & Explosifs Ste Nale | NEEDLELESS SYRINGE WITH MULTI-DUCT EJECTOR INSULATION MEMBRANE |
| US6629958B1 (en) | 2000-06-07 | 2003-10-07 | Ronald P. Spinello | Leak sealing needle |
| US6406456B1 (en) | 2000-06-08 | 2002-06-18 | Avant Drug Delivery Systems, Inc. | Jet injector |
| DE10029325A1 (en) * | 2000-06-20 | 2002-01-03 | Peter Lell | Needle-free injection device with pyrotechnic drive |
| FR2810554B1 (en) * | 2000-06-22 | 2003-05-16 | Poudres & Explosifs Ste Nale | SYRINGE WITHOUT NEEDLE PROVIDED WITH A MODULAR RESERVOIR |
| FR2812202B1 (en) * | 2000-07-28 | 2002-09-13 | Poudres & Explosifs Ste Nale | NEEDLELESS SYRINGE OPERATING BY COMPRESSION OF THE TANK CONTAINING THE LIQUID ACTIVE INGREDIENT |
| UA81743C2 (en) | 2000-08-07 | 2008-02-11 | Центокор, Инк. | HUMAN MONOCLONAL ANTIBODY WHICH SPECIFICALLY BINDS TUMOR NECROSIS FACTOR ALFA (TNFα), PHARMACEUTICAL MIXTURE CONTAINING THEREOF, AND METHOD FOR TREATING ARTHRITIS |
| US7288390B2 (en) | 2000-08-07 | 2007-10-30 | Centocor, Inc. | Anti-dual integrin antibodies, compositions, methods and uses |
| US6902734B2 (en) | 2000-08-07 | 2005-06-07 | Centocor, Inc. | Anti-IL-12 antibodies and compositions thereof |
| GB0022742D0 (en) | 2000-09-15 | 2000-11-01 | Smithkline Beecham Biolog | Vaccine |
| CA2324045A1 (en) * | 2000-10-20 | 2002-04-20 | Universite De Sherbrooke | No-needle syringe for the subcutaneous injection of medicated powders |
| US8071740B2 (en) * | 2000-11-17 | 2011-12-06 | Vascular Biogenics Ltd. | Promoters exhibiting endothelial cell specificity and methods of using same for regulation of angiogenesis |
| AU2003222427B8 (en) * | 2000-11-17 | 2010-04-29 | Vascular Biogenics Ltd. | Promoters exhibiting endothelial cell specificity and methods of using same |
| EP1339442A4 (en) * | 2000-11-30 | 2006-12-27 | Biovalve Technologies Inc | Injection systems |
| CA2438942A1 (en) | 2001-02-23 | 2002-09-26 | Glaxosmithkline Biologicals S.A. | Influenza vaccine formulations for intradermal delivery |
| US6645170B2 (en) | 2001-03-05 | 2003-11-11 | Bioject Medical Technologies, Inc. | Simplified disposable needle-free injection apparatus and method |
| US6471669B2 (en) | 2001-03-05 | 2002-10-29 | Bioject Medical Technologies Inc. | Disposable needle-free injection apparatus and method |
| CA2440983A1 (en) | 2001-03-14 | 2002-09-26 | Penjet Corporation | System and method for removing dissolved gas from a solution |
| GB0109297D0 (en) | 2001-04-12 | 2001-05-30 | Glaxosmithkline Biolog Sa | Vaccine |
| BR0116984A (en) | 2001-04-13 | 2004-06-29 | Penjet Corp | Needle injector with modular gas pressurization |
| US20050192530A1 (en) * | 2001-04-13 | 2005-09-01 | Penjet Corporation | Method and apparatus for needle-less injection with a degassed fluid |
| US6613010B2 (en) | 2001-04-13 | 2003-09-02 | Penjet Corporation | Modular gas-pressured needle-less injector |
| WO2002087663A2 (en) | 2001-04-27 | 2002-11-07 | Penjet Corporation | Method and apparatus for filling or refilling a needle-less injector |
| MY134424A (en) | 2001-05-30 | 2007-12-31 | Saechsisches Serumwerk | Stable influenza virus preparations with low or no amount of thiomersal |
| US20100221284A1 (en) | 2001-05-30 | 2010-09-02 | Saech-Sisches Serumwerk Dresden | Novel vaccine composition |
| US6752781B2 (en) * | 2001-06-08 | 2004-06-22 | Sergio Landau | Durable hypodermic jet injector apparatus and method |
| US7544188B2 (en) * | 2001-07-19 | 2009-06-09 | Intelliject, Inc. | Medical injector |
| JP4173446B2 (en) | 2001-10-19 | 2008-10-29 | ヴァスキュラー バイオジェニックス リミテッド | Polynucleotide constructs and pharmaceutical compositions and methods for targeted down-regulation of angiogenesis and anti-cancer therapy |
| US6824526B2 (en) | 2001-10-22 | 2004-11-30 | Penjet Corporation | Engine and diffuser for use with a needle-less injector |
| US6607510B2 (en) | 2001-11-09 | 2003-08-19 | Bioject Medical Technologies Inc. | Disposable needle-free injection apparatus and method |
| DE10155344A1 (en) * | 2001-11-10 | 2003-05-28 | Schott Glas | Filled container for a subcutaneous jet injection system has a screw closure cap, of the same material as the container, with a centering unit to align a pin with the jet outlet opening for sealing |
| CA2467719C (en) | 2001-11-14 | 2015-03-17 | Jill Giles-Komar | Anti-il-6 antibodies, compositions, methods and uses |
| EP1470161A1 (en) * | 2002-01-18 | 2004-10-27 | Inovio AS | Bispecific antibody dna constructs for intramuscular administration |
| EP1476210B1 (en) | 2002-02-11 | 2008-09-24 | Antares Pharma, Inc. | Intradermal injector |
| WO2003074102A2 (en) * | 2002-03-04 | 2003-09-12 | Nano Pass Technologies Ltd. | Devices and methods for transporting fluid across a biological barrier |
| GB0206560D0 (en) * | 2002-03-20 | 2002-05-01 | Glaxo Group Ltd | Novel device |
| US20030196928A1 (en) * | 2002-04-19 | 2003-10-23 | Parsons J. Stuart | Multi-component ampule |
| WO2003103751A1 (en) * | 2002-06-10 | 2003-12-18 | Akzo Nobel N.V. | Needle-less injector |
| WO2004002417A2 (en) | 2002-06-28 | 2004-01-08 | Centocor, Inc. | Mammalian ch1 deleted mimetibodies, compositions, methods and uses |
| AU2003243875B2 (en) * | 2002-07-11 | 2006-07-06 | Tecpharma Licensing Ag | Needle-free injection device |
| US7081109B2 (en) * | 2002-08-22 | 2006-07-25 | Baxa Corporation | Sterile docking apparatus and method |
| MXPA05002072A (en) | 2002-08-26 | 2005-06-08 | Penjet Corp | Apparatus for needle-less injection with a degassed fluid. |
| FR2852517B1 (en) * | 2003-03-21 | 2005-11-11 | INJECTION DEVICE WITHOUT NEEDLE WITH PYROTECHNIC CARTRIDGE AND METHOD FOR ASSEMBLING SUCH A DEVICE | |
| US8012136B2 (en) * | 2003-05-20 | 2011-09-06 | Optimyst Systems, Inc. | Ophthalmic fluid delivery device and method of operation |
| CA2526362C (en) * | 2003-05-20 | 2012-10-09 | James F. Collins | Ophthalmic drug delivery system |
| AU2004272972A1 (en) | 2003-05-22 | 2005-03-24 | Fraunhofer Usa, Inc. | Recombinant carrier molecule for expression, delivery and purification of target polypeptides |
| WO2004112871A1 (en) * | 2003-06-20 | 2004-12-29 | Allergan, Inc. | Needless injectors |
| US20070293447A1 (en) * | 2003-08-29 | 2007-12-20 | Yasuo Kunugiza | Gene Therapy for Skin Disorders Using Needleless Syringes |
| WO2005034949A1 (en) | 2003-09-09 | 2005-04-21 | University Of Florida | Desferrithiocin derivatives and their use as iron chelators |
| IL157984A (en) | 2003-09-17 | 2015-02-26 | Dali Medical Devices Ltd | Autoneedle |
| IL157981A (en) | 2003-09-17 | 2014-01-30 | Elcam Medical Agricultural Cooperative Ass Ltd | Auto-injector |
| PL2332968T3 (en) | 2003-11-05 | 2017-08-31 | Dana-Farber Cancer Institute, Inc. | Alpha-helical peptides suitable for activating or inhibiting cell death |
| EP1699524A4 (en) * | 2003-11-18 | 2009-07-15 | Nanopass Technologies Ltd | Enhanced penetration system and method for sliding microneedles |
| CA2546468C (en) * | 2003-12-05 | 2015-05-26 | Aradigm Corporation | A device for readying a needle free injector for delivery |
| EP1722842A1 (en) * | 2004-01-26 | 2006-11-22 | The Medical House Plc | Needle-free injection device |
| US7717879B2 (en) * | 2004-02-03 | 2010-05-18 | Smjm Inject Gmbh | Anesthetic syringe |
| IL160891A0 (en) | 2004-03-16 | 2004-08-31 | Auto-mix needle | |
| EP1750754A4 (en) * | 2004-03-31 | 2010-09-22 | Centocor Ortho Biotech Inc | Human glp-1 mimetibodies, compositions, methods and uses |
| US7717874B2 (en) * | 2004-05-28 | 2010-05-18 | Bioject, Inc. | Needle-free injection system |
| EP1773439A4 (en) * | 2004-07-14 | 2010-01-20 | By Pass Inc | Material delivery system |
| US7910787B2 (en) * | 2004-07-29 | 2011-03-22 | Gas Technologies Llc | Method and system for methanol production |
| US9180426B2 (en) | 2004-07-29 | 2015-11-10 | Gas Technologies, Llc | Scrubber for methanol production system |
| US7393662B2 (en) | 2004-09-03 | 2008-07-01 | Centocor, Inc. | Human EPO mimetic hinge core mimetibodies, compositions, methods and uses |
| CA2580103C (en) | 2004-09-22 | 2021-11-16 | Glaxosmithkline Biologicals S.A. | Immunogenic composition |
| US9492400B2 (en) | 2004-11-04 | 2016-11-15 | Massachusetts Institute Of Technology | Coated controlled release polymer particles as efficient oral delivery vehicles for biopharmaceuticals |
| US7947017B2 (en) | 2004-11-22 | 2011-05-24 | Intelliject, Inc. | Devices, systems and methods for medicament delivery |
| US10737028B2 (en) | 2004-11-22 | 2020-08-11 | Kaleo, Inc. | Devices, systems and methods for medicament delivery |
| AU2004325202B2 (en) | 2004-11-22 | 2009-02-19 | Kaleo, Inc. | Devices, systems, and methods for medicament delivery |
| US11590286B2 (en) | 2004-11-22 | 2023-02-28 | Kaleo, Inc. | Devices, systems and methods for medicament delivery |
| US7648483B2 (en) | 2004-11-22 | 2010-01-19 | Intelliject, Inc. | Devices, systems and methods for medicament delivery |
| US7648482B2 (en) * | 2004-11-22 | 2010-01-19 | Intelliject, Inc. | Devices, systems, and methods for medicament delivery |
| JP5216328B2 (en) | 2005-01-24 | 2013-06-19 | アンタレス ファーマ インコーポレイテッド | Pre-filled needle assist syringe jet injector |
| PL2058020T3 (en) | 2005-02-01 | 2013-03-29 | Kaleo Inc | Devices for medicament delivery |
