GB2388033A - Automatic injection device - Google Patents

Automatic injection device Download PDF

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Publication number
GB2388033A
GB2388033A GB0210123A GB0210123A GB2388033A GB 2388033 A GB2388033 A GB 2388033A GB 0210123 A GB0210123 A GB 0210123A GB 0210123 A GB0210123 A GB 0210123A GB 2388033 A GB2388033 A GB 2388033A
Authority
GB
United Kingdom
Prior art keywords
syringe
drive
injection device
dispensing piston
needle
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.)
Withdrawn
Application number
GB0210123A
Other versions
GB0210123D0 (en
Inventor
Jeffrey Martin
Martin Lawrence Hughes
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
PA CONSULTING SERVICES
PA CONSULTING SERVICES Ltd
Original Assignee
PA CONSULTING SERVICES
PA CONSULTING SERVICES Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by PA CONSULTING SERVICES, PA CONSULTING SERVICES Ltd filed Critical PA CONSULTING SERVICES
Priority to GB0210123A priority Critical patent/GB2388033A/en
Publication of GB0210123D0 publication Critical patent/GB0210123D0/en
Priority claimed from US10/513,159 external-priority patent/US7476217B2/en
Priority claimed from AU2003229994A external-priority patent/AU2003229994B2/en
Publication of GB2388033A publication Critical patent/GB2388033A/en
Application status is Withdrawn legal-status Critical

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Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/178Syringes
    • A61M5/20Automatic syringes, e.g. with automatically actuated piston rod, with automatic needle injection, filling automatically
    • A61M5/2033Spring-loaded one-shot injectors with or without automatic needle insertion
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/178Syringes
    • A61M5/20Automatic syringes, e.g. with automatically actuated piston rod, with automatic needle injection, filling automatically
    • A61M2005/206With automatic needle insertion
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/178Syringes
    • A61M5/31Details
    • A61M2005/3143Damping means for syringe components executing relative movements, e.g. retarders or attenuators slowing down or timing syringe mechanisms
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/178Syringes
    • A61M5/31Details
    • A61M5/315Pistons; Piston-rods; Guiding, blocking or restricting the movement of the rod or piston; Appliances on the rod for facilitating dosing ; Dosing mechanisms
    • A61M5/31511Piston or piston-rod constructions, e.g. connection of piston with piston-rod
    • A61M2005/3152Piston or piston-rod constructions, e.g. connection of piston with piston-rod including gearings to multiply or attenuate the piston displacing force
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/178Syringes
    • A61M5/31Details
    • A61M5/315Pistons; Piston-rods; Guiding, blocking or restricting the movement of the rod or piston; Appliances on the rod for facilitating dosing ; Dosing mechanisms
    • A61M5/31511Piston or piston-rod constructions, e.g. connection of piston with piston-rod
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/178Syringes
    • A61M5/31Details
    • A61M5/32Needles; Details of needles pertaining to their connection with syringe or hub; Accessories for bringing the needle into, or holding the needle on, the body; Devices for protection of needles
    • A61M5/3205Apparatus for removing or disposing of used needles or syringes, e.g. containers; Means for protection against accidental injuries from used needles
    • A61M5/321Means for protection against accidental injuries by used needles
    • A61M5/3243Means for protection against accidental injuries by used needles being axially-extensible, e.g. protective sleeves coaxially slidable on the syringe barrel
    • A61M5/3257Semi-automatic sleeve extension, i.e. in which the triggering of the sleeve extension requires a deliberate action by the user, e.g. manual release of spring-biased extension means
    • A61M5/326Fully automatic, i.e. in which the triggering does not require a deliberate action by the user

Abstract

An injection device for use with a syringe 30 having a bore extending from an end surface 34, a needle 36 communicating with the bore through the end surface and a dispensing piston 38 movable in said bore towards said end surface so as to expel the content of the syringe through the needle, the injection device including a housing 60 having an opening at one end through which the needle may extend, a resilient member 74 for biassing the syringe and needle inwardly of the housing, a drive element movable towards said one end so as to move the needle of the syringe out of the opening against the bias of the resilient member and to move the dispensing piston of the syringe towards the end surface, a delatch mechanism 72 operable to release the syringe such that the needle moves inwardly of the housing, a drive coupling 40 for extending from said drive element to the dispensing piston of the syringe so as to transfer movement of said drive element to the dispensing piston, wherein the drive coupling gradually reduces in length such that, after the drive element has moved the dispensing piston to the end surface, the drive element continues to move to said predetermined position at which said delatch mechanism releases the syringe. The drive coupling may be a fluid 52 with a bleed valve 56 such that it reduces in length during its travel. The drive coupling may also be a direct engagement which is released when the needle extends out of the housing.

Description

-1 INJECTION DEVICE

The present invention relates to an injection device, in particular an injection device which, having dispensed the contents of a syringe, automatically retracts the 5 needle of the syringe.

Devices exist which are spring loaded to extend automatically the needle of a syringe from the device, dispense the contents of the syringe and then automatically retract the needle. WO 95/35126 describes such a device.