| US7731686B2 (en) | 2005-02-01 | 2010-06-08 | Intelliject, Inc. | Devices, systems and methods for medicament delivery |
| US8231573B2 (en) | 2005-02-01 | 2012-07-31 | Intelliject, Inc. | Medicament delivery device having an electronic circuit system |
| US9022980B2 (en) | 2005-02-01 | 2015-05-05 | Kaleo, Inc. | Medical injector simulation device |
| US8206360B2 (en) | 2005-02-01 | 2012-06-26 | Intelliject, Inc. | Devices, systems and methods for medicament delivery |
| US8361026B2 (en) | 2005-02-01 | 2013-01-29 | Intelliject, Inc. | Apparatus and methods for self-administration of vaccines and other medicaments |
| EP1861122A1 (en) | 2005-03-23 | 2007-12-05 | GlaxoSmithKline Biologicals S.A. | Composition |
| MX2007012226A (en) | 2005-04-04 | 2007-12-10 | Univ Florida | Desferrithiocin polyether analogues. |
| PA8672101A1 (en) | 2005-04-29 | 2006-12-07 | Centocor Inc | ANTI-IL-6 ANTIBODIES, COMPOSITIONS, METHODS AND USES |
| US7611505B2 (en) * | 2005-05-10 | 2009-11-03 | Baxa Corporation | Sterile docking apparatus and method |
| EP1896073B1 (en) | 2005-06-30 | 2013-03-06 | Janssen Biotech, Inc. | Anti-il-23 antibodies, compositions, methods and uses |
| KR101446025B1 (en) | 2005-08-03 | 2014-10-01 | 아이바이오, 인크. | Compositions and methods for production of immunoglobulins |
| US8998881B2 (en) * | 2005-08-10 | 2015-04-07 | Alza Corporation | Method for delivering drugs to tissue under microjet propulsion |
| TWI457133B (en) | 2005-12-13 | 2014-10-21 | Glaxosmithkline Biolog Sa | Novel composition |
| US9267937B2 (en) | 2005-12-15 | 2016-02-23 | Massachusetts Institute Of Technology | System for screening particles |
| ES2707499T3 (en) | 2005-12-22 | 2019-04-03 | Glaxosmithkline Biologicals Sa | Pneumococcal polysaccharide conjugate vaccine |
| GB0607088D0 (en) | 2006-04-07 | 2006-05-17 | Glaxosmithkline Biolog Sa | Vaccine |
| HUE049832T2 (en) | 2005-12-29 | 2020-10-28 | Janssen Biotech Inc | Human anti-il-23 antibodies, compositions, method and uses |
| CA2642054C (en) | 2006-02-13 | 2017-11-21 | Fraunhofer Usa, Inc. | Influenza antigens, vaccine compositions, and related methods |
| US7666912B2 (en) | 2006-03-23 | 2010-02-23 | Massachusetts Eye And Ear Infirmary | Compositions and methods for reducing body fat |
| EP1998802A2 (en) | 2006-03-30 | 2008-12-10 | GlaxoSmithKline Biologicals S.A. | Immunogenic composition |
| CA2648035A1 (en) * | 2006-03-31 | 2007-10-11 | Centocor, Inc. | Human epo mimetic hinge core mimetibodies, compositions, methods and uses for preventing or treating glucose intolerance related conditions or renal disease associated anemia |
| ES2776100T3 (en) | 2006-03-31 | 2020-07-29 | Massachusetts Inst Technology | System for targeted delivery of therapeutic agents |
| US20070254381A1 (en) * | 2006-04-27 | 2007-11-01 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Monitoring and/or treating syringe mechanism |
| US8251947B2 (en) | 2006-05-03 | 2012-08-28 | Antares Pharma, Inc. | Two-stage reconstituting injector |
| US20070260174A1 (en) * | 2006-05-05 | 2007-11-08 | Searete Llc | Detecting a failure to maintain a regimen |
| CN101573141B (en) | 2006-05-15 | 2016-05-04 | 麻省理工学院 | For the polymer of functional particles |
| US9150626B2 (en) | 2006-06-02 | 2015-10-06 | President And Fellows Of Harvard College | Protein surface remodeling |
| WO2007150030A2 (en) | 2006-06-23 | 2007-12-27 | Massachusetts Institute Of Technology | Microfluidic synthesis of organic nanoparticles |
| EP2422810B1 (en) | 2006-07-17 | 2014-10-22 | GlaxoSmithKline Biologicals s.a. | Influenza vaccine |
| WO2008021367A2 (en) | 2006-08-11 | 2008-02-21 | President And Fellows Of Harvard College | Moenomycin biosynthesis-related compositions and methods of use thereof |
| DE202006018609U1 (en) * | 2006-08-29 | 2007-05-16 | Euro-Celtique S.A. | Needle-free apparatus for administrating pharmaceutical composition in humans, comprises a housing; auxiliary substance to force a pharmaceutical composition from a package into human body; a composition comprising analgesic, e.g. opioids |
| US7547293B2 (en) | 2006-10-06 | 2009-06-16 | Bioject, Inc. | Triggering mechanism for needle-free injector |
| JO3598B1 (en) | 2006-10-10 | 2020-07-05 | Infinity Discovery Inc | Boronic acids and esters as inhibitors of fatty acid amide hydrolase |
| PL2086582T3 (en) | 2006-10-12 | 2013-04-30 | Glaxosmithkline Biologicals Sa | Vaccine comprising an oil in water emulsion adjuvant |
| CN101522218B (en) | 2006-10-12 | 2012-09-26 | 葛兰素史密丝克莱恩生物有限公司 | Vaccine comprising an oil in water emulsion adjuvant |
| DE202006017522U1 (en) * | 2006-11-15 | 2007-01-18 | Perma-Tec Gmbh & Co. Kg | Lubricant dispenser has at least one tooth arranged on periphery of piston and pressing against inside wall of lubricant reservoir, and consists of harder material in comparison to lubricant reservoir |
| CA2671447A1 (en) | 2006-12-01 | 2008-06-12 | Anterios, Inc. | Amphiphilic entity nanoparticles |
| US20080140001A1 (en) * | 2006-12-12 | 2008-06-12 | By-Pass Inc. | Fluid Delivery Apparatus And Methods |
| TW200843794A (en) * | 2006-12-21 | 2008-11-16 | Centocor Inc | Use of long-acting GLP-1 receptor agonists to improve insulin sensitivity and lipid profiles |
| CN105622463B (en) | 2006-12-26 | 2019-02-22 | 兰休斯医疗成像公司 | For making the ligand of imaging cardiac innervation |
| US20080171968A1 (en) * | 2007-01-15 | 2008-07-17 | Bioject, Inc. | Methods of administering injectables to a joint with a needle-free injection system |
| EP2125075A2 (en) | 2007-01-22 | 2009-12-02 | Intelliject, Inc. | Medical injector with compliance tracking and monitoring |
| PT2118123E (en) | 2007-01-31 | 2016-02-10 | Harvard College | Stabilized p53 peptides and uses thereof |
| WO2008098165A2 (en) | 2007-02-09 | 2008-08-14 | Massachusetts Institute Of Technology | Oscillating cell culture bioreactor |
| WO2008103997A2 (en) * | 2007-02-23 | 2008-08-28 | Bioject Inc. | Needle-free injection devices and drug delivery systems therefor |
| WO2008115433A1 (en) | 2007-03-15 | 2008-09-25 | University Of Florida | Desferrithiocin polyether analogues |
| US7960139B2 (en) | 2007-03-23 | 2011-06-14 | Academia Sinica | Alkynyl sugar analogs for the labeling and visualization of glycoconjugates in cells |
| EP2508531B1 (en) | 2007-03-28 | 2016-10-19 | President and Fellows of Harvard College | Stitched polypeptides |
| WO2008124639A2 (en) | 2007-04-04 | 2008-10-16 | Massachusetts Institute Of Technology | Poly (amino acid) targeting moieties |
| US8778348B2 (en) | 2007-04-28 | 2014-07-15 | Ibio Inc. | Trypanosoma antigens, vaccine compositions, and related methods |
| WO2008156676A1 (en) | 2007-06-15 | 2008-12-24 | President And Fellows Of Harvard College | Methods and compositions for detecting and modulating o-glycosylation |
| RS54349B1 (en) | 2007-06-26 | 2016-02-29 | Glaxosmithkline Biologicals S.A. | Vaccine comprising streptococcus pneumoniae capsular polysaccharide conjugates |
| WO2009009759A2 (en) | 2007-07-11 | 2009-01-15 | Fraunhofer Usa, Inc. | Yersinia pestis antigens, vaccine compositions, and related methods |
| US8604004B2 (en) | 2007-10-04 | 2013-12-10 | President And Fellows Of Harvard College | Moenomycin analogs, methods of synthesis, and uses thereof |
| CN105770878A (en) | 2007-10-12 | 2016-07-20 | 麻省理工学院 | Vaccine Nanotechnology |
| PL2214699T3 (en) | 2007-11-02 | 2017-05-31 | Grifols Therapeutics Inc. | Method, composition, and article of manufacture for providing alpha-1 antitrypsin |
| US9533098B2 (en) | 2007-11-19 | 2017-01-03 | Painless Tech Gmbh | Injection device for the needle-free injection of a medium |
| CA2711330A1 (en) | 2008-01-03 | 2009-07-16 | Massachusetts Institute Of Technology | Decoy influenza therapies |
| US8193182B2 (en) | 2008-01-04 | 2012-06-05 | Intellikine, Inc. | Substituted isoquinolin-1(2H)-ones, and methods of use thereof |
| US20090212133A1 (en) * | 2008-01-25 | 2009-08-27 | Collins Jr James F | Ophthalmic fluid delivery device and method of operation |
| US8986253B2 (en) | 2008-01-25 | 2015-03-24 | Tandem Diabetes Care, Inc. | Two chamber pumps and related methods |
| WO2009126691A1 (en) | 2008-04-09 | 2009-10-15 | Infinity Pharmaceuticals, Inc | Inhibitors of fatty acid amide hydrolase |
| WO2009127676A1 (en) | 2008-04-16 | 2009-10-22 | Glaxosmithkline Biologicals S.A. | Vaccine |
| USD994111S1 (en) | 2008-05-12 | 2023-08-01 | Kaleo, Inc. | Medicament delivery device cover |
| US8021344B2 (en) | 2008-07-28 | 2011-09-20 | Intelliject, Inc. | Medicament delivery device configured to produce an audible output |
| US20090291986A1 (en) | 2008-05-22 | 2009-11-26 | Apostolos Pappas | Composition and method of treating facial skin defect |
| CN105147608B (en) | 2008-06-26 | 2019-12-10 | 安特里奥公司 | Dermal delivery |
| US8680020B2 (en) | 2008-07-15 | 2014-03-25 | Academia Sinica | Glycan arrays on PTFE-like aluminum coated glass slides and related methods |
| US20110144306A1 (en) | 2008-07-23 | 2011-06-16 | President And Fellows Of Harvard College | Ligation of stapled polypeptides |
| JP5611208B2 (en) | 2008-08-05 | 2014-10-22 | アンタレス・ファーマ・インコーポレーテッド | Multiple dose injection device |
| CA2733642A1 (en) | 2008-08-14 | 2010-02-18 | Cephalon Australia Pty Ltd | Anti-il-12/il-23 antibodies |
| US8408421B2 (en) | 2008-09-16 | 2013-04-02 | Tandem Diabetes Care, Inc. | Flow regulating stopcocks and related methods |
| US8650937B2 (en) | 2008-09-19 | 2014-02-18 | Tandem Diabetes Care, Inc. | Solute concentration measurement device and related methods |
| US9206223B2 (en) | 2008-09-22 | 2015-12-08 | Aileron Therapeutics, Inc. | Methods for preparing purified polypeptide compositions |
| US8663196B2 (en) * | 2008-09-23 | 2014-03-04 | Kassab Kughn Endovascular Devices Llc | Endovascular sheath with gradable stiffness device and method |
| DE102008048595A1 (en) | 2008-09-23 | 2010-04-01 | Lts Lohmann Therapie-Systeme Ag | Disposable injector with high injection safety |
| WO2010037046A1 (en) | 2008-09-28 | 2010-04-01 | Fraunhofer Usa, Inc. | Humanized neuraminidase antibody and methods of use thereof |
| US8343498B2 (en) | 2008-10-12 | 2013-01-01 | Massachusetts Institute Of Technology | Adjuvant incorporation in immunonanotherapeutics |
| US8343497B2 (en) | 2008-10-12 | 2013-01-01 | The Brigham And Women's Hospital, Inc. | Targeting of antigen presenting cells with immunonanotherapeutics |
| US8591905B2 (en) | 2008-10-12 | 2013-11-26 | The Brigham And Women's Hospital, Inc. | Nicotine immunonanotherapeutics |
| US8277812B2 (en) | 2008-10-12 | 2012-10-02 | Massachusetts Institute Of Technology | Immunonanotherapeutics that provide IgG humoral response without T-cell antigen |
| BRPI0919881B1 (en) | 2008-10-31 | 2021-09-08 | Centocor Ortho Biotech Inc | FRAMEWORK PROTEIN AND ITS GENERATION METHOD, LIBRARY AND ITS CONSTRUCTION METHOD, NUCLEIC ACID MOLECULE, NUCLEIC ACID VECTOR, HOST CELL, COMPOSITION, MEDICAL DEVICE AND MANUFACTURING ARTICLE |
| CA2743904A1 (en) | 2008-11-17 | 2010-05-20 | The Regents Of The University Of Michigan | Cancer vaccine compositions and methods of using the same |
| EP2376619A4 (en) | 2008-12-15 | 2012-07-04 | Greenlight Biosciences Inc | Methods for control of flux in metabolic pathways |
| CN102256615A (en) | 2009-01-14 | 2011-11-23 | 爱勒让治疗公司 | Peptidomimetic macrocycles |
| EP2396011B1 (en) | 2009-02-12 | 2016-04-13 | Janssen Biotech, Inc. | Fibronectin type iii domain based scaffold compositions, methods and uses |
| WO2010108116A1 (en) | 2009-03-20 | 2010-09-23 | Antares Pharma, Inc. | Hazardous agent injection system |
| IL197761A0 (en) * | 2009-03-23 | 2009-12-24 | Moshe Zalsman | Capsule for mixing together two flowable materials, and kits including such capsules, particularly useful in dentistry |
| JP2012525146A (en) | 2009-04-28 | 2012-10-22 | プレジデント アンド フェロウズ オブ ハーバード カレッジ | Overcharged protein for cell penetration |
| US9149465B2 (en) | 2009-05-18 | 2015-10-06 | Infinity Pharmaceuticals, Inc. | Isoxazolines as inhibitors of fatty acid amide hydrolase |
| US8765735B2 (en) | 2009-05-18 | 2014-07-01 | Infinity Pharmaceuticals, Inc. | Isoxazolines as inhibitors of fatty acid amide hydrolase |
| US8927551B2 (en) | 2009-05-18 | 2015-01-06 | Infinity Pharmaceuticals, Inc. | Isoxazolines as inhibitors of fatty acid amide hydrolase |
| WO2010141074A2 (en) | 2009-06-01 | 2010-12-09 | President And Fellows Of Harvard College | O-glcnac transferase inhibitors and uses thereof |
| US9163330B2 (en) | 2009-07-13 | 2015-10-20 | President And Fellows Of Harvard College | Bifunctional stapled polypeptides and uses thereof |
| EP3284494A1 (en) | 2009-07-30 | 2018-02-21 | Tandem Diabetes Care, Inc. | Portable infusion pump system |
| GB0913681D0 (en) | 2009-08-05 | 2009-09-16 | Glaxosmithkline Biolog Sa | Immunogenic composition |
| EP2298390A1 (en) * | 2009-08-28 | 2011-03-23 | Sanofi-Aventis Deutschland GmbH | Medical delivery device, housing cap for a medical delivery device and drive mechanism for a medical delivery device |
| CA2774973A1 (en) | 2009-09-22 | 2011-03-31 | Aileron Therapeutics, Inc. | Peptidomimetic macrocycles |
| CA2776144C (en) | 2009-09-29 | 2020-10-27 | Fraunhofer Usa, Inc. | Influenza hemagglutinin antibodies, compositions, and related methods |
| US20140200511A1 (en) * | 2009-10-30 | 2014-07-17 | Searete Llc | Systems, devices, and methods for making or administering frozen particles |
| US11377485B2 (en) | 2009-12-02 | 2022-07-05 | Academia Sinica | Methods for modifying human antibodies by glycan engineering |
| US10087236B2 (en) | 2009-12-02 | 2018-10-02 | Academia Sinica | Methods for modifying human antibodies by glycan engineering |
| WO2011094445A1 (en) | 2010-01-27 | 2011-08-04 | Massachusetts Institute Of Technology | Engineered polypeptide agents for targeted broad spectrum influenza neutralization |
| KR101888026B1 (en) | 2010-02-03 | 2018-08-13 | 인피니티 파마슈티컬스, 인코포레이티드 | Fatty acid amide hydrolase inhibitors |
| WO2011098518A2 (en) * | 2010-02-11 | 2011-08-18 | Ablynx Nv | Delivery of immunoglobulin variable domains and constructs thereof |
| CN102844023B (en) | 2010-03-08 | 2016-01-20 | 索隆-基特林癌症研究协会 | CDC7 inhibitors of kinases with and uses thereof |
| GB201003922D0 (en) | 2010-03-09 | 2010-04-21 | Glaxosmithkline Biolog Sa | Conjugation process |
| GB201003920D0 (en) | 2010-03-09 | 2010-04-21 | Glaxosmithkline Biolog Sa | Method of treatment |
| WO2011119549A1 (en) | 2010-03-22 | 2011-09-29 | President And Fellows Of Harvard College | Trioxacarcins and uses thereof |
| WO2011130332A1 (en) | 2010-04-12 | 2011-10-20 | Academia Sinica | Glycan arrays for high throughput screening of viruses |
| EP2566853B1 (en) | 2010-05-05 | 2017-01-25 | Infinity Pharmaceuticals, Inc. | Tetrazolones as inhibitors of fatty acid synthase |
| US8450350B2 (en) | 2010-05-05 | 2013-05-28 | Infinity Pharmaceuticals, Inc. | Triazoles as inhibitors of fatty acid synthase |
| DK2566953T3 (en) | 2010-05-07 | 2019-04-15 | Greenlight Biosciences Inc | METHODS OF MANAGING THE POWER BY METABOLIC ROADS USING ENZYMOUS LOCATION |
| RU2019142507A (en) | 2010-05-11 | 2020-08-24 | Лантеус Медикал Имэджинг, Инк. | COMPOSITIONS, METHODS AND SYSTEMS FOR SYNTHESIS AND APPLICATION OF VISUALIZING AGENTS |
| CN103180318B (en) | 2010-05-14 | 2017-05-10 | 达那-法伯癌症研究所 | male contraceptive compositions and methods of use |
| US9193989B2 (en) | 2010-06-18 | 2015-11-24 | Taiho Pharmaceutical Co., Ltd. | PRPK-TPRKB modulators and uses thereof |
| AU2011268110B2 (en) | 2010-06-19 | 2016-05-19 | Memorial Sloan-Kettering Cancer Center | Anti-GD2 antibodies |
| US10154923B2 (en) | 2010-07-15 | 2018-12-18 | Eyenovia, Inc. | Drop generating device |
| ES2787254T3 (en) | 2010-07-15 | 2020-10-15 | Eyenovia Inc | Supply of ophthalmic drugs |
| JP2013531548A (en) | 2010-07-15 | 2013-08-08 | コリンシアン オフサルミック，インコーポレイティド | Method and system for performing teletherapy and remote monitoring |
| JP5964826B2 (en) | 2010-07-15 | 2016-08-03 | アイノビア，インコーポレイティド | Drop generation device |
| CA2807552A1 (en) | 2010-08-06 | 2012-02-09 | Moderna Therapeutics, Inc. | Engineered nucleic acids and methods of use thereof |
| CA2807685C (en) | 2010-08-13 | 2020-10-06 | Aileron Therapeutics, Inc. | P53 derived peptidomimetic macrocycle |
| CA2809284C (en) | 2010-08-31 | 2021-02-23 | Greenlight Biosciences, Inc. | Methods for control of flux in metabolic pathways through protease manipulation |
| US8802110B2 (en) | 2010-09-21 | 2014-08-12 | Massachusetts Institute Of Technology | Influenza treatment and/or characterization, human-adapted HA polypeptides; vaccines |
| US8957026B2 (en) | 2010-09-22 | 2015-02-17 | President And Fellows Of Harvard College | Beta-catenin targeting peptides and uses thereof |
| ES2862955T3 (en) | 2010-10-01 | 2021-10-08 | Modernatx Inc | Manipulated nucleic acids and methods of using them |
| RU2663718C2 (en) | 2010-10-04 | 2018-08-08 | Массачусетс Инститьют Оф Текнолоджи | Hemagglutinin polypeptides, and reagents and methods relating thereto |
| CA2817577A1 (en) | 2010-11-10 | 2012-05-18 | Infinity Pharmaceuticals, Inc. | Heterocyclic compounds and uses thereof |
| GB201021716D0 (en) * | 2010-12-22 | 2011-02-02 | Owen Mumford Ltd | Autoinjectors |
| AU2012205735B8 (en) * | 2011-01-10 | 2014-09-18 | Zogenix, Inc. | Needle free injectors |
| DK2663309T3 (en) | 2011-01-10 | 2017-06-19 | Infinity Pharmaceuticals Inc | METHODS FOR PRODUCING ISOQUINOLINONES AND SOLID FORMS OF ISOQUINOLINONES |
| WO2012099942A2 (en) | 2011-01-19 | 2012-07-26 | Terakine Therapeutics, Inc. | Methods and compositions for treating metabolic syndrome |
| JP2014503586A (en) | 2011-01-24 | 2014-02-13 | アンテリオス， インコーポレイテッド | Oil composition |
| BR112013018920A2 (en) | 2011-01-24 | 2017-11-28 | Anterios Inc | nanoparticle compositions, formulations thereof and their uses |
| CN103747782A (en) | 2011-01-24 | 2014-04-23 | 安特里奥公司 | Nanoparticle compositions |
| US9173999B2 (en) | 2011-01-26 | 2015-11-03 | Kaleo, Inc. | Devices and methods for delivering medicaments from a multi-chamber container |
| US8939943B2 (en) | 2011-01-26 | 2015-01-27 | Kaleo, Inc. | Medicament delivery device for administration of opioid antagonists including formulations for naloxone |
| US8627816B2 (en) | 2011-02-28 | 2014-01-14 | Intelliject, Inc. | Medicament delivery device for administration of opioid antagonists including formulations for naloxone |
| KR20140010126A (en) | 2011-03-03 | 2014-01-23 | 터서스 파마수티칼 엘엘씨 | Compositions and methods comprising c16:1n7-palmitoleate |
| GB201103836D0 (en) | 2011-03-07 | 2011-04-20 | Glaxosmithkline Biolog Sa | Conjugation process |
| US9193767B2 (en) | 2011-03-30 | 2015-11-24 | Brown University | Enopeptins, uses thereof, and methods of synthesis thereto |
| US8710200B2 (en) | 2011-03-31 | 2014-04-29 | Moderna Therapeutics, Inc. | Engineered nucleic acids encoding a modified erythropoietin and their expression |
| UY34073A (en) | 2011-05-17 | 2013-01-03 | Glaxosmithkline Biolog Sa | IMPROVED VACCINE OF STREPTOCOCCUS PNEUMONIAE AND PREPARATION METHODS. |
| FR2976568B1 (en) * | 2011-06-14 | 2014-09-05 | Valois Sas | DEVICE FOR DISPENSING FLUID PRODUCT. |
| CA2840224C (en) | 2011-06-22 | 2019-08-13 | The General Hospital Corporation | Treatment of proteinopathies |
| US8672883B2 (en) | 2011-07-11 | 2014-03-18 | C. Garyen Denning | Fluid delivery device and methods |
| US9220660B2 (en) | 2011-07-15 | 2015-12-29 | Antares Pharma, Inc. | Liquid-transfer adapter beveled spike |
| US8496619B2 (en) | 2011-07-15 | 2013-07-30 | Antares Pharma, Inc. | Injection device with cammed ram assembly |
| AU2012284088B2 (en) | 2011-07-19 | 2015-10-08 | Infinity Pharmaceuticals Inc. | Heterocyclic compounds and uses thereof |
| MX2014000648A (en) | 2011-07-19 | 2014-09-25 | Infinity Pharmaceuticals Inc | Heterocyclic compounds and uses thereof. |
| RS58438B1 (en) | 2011-07-22 | 2019-04-30 | Massachusetts Inst Technology | Activators of class i histone deacetlyases (hdacs) and uses thereof |
| KR20140075693A (en) | 2011-08-29 | 2014-06-19 | 인피니티 파마슈티칼스, 인코포레이티드 | Heterocyclic compounds and uses thereof |
| DK2753605T3 (en) | 2011-09-09 | 2019-06-17 | Lantheus Medical Imaging Inc | COMPOSITIONS, METHODS AND SYSTEMS FOR THE SYNTHESIS AND THE APPLICATION OF IMAGE CRAFTS |
| JP2014526250A (en) | 2011-09-09 | 2014-10-06 | グリーンライト バイオサイエンシーズ インコーポレーテッド | Cell-free preparation of carbapenem |
| EP3384938A1 (en) | 2011-09-12 | 2018-10-10 | Moderna Therapeutics, Inc. | Engineered nucleic acids and methods of use thereof |
| US9630979B2 (en) | 2011-09-29 | 2017-04-25 | Infinity Pharmaceuticals, Inc. | Inhibitors of monoacylglycerol lipase and methods of their use |
| WO2013052523A1 (en) | 2011-10-03 | 2013-04-11 | modeRNA Therapeutics | Modified nucleosides, nucleotides, and nucleic acids, and uses thereof |
| TWI643868B (en) | 2011-10-18 | 2018-12-11 | 艾利倫治療公司 | Peptidomimetic macrocycles |
| EP2822935B1 (en) | 2011-11-17 | 2019-05-15 | Dana-Farber Cancer Institute, Inc. | Inhibitors of c-jun-n-terminal kinase (jnk) |
| GB201119999D0 (en) | 2011-11-20 | 2012-01-04 | Glaxosmithkline Biolog Sa | Vaccine |
| GB201120000D0 (en) | 2011-11-20 | 2012-01-04 | Glaxosmithkline Biolog Sa | Vaccine |
| EP2790620A1 (en) | 2011-12-12 | 2014-10-22 | Corinthian Ophthalmic, Inc. | High modulus polymeric ejector mechanism, ejector device, and methods of use |
| CN104114572A (en) | 2011-12-16 | 2014-10-22 | 现代治疗公司 | Modified nucleoside, nucleotide, and nucleic acid compositions |
| US8426471B1 (en) | 2011-12-19 | 2013-04-23 | Topokine Therapeutics, Inc. | Methods and compositions for reducing body fat and adipocytes |
| MX362492B (en) | 2012-02-15 | 2019-01-21 | Aileron Therapeutics Inc | Peptidomimetic macrocycles. |
| US8987414B2 (en) | 2012-02-15 | 2015-03-24 | Aileron Therapeutics, Inc. | Triazole-crosslinked and thioether-crosslinked peptidomimetic macrocycles |
| KR20150011346A (en) | 2012-04-06 | 2015-01-30 | 안타레스 팔마, 인코퍼레이티드 | Needle assisted jet injection administration of testosterone compositions |
| EP2834254A2 (en) | 2012-04-06 | 2015-02-11 | President and Fellows of Harvard College | Moenomycin analogs, methods of synthesis, and uses thereof |
| WO2013151697A1 (en) | 2012-04-06 | 2013-10-10 | President And Fellows Of Harvard College | Methods and compounds for identifying glycosyltransferase inhibitors |
| EP2850090B1 (en) | 2012-04-06 | 2018-10-03 | President and Fellows of Harvard College | Chemoenzymatic methods for synthesizing moenomycin analogs |
| US8940742B2 (en) | 2012-04-10 | 2015-01-27 | Infinity Pharmaceuticals, Inc. | Heterocyclic compounds and uses thereof |
| US10130714B2 (en) | 2012-04-14 | 2018-11-20 | Academia Sinica | Enhanced anti-influenza agents conjugated with anti-inflammatory activity |
| US9597385B2 (en) | 2012-04-23 | 2017-03-21 | Allertein Therapeutics, Llc | Nanoparticles for treatment of allergy |
| US9364610B2 (en) | 2012-05-07 | 2016-06-14 | Antares Pharma, Inc. | Injection device with cammed ram assembly |
| BR112014027991A2 (en) | 2012-05-10 | 2017-07-18 | Massachusetts Inst Technology | agents for neutralizing influenza |
| US9180242B2 (en) | 2012-05-17 | 2015-11-10 | Tandem Diabetes Care, Inc. | Methods and devices for multiple fluid transfer |
| US9522235B2 (en) | 2012-05-22 | 2016-12-20 | Kaleo, Inc. | Devices and methods for delivering medicaments from a multi-chamber container |
| US20140037680A1 (en) | 2012-08-06 | 2014-02-06 | Glaxosmithkline Biologicals, S.A. | Novel method |
| WO2014024026A1 (en) | 2012-08-06 | 2014-02-13 | Glaxosmithkline Biologicals S.A. | Method for eliciting in infants an immune response against rsv and b. pertussis |
| AU2013203000B9 (en) | 2012-08-10 | 2017-02-02 | Lantheus Medical Imaging, Inc. | Compositions, methods, and systems for the synthesis and use of imaging agents |
| CA2880701A1 (en) | 2012-08-18 | 2014-02-27 | Academia Sinica | Cell-permeable probes for identification and imaging of sialidases |
| WO2014042930A1 (en) * | 2012-09-17 | 2014-03-20 | Hns International, Inc. | Needleless hypodermic injector and related method |
| WO2014052647A2 (en) | 2012-09-26 | 2014-04-03 | President And Fellows Of Harvard College | Proline-locked stapled peptides and uses thereof |
| US20150225471A1 (en) | 2012-10-01 | 2015-08-13 | President And Fellows Of Harvard College | Stabilized polypeptide insulin receptor modulators |
| ES2719776T3 (en) | 2012-10-12 | 2019-07-16 | Broad Inst Inc | GSK3 inhibitors and methods of use thereof |
| EP2909194A1 (en) | 2012-10-18 | 2015-08-26 | Dana-Farber Cancer Institute, Inc. | Inhibitors of cyclin-dependent kinase 7 (cdk7) |
| USRE48175E1 (en) | 2012-10-19 | 2020-08-25 | Dana-Farber Cancer Institute, Inc. | Hydrophobically tagged small molecules as inducers of protein degradation |
| US20140114248A1 (en) * | 2012-10-24 | 2014-04-24 | Nuance Designs, LLC | Power pack for an autoinjector |
| DK2914296T4 (en) | 2012-11-01 | 2022-01-03 | Infinity Pharmaceuticals Inc | Treatment of cancers using PI3 kinase isoform modulators |
| EP2914256B1 (en) | 2012-11-01 | 2019-07-31 | Aileron Therapeutics, Inc. | Disubstituted amino acids and methods of preparation and use thereof |
| EP2917203B1 (en) | 2012-11-02 | 2019-04-03 | Dana-Farber Cancer Institute, Inc. | Method for identifying myc inhibitors |
| KR101651448B1 (en) | 2012-11-21 | 2016-08-26 | 토포카인 쎄라퓨틱스, 인코포레이티드 | Methods and compositions for locally increasing body fat |
| JP6408478B2 (en) | 2012-11-26 | 2018-10-17 | プレジデント アンド フェローズ オブ ハーバード カレッジ | Trioxacalcin, trioxacalcin-antibody complex and use thereof |
| PL2922554T3 (en) | 2012-11-26 | 2022-06-20 | Modernatx, Inc. | Terminally modified rna |
| WO2014100695A1 (en) | 2012-12-21 | 2014-06-26 | Epizyme, Inc. | Prmt5 inhibitors and uses thereof |
| US9745291B2 (en) | 2012-12-21 | 2017-08-29 | Epizyme, Inc. | PRMT5 inhibitors containing a dihydro- or tetrahydroisoquinoline and uses thereof |
| MX2015008052A (en) | 2012-12-21 | 2016-08-18 | Epizyme Inc | Teatrahydro- and dihydro-isoquinoline prmt5 inhibitors and uses thereof. |
| JP2016505001A (en) | 2012-12-21 | 2016-02-18 | エピザイム，インコーポレイティド | PRMT5 inhibitors and uses thereof |
| CA2896708A1 (en) | 2012-12-27 | 2014-07-03 | Kaleo, Inc. | Devices, systems and methods for locating and interacting with medicament delivery systems |
| EP2946014A2 (en) | 2013-01-17 | 2015-11-25 | Moderna Therapeutics, Inc. | Signal-sensor polynucleotides for the alteration of cellular phenotypes |
| US20140335504A1 (en) | 2013-02-07 | 2014-11-13 | Massachusetts Institute Of Technology | Human adaptation of h5 influenza |
| CA2900008A1 (en) | 2013-02-07 | 2014-08-14 | Children's Medical Center Corporation | Protein antigens that provide protection against pneumococcal colonization and/or disease |
| EP4349383A2 (en) | 2013-02-11 | 2024-04-10 | Antares Pharma, Inc. | Needle assisted jet injection device having reduced trigger force |
| EP2968792B1 (en) | 2013-03-11 | 2019-05-15 | Antares Pharma, Inc. | Dosage injector with pinion system |
| US20160024181A1 (en) | 2013-03-13 | 2016-01-28 | Moderna Therapeutics, Inc. | Long-lived polynucleotide molecules |
| US10081654B2 (en) | 2013-03-13 | 2018-09-25 | President And Fellows Of Harvard College | Stapled and stitched polypeptides and uses thereof |
| US9173998B2 (en) | 2013-03-14 | 2015-11-03 | Tandem Diabetes Care, Inc. | System and method for detecting occlusions in an infusion pump |
| EP2970194A1 (en) | 2013-03-15 | 2016-01-20 | Infinity Pharmaceuticals, Inc. | Salts and solid forms of isoquinolinones and composition comprising and methods of using the same |
| KR102207859B1 (en) | 2013-03-15 | 2021-01-27 | 메모리얼 슬로안 케터링 캔서 센터 | High affinity anti-gd2 antibodies |
| KR102233251B1 (en) | 2013-04-03 | 2021-03-26 | 엔-폴드 엘엘씨 | Novel nanoparticle compositions |
| EP2988597B1 (en) | 2013-04-04 | 2022-06-08 | President and Fellows of Harvard College | Macrolides and methods of their preparation and use |
| ES2774330T3 (en) | 2013-04-09 | 2020-07-20 | Massachusetts Inst Technology | Drug supply polymer and uses thereof |
| WO2014179464A1 (en) | 2013-04-30 | 2014-11-06 | Massachusetts Institute Of Technology | Human adaptation of h3 influenza |
| WO2014179562A1 (en) | 2013-05-01 | 2014-11-06 | Massachusetts Institute Of Technology | 1,3,5-triazinane-2,4,6-trione derivatives and uses thereof |
| NO2753788T3 (en) | 2013-05-10 | 2018-06-16 | ||
| WO2014186504A1 (en) | 2013-05-15 | 2014-11-20 | Topokine Therapeutics, Inc. | Methods and compositions for topical delivery of prostaglandins to subcutaneous fat |
| DK3003309T3 (en) | 2013-05-30 | 2020-12-14 | Infinity Pharmaceuticals Inc | Treatment of cancer with PI3 kinase isoform modulators |
| US10526375B2 (en) | 2013-06-05 | 2020-01-07 | Massachusetts Institute Of Technology | Human Adaptation of H7 HA |
| US9212145B2 (en) | 2013-06-11 | 2015-12-15 | Kala Pharmaceuticals, Inc. | Urea derivatives and uses thereof |
| AU2014278005B2 (en) | 2013-06-14 | 2018-11-22 | President And Fellows Of Harvard College | Stabilized polypeptide insulin receptor modulators |
| WO2014210397A1 (en) | 2013-06-26 | 2014-12-31 | Academia Sinica | Rm2 antigens and use thereof |
| US9981030B2 (en) | 2013-06-27 | 2018-05-29 | Academia Sinica | Glycan conjugates and use thereof |
| EP3024327B1 (en) | 2013-07-25 | 2019-09-04 | Dana-Farber Cancer Institute, Inc. | Inhibitors of transcription factors and uses thereof |
| EP3030260A1 (en) | 2013-08-05 | 2016-06-15 | GlaxoSmithKline Biologicals S.A. | Combination immunogenic compositions |
| WO2015021058A2 (en) | 2013-08-05 | 2015-02-12 | Greenlight Biosciences, Inc. | Engineered proteins with a protease cleavage site |
| CA2923579C (en) | 2013-09-06 | 2023-09-05 | Academia Sinica | Human inkt cell activation using glycolipids with altered glycosyl groups |
| WO2015051241A1 (en) | 2013-10-04 | 2015-04-09 | Infinity Pharmaceuticals, Inc. | Heterocyclic compounds and uses thereof |
| NZ718430A (en) | 2013-10-04 | 2021-12-24 | Infinity Pharmaceuticals Inc | Heterocyclic compounds and uses thereof |
| WO2015057894A1 (en) | 2013-10-15 | 2015-04-23 | Massachusetts Institute Of Technology | Methods for treating polycystic kidney disease and polycystic liver disease |
| US9902986B2 (en) | 2013-10-16 | 2018-02-27 | Massachusetts Institute Of Technology | Enterobactin conjugates and uses thereof |
| JP6491202B2 (en) | 2013-10-18 | 2019-03-27 | デイナ ファーバー キャンサー インスティチュート，インコーポレイテッド | Polycyclic inhibitors of cyclin dependent kinase 7 (CDK 7) |
| US20160244452A1 (en) | 2013-10-21 | 2016-08-25 | Infinity Pharmaceuticals, Inc. | Heterocyclic compounds and uses thereof |
| AU2014342042B2 (en) | 2013-11-01 | 2017-08-17 | KALA BIO, Inc. | Crystalline forms of therapeutic compounds and uses thereof |
| US11446309B2 (en) | 2013-11-08 | 2022-09-20 | Dana-Farber Cancer Institute, Inc. | Combination therapy for cancer using bromodomain and extra-terminal (BET) protein inhibitors |
| US20160243544A1 (en) * | 2013-11-14 | 2016-08-25 | Abon Biopharm (Hangzhou) Co., Ltd. | A device and method for using the device |
| CN106103452B (en) | 2013-12-24 | 2019-05-21 | 哈佛学院院长等 | Cortex chalone analog and its synthesis and purposes |
| US10150818B2 (en) | 2014-01-16 | 2018-12-11 | Academia Sinica | Compositions and methods for treatment and detection of cancers |
| TW201620939A (en) | 2014-01-16 | 2016-06-16 | 中央研究院 | Compositions and methods for treatment and detection of cancers |
| US10793571B2 (en) | 2014-01-31 | 2020-10-06 | Dana-Farber Cancer Institute, Inc. | Uses of diazepane derivatives |
| JP2017506666A (en) | 2014-02-28 | 2017-03-09 | テンシャ セラピューティクス，インコーポレイテッド | Treatment of symptoms related to hyperinsulinemia |
| WO2015134920A1 (en) | 2014-03-07 | 2015-09-11 | The Arizona Board Of Regents On Behalf Of The University Of Arizona | Non-narcotic crmp2 peptides targeting sodium channels for chronic pain |
| JP6296840B2 (en) * | 2014-03-11 | 2018-03-20 | テルモ株式会社 | Liquid dosing device |
| JP6262030B2 (en) * | 2014-03-11 | 2018-01-17 | テルモ株式会社 | Liquid dosing device |
| EA201691872A1 (en) | 2014-03-19 | 2017-04-28 | Инфинити Фармасьютикалз, Инк. | HETEROCYCLIC COMPOUNDS FOR APPLICATION IN THE TREATMENT OF PI3K-GAMMA-MEDIATED DISORDERS |
| JP6562942B2 (en) | 2014-03-27 | 2019-08-28 | アカデミア シニカＡｃａｄｅｍｉａ Ｓｉｎｉｃａ | Reactive labeled compounds and uses thereof |
| CN106456735B (en) | 2014-03-28 | 2021-06-29 | 华盛顿大学商业中心 | Breast and ovarian cancer vaccines |
| WO2015168079A1 (en) | 2014-04-29 | 2015-11-05 | Infinity Pharmaceuticals, Inc. | Pyrimidine or pyridine derivatives useful as pi3k inhibitors |
| US10039816B2 (en) | 2014-04-30 | 2018-08-07 | Massachusetts Institute Of Technology | Siderophore-based immunization against gram-negative bacteria |
| WO2015179635A2 (en) | 2014-05-21 | 2015-11-26 | President And Fellows Of Harvard College | Ras inhibitory peptides and uses thereof |
| JP2017518989A (en) | 2014-05-27 | 2017-07-13 | アカデミア シニカＡｃａｄｅｍｉａ Ｓｉｎｉｃａ | Anti-CD20 glycoengineered antibody group and use thereof |
| WO2015184008A1 (en) | 2014-05-27 | 2015-12-03 | Academia Sinica | Fucosidase from bacteroides and methods using the same |
| US10118969B2 (en) | 2014-05-27 | 2018-11-06 | Academia Sinica | Compositions and methods relating to universal glycoforms for enhanced antibody efficacy |
| AU2015267045B2 (en) | 2014-05-27 | 2021-02-25 | Academia Sinica | Anti-HER2 glycoantibodies and uses thereof |
| TWI732738B (en) | 2014-05-28 | 2021-07-11 | 中央研究院 | Anti-tnf-alpha glycoantibodies and uses thereof |
| WO2015187802A1 (en) | 2014-06-03 | 2015-12-10 | Amgen Inc. | Devices and methods for assisting a user of a drug delivery device |
| JP6664338B2 (en) | 2014-06-13 | 2020-03-13 | グラクソスミスクライン バイオロジカルズ ソシエテ アノニム | Immunogenic combination |
| CN106559991B (en) | 2014-06-19 | 2019-09-20 | 阿里亚德医药股份有限公司 | Heteroaryl compound for kinase inhibition |
| WO2015200425A1 (en) | 2014-06-27 | 2015-12-30 | Topokine Therapeutics, Inc. | Topical dosage regimen |
| EP3164379A1 (en) | 2014-07-02 | 2017-05-10 | Massachusetts Institute of Technology | Polyamine-fatty acid derived lipidoids and uses thereof |
| US10182906B2 (en) * | 2014-07-15 | 2019-01-22 | Alcon Pharmaceuticals, Ltd. | Intraocular lens inserter with temperature compensation |
| US9517307B2 (en) | 2014-07-18 | 2016-12-13 | Kaleo, Inc. | Devices and methods for delivering opioid antagonists including formulations for naloxone |
| WO2016011386A1 (en) | 2014-07-18 | 2016-01-21 | University Of Washington | Cancer vaccine compositions and methods of use thereof |
| US10736966B2 (en) | 2014-08-12 | 2020-08-11 | Massachusetts Institute Of Technology | Brush-poly (glycoamidoamine)-lipids and uses thereof |
| CN104162207A (en) * | 2014-08-27 | 2014-11-26 | 苏州承乐电子科技有限公司 | Continuous type needleless injector |
| CA2960712A1 (en) | 2014-09-08 | 2016-03-17 | Academia Sinica | Human inkt cell activation using glycolipids |
| CN107106642B (en) | 2014-09-24 | 2021-02-26 | 艾瑞朗医疗公司 | Peptidomimetic macrocycles and formulations thereof |
| SG10201902594QA (en) | 2014-09-24 | 2019-04-29 | Aileron Therapeutics Inc | Peptidomimetic macrocycles and uses thereof |
| US9708348B2 (en) | 2014-10-03 | 2017-07-18 | Infinity Pharmaceuticals, Inc. | Trisubstituted bicyclic heterocyclic compounds with kinase activities and uses thereof |
| AU2015335950B2 (en) | 2014-10-21 | 2018-01-25 | Takeda Pharmaceutical Company Limited | Crystalline forms of 5-chloro-N4-[-2-(dimethylphosphoryl) phenyl]-N2-{2-methoxy-4-[4-(4-methylpiperazin-1-yl) piperidin-1-yl] phenyl}pyrimidine-2,4-diamine |
| CA2965330A1 (en) | 2014-10-27 | 2016-05-06 | Tensha Therapeutics, Inc. | Bromodomain inhibitors |
| JP2017533238A (en) | 2014-10-28 | 2017-11-09 | アンスティチュ ナショナル ドゥ ラ サンテ エ ドゥ ラ ルシェルシュ メディカル | Compositions and methods for antigen-specific tolerance |
| WO2016077125A1 (en) | 2014-11-10 | 2016-05-19 | Moderna Therapeutics, Inc. | Alternative nucleic acid molecules containing reduced uracil content and uses thereof |
| WO2016086026A1 (en) | 2014-11-26 | 2016-06-02 | Kala Pharmaceuticals, Inc. | Crystalline forms of a therapeutic compound and uses thereof |
| US10174022B2 (en) | 2014-12-10 | 2019-01-08 | Kala Pharmaceuticals, Inc. | 1-amino-triazolo(1,5-A)pyridine-substituted urea derivative and uses thereof |
| ES2785311T3 (en) | 2014-12-19 | 2020-10-06 | Amgen Inc | Mobile button drug delivery device or user interface field |
| US10799630B2 (en) | 2014-12-19 | 2020-10-13 | Amgen Inc. | Drug delivery device with proximity sensor |
| US10314815B2 (en) | 2014-12-23 | 2019-06-11 | Sloan-Kettering Institute For Cancer Research | Polymorph of granaticin B |
| US9975965B2 (en) | 2015-01-16 | 2018-05-22 | Academia Sinica | Compositions and methods for treatment and detection of cancers |
| US10495645B2 (en) | 2015-01-16 | 2019-12-03 | Academia Sinica | Cancer markers and methods of use thereof |
| JP6779887B2 (en) | 2015-01-24 | 2020-11-04 | アカデミア シニカＡｃａｄｅｍｉａ Ｓｉｎｉｃａ | New glycan conjugate and how to use it |
| KR102618312B1 (en) | 2015-03-17 | 2023-12-28 | 메모리얼 슬로안 케터링 캔서 센터 | Anti-MUC16 antibody and use thereof |
| AU2016235424A1 (en) | 2015-03-20 | 2017-10-05 | Aileron Therapeutics, Inc. | Peptidomimetic macrocycles and uses thereof |
| CA2980004C (en) | 2015-03-24 | 2023-10-10 | Kaleo, Inc. | Devices and methods for delivering a lyophilized medicament |
| JP6861166B2 (en) | 2015-03-27 | 2021-04-21 | ダナ−ファーバー キャンサー インスティテュート， インコーポレイテッド | Inhibitor of cyclin-dependent kinase |
| EP3277808A4 (en) | 2015-03-30 | 2019-05-22 | Greenlight Biosciences, Inc. | Cell-free production of ribonucleic acid |
| EP3288557A4 (en) | 2015-04-27 | 2018-11-07 | University of Florida Research Foundation, Inc. | Metabolically programmed metal chelators and uses thereof |
| WO2016178591A2 (en) | 2015-05-05 | 2016-11-10 | Gene Predit, Sa | Genetic markers and treatment of male obesity |
| HRP20230494T1 (en) | 2015-06-19 | 2023-08-04 | Massachusetts Institute Of Technology | Alkenyl substituted 2,5-piperazinediones and their use in compositions for delivering an agent to a subject or cell |
| CA2990950A1 (en) | 2015-06-30 | 2017-01-05 | Kaleo, Inc. | Auto-injectors for administration of a medicament within a prefilled syringe |
| WO2017004548A1 (en) | 2015-07-01 | 2017-01-05 | Aileron Therapeutics, Inc. | Peptidomimetic macrocycles |
| EP3347372A4 (en) | 2015-09-10 | 2019-09-04 | Aileron Therapeutics, Inc. | Peptidomimetic macrocycles as modulators of mcl-1 |
| DK3350333T3 (en) | 2015-09-17 | 2022-01-31 | Modernatx Inc | POLYNUCLEOTIDES CONTAINING A STABILIZING TAIL REGION |
| HRP20220156T1 (en) | 2015-09-17 | 2022-04-15 | Modernatx, Inc. | Compounds and compositions for intracellular delivery of therapeutic agents |
| EP3355882A1 (en) | 2015-10-01 | 2018-08-08 | Kythera Biopharmaceuticals, Inc. | Compositions comprising a statin for use in methods of adipolysis |
| GB201518684D0 (en) | 2015-10-21 | 2015-12-02 | Glaxosmithkline Biolog Sa | Vaccine |
| DK3394030T3 (en) | 2015-12-22 | 2022-03-28 | Modernatx Inc | COMPOUNDS AND COMPOSITIONS FOR INTRACELLULAR RELEASE OF FUNDS |
| CN109195996A (en) | 2016-03-08 | 2019-01-11 | 中央研究院 | The modularity synthetic method of N- glycan and its array |
| US10918808B2 (en) * | 2016-03-09 | 2021-02-16 | Portal Instruments, Inc. | Angled injection nozzle |
| WO2017161116A1 (en) | 2016-03-17 | 2017-09-21 | Infinity Pharmaceuticals, Inc. | Isotopologues of isoquinolinone and quinazolinone compounds and uses thereof as pi3k kinase inhibitors |
| CN109071653A (en) | 2016-03-29 | 2018-12-21 | 詹森生物科技公司 | Psoriasis is treated with the increased anti-antibody administration of IL12 and/or -23 interval |
| US10954541B2 (en) | 2016-04-06 | 2021-03-23 | Greenlight Biosciences, Inc. | Cell-free production of ribonucleic acid |
| WO2017196504A1 (en) | 2016-05-10 | 2017-11-16 | Sage Burton H Jr | Spring-driven drug delivery device |
| TW201803615A (en) * | 2016-05-31 | 2018-02-01 | 賽諾菲阿凡提斯德意志有限公司 | Button for a drug delivery device and method for assembling a button for a drug delivery device |
| TWI729141B (en) * | 2016-05-31 | 2021-06-01 | 德商賽諾菲阿凡提斯德意志有限公司 | Cap assembly for a drug delivery device and method for assembling a cap assembly |
| CN115746107A (en) | 2016-06-03 | 2023-03-07 | 圣诺菲·帕斯图尔公司 | Modification of engineered influenza hemagglutinin polypeptides |
| WO2017214337A1 (en) | 2016-06-07 | 2017-12-14 | Massachusetts Institute Of Technology | Drug delivery polymers and uses thereof |
| WO2017214269A1 (en) | 2016-06-08 | 2017-12-14 | Infinity Pharmaceuticals, Inc. | Heterocyclic compounds and uses thereof |
| JP2019525901A (en) | 2016-06-14 | 2019-09-12 | モデルナティエックス インコーポレイテッドＭｏｄｅｒｎａＴＸ，Ｉｎｃ． | Stabilized preparation of lipid nanoparticles |
| GB201610599D0 (en) | 2016-06-17 | 2016-08-03 | Glaxosmithkline Biologicals Sa | Immunogenic Composition |
| RU2019104075A (en) | 2016-07-15 | 2020-08-17 | Посейда Терапьютикс, Инк. | CHIMERIC ANTIGEN RECEPTORS (CAR) SPECIFIC FOR MUC1 AND METHODS OF THEIR APPLICATION |
| US20190177421A1 (en) | 2016-07-15 | 2019-06-13 | Poseida Therapeutics, Inc. | Chimeric antigen receptors and methods for use |
| MX2019001341A (en) | 2016-08-05 | 2019-07-04 | Sanofi Pasteur Inc | Multivalent pneumococcal polysaccharide-protein conjugate composition. |
| CN109862908B (en) | 2016-08-05 | 2023-05-02 | 圣诺菲·帕斯图尔公司 | Multivalent pneumococcal polysaccharide-protein conjugate composition |
| CA3034057A1 (en) | 2016-08-22 | 2018-03-01 | CHO Pharma Inc. | Antibodies, binding fragments, and methods of use |
| JP2020500152A (en) | 2016-09-30 | 2020-01-09 | ヤンセン バイオテツク，インコーポレーテツド | Safe and effective method of treating psoriasis with anti-IL23 specific antibody |
| WO2018089540A1 (en) | 2016-11-08 | 2018-05-17 | Modernatx, Inc. | Stabilized formulations of lipid nanoparticles |
| MX2019005661A (en) | 2016-11-16 | 2019-10-07 | Janssen Biotech Inc | Method of treating psoriasis with anti-il-23 specific antibody. |
| CN107050580B (en) * | 2016-11-28 | 2019-12-31 | 大连医科大学附属第二医院 | Automatic reset needleless injector with pressurization function |
| CN106668992B (en) * | 2016-11-28 | 2019-07-12 | 合肥讯创信息科技有限公司 | It is pressurized Needleless injection device |
| WO2018106738A1 (en) | 2016-12-05 | 2018-06-14 | Massachusetts Institute Of Technology | Brush-arm star polymers, conjugates and particles, and uses thereof |
| WO2018119218A1 (en) | 2016-12-23 | 2018-06-28 | Kaleo, Inc. | Medicament delivery device and methods for delivering drugs to infants and children |
| WO2018136413A2 (en) | 2017-01-17 | 2018-07-26 | Kaleo, Inc. | Medicament delivery devices with wireless connectivity and event detection |
| EP3574012A1 (en) | 2017-01-27 | 2019-12-04 | Memorial Sloan Kettering Cancer Center | Bispecific her2 and cd3 binding molecules |
| MX2019008989A (en) | 2017-01-30 | 2019-10-09 | Janssen Biotech Inc | Anti-tnf antibodies, compositions, and methods for the treatment of active psoriatic arthritis. |
| GB2559553B (en) | 2017-02-06 | 2021-10-13 | Consort Medical Plc | A medicament delivery device |
| CN110418652A (en) | 2017-02-07 | 2019-11-05 | 詹森生物科技公司 | For treating the anti-TNF antibodies, composition and method of activity ankylosing spondylitis |
| RS63953B1 (en) | 2017-03-15 | 2023-02-28 | Modernatx Inc | Compound and compositions for intracellular delivery of therapeutic agents |
| JP7332478B2 (en) | 2017-03-15 | 2023-08-23 | モデルナティエックス インコーポレイテッド | Lipid nanoparticle formulation |
| US11555031B2 (en) | 2017-03-20 | 2023-01-17 | The Broad Institute, Inc. | Compounds and methods for regulating insulin secretion |
| KR102643190B1 (en) | 2017-06-10 | 2024-03-04 | 아이노비아 인코포레이티드 | Devices for handling fluids and delivering fluids to the eye |
| WO2018232120A1 (en) | 2017-06-14 | 2018-12-20 | Modernatx, Inc. | Compounds and compositions for intracellular delivery of agents |
| CN107252512B (en) * | 2017-06-16 | 2018-03-13 | 南阳市中心医院 | A kind of gas-driven needle-less syringe |
| EP3641828B1 (en) | 2017-06-23 | 2023-11-22 | Affinivax, Inc. | Immunogenic compositions |
| WO2019013789A1 (en) | 2017-07-12 | 2019-01-17 | Curza Global, Llc | Antimicrobial compounds |
| WO2019013790A1 (en) | 2017-07-12 | 2019-01-17 | Curza Global, Llc | Antimicrobial compounds and uses thereof |
| WO2019040399A1 (en) | 2017-08-22 | 2019-02-28 | Shire-Nps Pharmaceuticals, Inc. | Glp-2 fusion polypeptides and uses for treating and preventing gastrointestinal conditions |
| US11318253B2 (en) * | 2017-08-29 | 2022-05-03 | Clear Dart, L.L.C. | Dart syringe projectile |
| KR101862201B1 (en) | 2017-08-31 | 2018-05-29 | 제이에스케이바이오메드(주) | Micro-jet drug injection device with backflow prevention valve |
| EP3675817A1 (en) | 2017-08-31 | 2020-07-08 | Modernatx, Inc. | Methods of making lipid nanoparticles |
| CN111727256A (en) | 2017-09-08 | 2020-09-29 | 波赛达治疗公司 | Compositions and methods for Chimeric Ligand Receptor (CLR) -mediated conditional gene expression |
| TW201922780A (en) | 2017-09-25 | 2019-06-16 | 美商健生生物科技公司 | Safe and effective method of treating Lupus with anti-IL12/IL23 antibody |
| CN111465701A (en) | 2017-10-11 | 2020-07-28 | 绿光生物科技股份有限公司 | Methods and compositions for nucleoside triphosphate and ribonucleic acid generation |
| WO2019109079A1 (en) | 2017-12-01 | 2019-06-06 | North Carolina State University | Fibrin particles and methods of making the same |
| EP3728305A1 (en) | 2017-12-20 | 2020-10-28 | Poseida Therapeutics, Inc. | Vcar compositions and methods for use |
| GB201721582D0 (en) | 2017-12-21 | 2018-02-07 | Glaxosmithkline Biologicals Sa | S aureus antigens and immunogenic compositions |
| GB201721576D0 (en) | 2017-12-21 | 2018-02-07 | Glaxosmithkline Biologicals Sa | Hla antigens and glycoconjugates thereof |
| KR101859735B1 (en) * | 2018-02-07 | 2018-05-21 | 주식회사 피테크 | Painless injection device |
| EP3762015A4 (en) | 2018-03-05 | 2022-04-27 | Janssen Biotech, Inc. | Methods of treating crohn's disease with anti-il23 specific antibody |
| WO2019173636A1 (en) | 2018-03-07 | 2019-09-12 | Poseida Therapeutics, Inc. | Cartyrin compositions and methods for use |
| US11931551B2 (en) * | 2018-04-09 | 2024-03-19 | Becton Dickinson France | Medical injection system |
| JP2021523138A (en) | 2018-05-11 | 2021-09-02 | ヤンセン バイオテツク，インコーポレーテツド | How to treat depression with IL-23 antibody |
| US11929160B2 (en) | 2018-07-16 | 2024-03-12 | Kaleo, Inc. | Medicament delivery devices with wireless connectivity and compliance detection |
| JP2021530697A (en) | 2018-07-18 | 2021-11-11 | ヤンセン バイオテツク，インコーポレーテツド | Sustained response predictor after treatment with anti-IL23 specific antibody |
| US20220409536A1 (en) | 2018-09-19 | 2022-12-29 | Modernatx, Inc. | Compounds and compositions for intracellular delivery of therapeutic agents |
| CA3113651A1 (en) | 2018-09-20 | 2020-03-26 | Modernatx, Inc. | Preparation of lipid nanoparticles and methods of administration thereof |
| BR112021005467A2 (en) | 2018-09-24 | 2021-06-22 | Janssen Biotech, Inc. | safe and effective method to treat ulcerative colitis with anti-il12/il23 antibody |
| CN113395979A (en) | 2018-11-20 | 2021-09-14 | 詹森生物科技公司 | Safe and effective methods for treating psoriasis with anti-IL-23 specific antibodies |
| MA54562A (en) | 2018-12-18 | 2021-10-27 | Janssen Biotech Inc | SAFE AND EFFECTIVE METHOD OF TREATING LUPUS WITH AN ANTI-IL12/IL23 ANTIBODY |
| AU2019401282A1 (en) | 2018-12-20 | 2021-07-15 | Poseida Therapeutics, Inc. | Nanotransposon compositions and methods of use |
| AU2020208828A1 (en) | 2019-01-15 | 2021-08-05 | Janssen Biotech, Inc. | Anti-TNF antibody compositions and methods for the treatment of juvenile idiopathic arthritis |
| US20230072397A1 (en) | 2019-01-16 | 2023-03-09 | Curza Global, Llc | Antimicrobial Compounds and Methods |
| US20230159491A1 (en) | 2019-01-16 | 2023-05-25 | Curza Global, Llc | Antimicrobial Compounds and Methods |
| EA202192038A1 (en) | 2019-01-23 | 2021-10-05 | Янссен Байотек, Инк. | ANTIBODY COMPOSITIONS TO TNF FOR USE IN METHODS FOR TREATMENT OF PSORIATIC ARTHRITIS |
| KR20210121137A (en) | 2019-01-29 | 2021-10-07 | 샤이어-엔피에스 파마슈티칼즈, 인크. | parathyroid hormone variants |
| JP2022519557A (en) | 2019-01-31 | 2022-03-24 | モデルナティエックス インコーポレイテッド | Method for preparing lipid nanoparticles |
| WO2020168466A1 (en) | 2019-02-19 | 2020-08-27 | Stemirna Therapeutics Co., Ltd. | Modified nucleoside and synthetic methods thereof |
| EA202192508A1 (en) | 2019-03-14 | 2022-03-29 | Янссен Байотек, Инк. | METHODS FOR OBTAINING COMPOSITIONS OF ANTIBODIES TO TNF |
| EP3938391A1 (en) | 2019-03-14 | 2022-01-19 | Janssen Biotech, Inc. | Methods for producing anti-tnf antibody compositions |
| CA3133381A1 (en) | 2019-03-14 | 2020-09-17 | Janssen Biotech, Inc. | Manufacturing methods for producing anti-tnf antibody compositions |
| CA3133395A1 (en) | 2019-03-14 | 2020-09-17 | Janssen Biotech, Inc. | Manufacturing methods for producing anti-il12/il23 antibody compositions |
| KR20210141583A (en) | 2019-03-18 | 2021-11-23 | 얀센 바이오테크 인코포레이티드 | Methods of Treating Psoriasis in Children Using Anti-IL-12/IL-23 Antibodies |
| US11780911B2 (en) | 2019-05-23 | 2023-10-10 | Janssen Biotech, Inc. | Method of treating inflammatory bowel disease with a combination therapy of antibodies to IL-23 and TNF alpha |
| KR20220029593A (en) | 2019-06-03 | 2022-03-08 | 얀센 바이오테크 인코포레이티드 | Anti-TNF antibody compositions, and methods for the treatment of psoriatic arthritis |
| JP2022535534A (en) | 2019-06-03 | 2022-08-09 | ヤンセン バイオテツク，インコーポレーテツド | Anti-TNF Antibodies, Compositions and Methods for Treating Active Ankylosing Spondylitis |
| AU2020319876A1 (en) | 2019-07-31 | 2022-02-24 | Modernatx, Inc. | Compositions and methods for delivery of RNA interference agents to immune cells |
| US20220265803A1 (en) | 2019-07-31 | 2022-08-25 | Sanofi Pasteur Inc. | Multivalent pneumococcal polysaccharide-protein conjugate compositions and methods of using the same |
| WO2021030210A1 (en) | 2019-08-09 | 2021-02-18 | Kaleo, Inc. | Devices and methods for delivery of substances within a prefilled syringe |
| WO2021028752A1 (en) | 2019-08-15 | 2021-02-18 | Janssen Biotech, Inc. | Anti-tfn antibodies for treating type i diabetes |
| CA3149892A1 (en) | 2019-09-05 | 2021-03-11 | Eric M. Ostertag | Allogeneic cell compositions and methods of use |
| CN110882447A (en) * | 2019-11-11 | 2020-03-17 | 徐州深丰精密机械有限公司 | Medical syringe assembly |
| WO2021097061A1 (en) | 2019-11-13 | 2021-05-20 | Curza Global, Llc | Antimicrobial compounds and methods |
| EP4077395A1 (en) | 2019-12-20 | 2022-10-26 | Poseida Therapeutics, Inc. | Anti-muc1 compositions and methods of use |
| WO2021155274A1 (en) | 2020-01-31 | 2021-08-05 | Modernatx, Inc. | Methods of preparing lipid nanoparticles |
| WO2021173965A1 (en) | 2020-02-28 | 2021-09-02 | Massachusetts Institute Of Technology | Identification of variable influenza residues and uses thereof |
| CA3169529A1 (en) | 2020-03-04 | 2021-09-10 | Jingjing Jiang | Compositions and methods for the treatment of metabolic liver disorders |
| EP4118107A1 (en) | 2020-03-11 | 2023-01-18 | Poseida Therapeutics, Inc. | Chimeric stimulatory receptors and methods of use in t cell activation and differentiation |
| CN115996747A (en) | 2020-04-14 | 2023-04-21 | 波赛达治疗公司 | Compositions and methods for treating cancer |
| WO2021214587A1 (en) | 2020-04-21 | 2021-10-28 | Janssen Biotech, Inc. | Anti-tnf alpha agent for treating viral infections |
| WO2021214588A1 (en) | 2020-04-21 | 2021-10-28 | Janssen Biotech, Inc. | Anti-tnf alpha agent for treating coronavirus infections |
| WO2021231729A1 (en) | 2020-05-13 | 2021-11-18 | Sanofi | Adjuvanted stabilized stem hemagglutinin nanoparticles and methods of using the same to induce broadly neutralizing antibodies against influenza |
| US11951284B2 (en) | 2020-08-27 | 2024-04-09 | Tandem Diabetes Care, Inc. | Transitioning to other modes in automated insulin delivery |
| EP4231999A1 (en) | 2020-10-21 | 2023-08-30 | Poseida Therapeutics, Inc. | Compositions and methods for delivery of nucleic acids |
| CN116710116A (en) | 2020-10-30 | 2023-09-05 | Ｘｅｎｏ－Ｉｎｔｅｒｆａｃｅ株式会社 | Beta-sheet femoral bridge peptide |
| CN117083065A (en) | 2020-10-30 | 2023-11-17 | 庆应义塾 | Novel treatment and prevention of sarcopenia-related diseases and the like |
| TW202237068A (en) | 2020-12-09 | 2022-10-01 | 美商建南德克公司 | High-throughput methods for preparing lipid nanoparticles and uses thereof |
| KR102611990B1 (en) * | 2021-02-19 | 2023-12-11 | (주)바이오시드 | One touch type of semi-automatic needle-less injector using gas pressure |
| US20240060090A1 (en) | 2021-02-23 | 2024-02-22 | Poseida Therapeutics, Inc. | Genetically modified induced pluripotent stem cells and methods of use thereof |
| WO2022182792A1 (en) | 2021-02-23 | 2022-09-01 | Poseida Therapeutics, Inc. | Compositions and methods for delivery of nucleic acids |
| WO2022187671A1 (en) | 2021-03-04 | 2022-09-09 | Poseida Therapeutics, Inc. | Compositions and methods for the treatment of hemophilia |
| EP4305088A1 (en) | 2021-03-09 | 2024-01-17 | Massachusetts Institute of Technology | Branched poly(-amino esters) for the delivery of nucleic acids |
| EP4305062A1 (en) | 2021-03-12 | 2024-01-17 | Janssen Biotech, Inc. | Method of treating psoriatic arthritis patients with inadequate response to tnf therapy with anti-il23 specific antibody |
| IL305802A (en) | 2021-03-12 | 2023-11-01 | Janssen Biotech Inc | Safe and effective method of treating psoriatic arthritis with anti-il23 specific antibody |
| TW202313065A (en) | 2021-05-28 | 2023-04-01 | 美商季卡尼醫療公司 | Compounds for treating genetic diseases |
| US20230040065A1 (en) | 2021-07-09 | 2023-02-09 | Janssen Biotech, Inc. | Manufacturing Methods for Producing Anti-TNF Antibody Compositions |
| KR20240034215A (en) | 2021-07-09 | 2024-03-13 | 얀센 바이오테크 인코포레이티드 | Manufacturing Methods for Producing Anti-IL12/IL23 Antibody Compositions |
| WO2023281463A1 (en) | 2021-07-09 | 2023-01-12 | Janssen Biotech, Inc. | Manufacturing methods for producing anti-tnf antibody compositions |
| KR102582365B1 (en) * | 2021-08-05 | 2023-09-25 | (주)씨엔엘바이오텍 | needleless syringe container |
| WO2023018817A1 (en) | 2021-08-11 | 2023-02-16 | Sanofi Pasteur Inc. | Truncated influenza neuraminidase and methods of using the same |
| US20230233667A1 (en) | 2021-09-08 | 2023-07-27 | Affinivax, Inc. | Coronavirus vaccine |
| CA3234642A1 (en) | 2021-10-04 | 2023-04-13 | Poseida Therapeutics, Inc. | Transposases and uses thereof |
| WO2023060088A1 (en) | 2021-10-04 | 2023-04-13 | Poseida Therapeutics, Inc. | Transposon compositions and methods of use thereof |
| WO2023059857A1 (en) | 2021-10-08 | 2023-04-13 | Sanofi Pasteur Inc. | Multivalent influenza vaccines |
| WO2023073615A1 (en) | 2021-10-29 | 2023-05-04 | Janssen Biotech, Inc. | Methods of treating crohn's disease with anti-il23 specific antibody |
| WO2023081798A1 (en) | 2021-11-05 | 2023-05-11 | Sanofi Pasteur Inc. | Multivalent influenza vaccines comprising recombinant hemagglutinin and neuraminidase and methods of using the same |
| WO2023079113A1 (en) | 2021-11-05 | 2023-05-11 | Sanofi | Hybrid multivalent influenza vaccines comprising hemagglutinin and neuraminidase and methods of using the same |
| US20230151087A1 (en) | 2021-11-15 | 2023-05-18 | Janssen Biotech, Inc. | Methods of Treating Crohn's Disease with Anti-IL23 Specific Antibody |
| US20230159633A1 (en) | 2021-11-23 | 2023-05-25 | Janssen Biotech, Inc. | Method of Treating Ulcerative Colitis with Anti-IL23 Specific Antibody |
| WO2023114889A1 (en) | 2021-12-16 | 2023-06-22 | Modernatx, Inc. | Processes for preparing lipid nanoparticles |
| WO2023129963A1 (en) | 2021-12-30 | 2023-07-06 | Curza Global, Llc | Antimicrobial compounds and methods |
| WO2023141576A1 (en) | 2022-01-21 | 2023-07-27 | Poseida Therapeutics, Inc. | Compositions and methods for delivery of nucleic acids |
| WO2023144206A1 (en) | 2022-01-27 | 2023-08-03 | Sanofi Pasteur | Modified vero cells and methods of using the same for virus production |
| WO2023164573A1 (en) | 2022-02-23 | 2023-08-31 | Poseida Therapeutics, Inc. | Genetically modified cells and methods of use thereof |
| WO2023177577A1 (en) | 2022-03-14 | 2023-09-21 | Sanofi Pasteur Inc. | Machine-learning techniques in protein design for vaccine generation |
| WO2023187707A1 (en) | 2022-03-30 | 2023-10-05 | Janssen Biotech, Inc. | Method of treating mild to moderate psoriasis with il-23 specific antibody |
| WO2023193002A1 (en) | 2022-04-01 | 2023-10-05 | Modernatx, Inc. | Cross mixers for lipid nanoparticle production, and methods of operating the same |
| WO2023223265A1 (en) | 2022-05-18 | 2023-11-23 | Janssen Biotech, Inc. | Method for evaluating and treating psoriatic arthritis with il23 antibody |
| WO2023235380A1 (en) | 2022-06-01 | 2023-12-07 | Zikani Therapeutics, Inc. | Macrolides for treating genetic diseases |
| WO2023250513A1 (en) | 2022-06-24 | 2023-12-28 | Zikani Therapeutics, Inc. | 13-membered macrolide compounds for treating diseases mediated by abnormal protein translation |
| WO2024026482A1 (en) | 2022-07-29 | 2024-02-01 | Modernatx, Inc. | Lipid nanoparticle compositions comprising surface lipid derivatives and related uses |
| WO2024026487A1 (en) | 2022-07-29 | 2024-02-01 | Modernatx, Inc. | Lipid nanoparticle compositions comprising phospholipid derivatives and related uses |
| WO2024026475A1 (en) | 2022-07-29 | 2024-02-01 | Modernatx, Inc. | Compositions for delivery to hematopoietic stem and progenitor cells (hspcs) and related uses |
| WO2024036273A1 (en) | 2022-08-11 | 2024-02-15 | Poseida Therapeutics, Inc. | Chimeric cd8-alpha co-receptor compositions and methods of use |
| WO2024049994A1 (en) | 2022-09-01 | 2024-03-07 | Zikani Therapeutics, Inc. | Treatment of familial adenomatous polyopsis using a 13-membered macrolide |
Family Cites Families (31)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US2642062A (en) * | 1949-05-17 | 1953-06-16 | Becton Dickinson Co | Injection apparatus |
| US3507276A (en) * | 1968-08-28 | 1970-04-21 | Murray B Burgess | Jet injector |
| US3688765A (en) * | 1969-10-03 | 1972-09-05 | Jack S Gasaway | Hypodermic injection device |
| US3946732A (en) * | 1973-08-08 | 1976-03-30 | Ampoules, Inc. | Two-chamber mixing syringe |
| NZ206650A (en) * | 1982-12-31 | 1987-05-29 | Phillips Pty Ltd N J | Injector, retractable needle shroud activates piston |
| US4596556A (en) * | 1985-03-25 | 1986-06-24 | Bioject, Inc. | Hypodermic injection apparatus |
| US4722728A (en) * | 1987-01-23 | 1988-02-02 | Patents Unlimited, Ltd. | Needleless hypodermic injector |
| US4941880A (en) * | 1987-06-19 | 1990-07-17 | Bioject, Inc. | Pre-filled ampule and non-invasive hypodermic injection device assembly |
| US4790824A (en) * | 1987-06-19 | 1988-12-13 | Bioject, Inc. | Non-invasive hypodermic injection device |
| AU628029B2 (en) * | 1987-11-16 | 1992-09-10 | Sy-Quest International Limited | Improved apparatus for hypodermic injection of liquids |
| US4874367A (en) * | 1988-02-05 | 1989-10-17 | Marpam International, Inc. | Hypodermic jet injector and cartridge therefor |
| US4913699A (en) | 1988-03-14 | 1990-04-03 | Parsons James S | Disposable needleless injection system |
| US5024656A (en) * | 1988-08-30 | 1991-06-18 | Injet Medical Products, Inc. | Gas-pressure-regulated needleless injection system |
| US5009634A (en) * | 1989-01-11 | 1991-04-23 | The University Of Virginia Alumni Patents Foundation | Metabolic catheter |
| US5064413A (en) * | 1989-11-09 | 1991-11-12 | Bioject, Inc. | Needleless hypodermic injection device |
| GB9118204D0 (en) * | 1991-08-23 | 1991-10-09 | Weston Terence E | Needle-less injector |
| US5279585A (en) | 1992-02-04 | 1994-01-18 | Becton, Dickinson And Company | Medication delivery pen having improved dose delivery features |
| US5569189A (en) | 1992-09-28 | 1996-10-29 | Equidyne Systems, Inc. | hypodermic jet injector |
| US5540664A (en) | 1993-05-27 | 1996-07-30 | Washington Biotech Corporation | Reloadable automatic or manual emergency injection system |
| JP3487856B2 (en) * | 1993-07-31 | 2004-01-19 | ウェストン メディカル リミテッド | Needleless syringe |
| US5593388A (en) * | 1993-11-11 | 1997-01-14 | N.J. Phillips Pty. Limited | Injector with retractable shroud |
| US5536249A (en) | 1994-03-09 | 1996-07-16 | Visionary Medical Products, Inc. | Pen-type injector with a microprocessor and blood characteristic monitor |
| US5899880A (en) * | 1994-04-08 | 1999-05-04 | Powderject Research Limited | Needleless syringe using supersonic gas flow for particle delivery |
| GB9425642D0 (en) | 1994-12-20 | 1995-02-22 | Weston Medical Ltd | Filling device |
| GB9504878D0 (en) * | 1995-03-10 | 1995-04-26 | Weston Medical Ltd | Viscously coupled actuator |
| US5730723A (en) * | 1995-10-10 | 1998-03-24 | Visionary Medical Products Corporation, Inc. | Gas pressured needle-less injection device and method |
| AU1860697A (en) | 1995-09-08 | 1997-07-28 | Visionary Medical Products Corporation | Pen-type injector drive mechanism |
| US6080130A (en) | 1998-11-14 | 2000-06-27 | Castellano; Thomas P. | Gas power source for a needle-less injector |
| US6156008A (en) | 1998-05-04 | 2000-12-05 | Castellano; Thomas P. | Device for avoiding subdermal hematomas from an injection |
| US6096002A (en) | 1998-11-18 | 2000-08-01 | Bioject, Inc. | NGAS powered self-resetting needle-less hypodermic jet injection apparatus and method |
| US6132395A (en) | 1998-12-08 | 2000-10-17 | Bioject, Inc. | Needleless syringe with prefilled cartridge |
-
1996
- 1996-09-25 US US08/719,459 patent/US5730723A/en not_active Expired - Fee Related
- 1996-10-09 ES ES96936287T patent/ES2216069T3/en not_active Expired - Lifetime
- 1996-10-09 JP JP51515797A patent/JP2001515370A/en not_active Ceased
- 1996-10-09 DE DE69632084T patent/DE69632084T2/en not_active Expired - Fee Related
- 1996-10-09 AU AU73970/96A patent/AU7397096A/en not_active Abandoned
- 1996-10-09 AT AT96936287T patent/ATE262935T1/en not_active IP Right Cessation
- 1996-10-09 CA CA002234055A patent/CA2234055C/en not_active Expired - Fee Related
- 1996-10-09 US US08/727,911 patent/US5851198A/en not_active Expired - Fee Related
- 1996-10-09 EP EP96936287A patent/EP0988074B1/en not_active Expired - Lifetime
- 1996-10-09 WO PCT/US1996/016172 patent/WO1997013537A1/en active IP Right Grant
-
1998
- 1998-12-19 US US09/215,769 patent/US6063053A/en not_active Expired - Fee Related
-
2000
- 2000-05-06 US US09/566,928 patent/US6447475B1/en not_active Expired - Fee Related
-
2002
- 2002-03-18 US US10/011,534 patent/US6673034B2/en not_active Expired - Fee Related
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US8221347B2 (en) | 2004-12-01 | 2012-07-17 | Acushot, Inc. | Needle-free injector |
Also Published As
| Publication number | Publication date |
|---|---|
| EP0988074A1 (en) | 2000-03-29 |
| ATE262935T1 (en) | 2004-04-15 |
| CA2234055A1 (en) | 1997-04-17 |
| ES2216069T3 (en) | 2004-10-16 |
| US5730723A (en) | 1998-03-24 |
| WO1997013537A1 (en) | 1997-04-17 |
| DE69632084D1 (en) | 2004-05-06 |
| DE69632084T2 (en) | 2004-11-11 |
| US6447475B1 (en) | 2002-09-10 |
| US6673034B2 (en) | 2004-01-06 |
| US20020099329A1 (en) | 2002-07-25 |
| AU7397096A (en) | 1997-04-30 |
| US6063053A (en) | 2000-05-16 |
| JP2001515370A (en) | 2001-09-18 |
| EP0988074B1 (en) | 2004-03-31 |
| US5851198A (en) | 1998-12-22 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2234055C (en) | Gas pressured needle-less injection device | |
| US6080130A (en) | Gas power source for a needle-less injector | |
| KR100223616B1 (en) | Needleless injector | |
| EP1476211B1 (en) | Injector with bypass channel | |
| EP0404818B1 (en) | Disposable needleless injection system | |
| US4874367A (en) | Hypodermic jet injector and cartridge therefor | |
| JP2781719B2 (en) | Disposable needleless syringe | |
| JP4299466B2 (en) | Needle-assisted jet injector | |
| EP1102606B1 (en) | Injection-assisting probe for medical injector assembly | |
| US8105272B2 (en) | Triggering mechanism for a needle-free injector | |
| US5073165A (en) | Hypodermic jet injector and cartridge therefor | |
| US20120179134A1 (en) | Needleless permanent makeup and tattoo device | |
| US5697917A (en) | Nozzle assembly with adjustable plunger travel gap | |
| US6474369B2 (en) | Apparatus and method for delivering a lyophilized active with a needle-less injector | |
| EP1128857B1 (en) | Apparatus and method for filling an ampule of a needle-less injector | |
| US20070027428A1 (en) | Vial system and method for needle-less injector | |
| WO2023030981A1 (en) | A method of assembling a medicament delivery device |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKLA | Lapsed |