As illustrated in Figure I of the accompanying drawings, the device includes 10 a housing 2 in which a syringe 4 is contained. The housing 2 includes an opening 6 through which the needle 8 of the syringe 4 may extend. A retraction spring 10 biases the syringe 4 away from the opening 6. The device also includes a drive element 12 which is biassed by a spring 14 to drive a coupling 16 to move the dispensing piston 18 of the syringe 4. In use, a release mechanism 20 releases the 15 drive element 12 such that the syringe 4 is first moved forwards and the needle 8 projects through the opening 6. Subsequently, the dispensing piston 18 is moved so as to expel the contents of the syringe 4. The device is designed to include a delatch mechanism. In particular, at the point at which the dispensing piston 18 reaches the end of the bore in the syringe 4, arms 22 at the end of the coupling 16 are deflected 20 by a collar 24 within the housing 2 so as to disengage from the drive element 12.

The arms 22 and coupling 16 may then move within a central passage of the drive element 12. As a result, by virtue of the bias of spring 10, the coupling 16 moves inside the drive element 12, the syringe 4 is driven away from the opening 6 and the needle 8 is retracted within the opening 6.

25 Other similar delatch or retract arrangements have also been proposed. For instance, EP-A-0 516 473 discloses one embodiment in which, at the point at which the dispensing piston reaches the end of the bore in the syringe, a portion of the coupling instantaneously collapses in length as the retraction spring retracts the needle of the spring.

30 In practice, all of these proposals suffer a problem that, due to a stack up of tolerances of the various manufactured components of the assembled device (the

( dimensions of all manufacture components vary around a mean), it cannot be assured that the delatch mechanism will enable retraction of the syringe and needle at precisely the moment at which the dispensing piston reaches the end of the bore. In practice, either the mechanism delatches before the dispensing piston reaches the end 5 of the bore, such that the syringe is not emptied, or the piston reaches the end of the bore before the mechanism has moved sufficiently far to delatch.

Although this problem has been recognised before, for instance in US 6, 159,181, the proposed solution has been to provide a user actuated retraction mechanism rather than an automatic one. This is considered to be undesirable.

10 It is an object of the present invention to provide an injection device which is relatively simple and of low cost (so as to be useful as a single use device) and which overcomes or at least reduces the problems identified above.

According to the present invention there is provided an injection device including: 15 a housing for containing a syringe having a bore extending from an end surface, a needle communicating with the bore through the end surface and a dispensing piston movable in said bore towards said end surface so as to expel the contents of the syringe through the needle, the housing having an opening at one end through which the needle may extend; 20 a resilient member for biassing the syringe and needle inwardly of the housing; a drive element movable towards said one end so as to move the needle of the syringe out of the opening against the bias of the resilient member and to move the dispensing piston of the syringe towards the end surface; 25 a delatch mechanism operable to release the syringe such that the needle moves inwardly of the housing; a drive coupling for extending from said drive element to the dispensing piston of the syringe so as to transfer movement of said drive element to the dispensing piston; wherein 30 the drive coupling is compressible in length whilst overcoming the bias of the resilient member such that' after the drive element has moved the dispensing piston

-3 to the end surface, the drive coupling gradually reduces in length whilst the dispensing piston is maintained at the end surface until said delatch mechanism releases the syringe.

5 According to the present invention there is also provided a drive coupling for use in an injection device, the drive coupling having: a length for extending from the drive element to the dispensing piston of the syringe so as to transfer movement of the drive element to the dispensing piston; wherein 10 the drive coupling is compressible in length whilst overcoming the bias of the resilient member such that, after the drive element has moved the dispensing piston to the end surface, the drive coupling gradually reduces in length whilst the dispensing piston is maintained at the end surface until the delatch mechanism releases the syringe.

15 Thus, since the drive coupling is able to gradually reduce in length whilst still providing a resistive force to overcome the resilient member and maintain the needle in its extended position, it is possible to design the injection device to operate the delatch mechanism at some point after the dispensing piston has reached the end surface and fully expelled the contents of the syringe. Since the delatch mechanism 20 is now triggered at some uncritical point of time after the contents of the syringe have been expelled, tolerances of the various components are no longer a problem.

Preferably, the delatch mechanism is operable when the drive element reaches a predetermined position in said housing and the drive coupling gradually reduces in Icny,th such that, after the dispensing piston reaches the end surface, the drive 25 element continues to move in said housing to said predetermined position.

The drive element may continue to move over a period of time as the drive coupling continues to reduce in length such that, even though the dispensing piston has reached the end of its travel and abuts the end surface, the drive element can assuredly move to the necessary position to trigger the return mechanism.

( lt is merely sufficient to ensure that the drive element does not reach the position for triggering the delatch mechanism before the dispensing piston reaches the end surface of the syringe.

It will be appreciated that, contrary to previous mechanisms, in particular the 5 collapsing structures of EP-A-O 516 473, the drive coupling of the present invention does not collapse instantaneously but reduces in length gradually. Indeed, the length of the drive coupling continues to reduce in length gradually even alter the dispensing piston abuts the end surface. Furthermore, whilst collapsing, the drive coupling still transfers sufficient force to overcome the bias of the retraction spring 10 and maintain the needle in its extended position.

In contrast, at some point up to and including that at which the dispensing piston abuts the end surface, previous collapsing couplings collapse instantaneously under the influence of the retraction spring and do not resist its bias. In particular, once the collapsing coupling of EPA-O 516 473 starts to reduce in length, it offers 1 S virtually no resistance to the retract spring and, hence, is almost instantaneously collapsed. Furthermore, in previous arrangements, once the dispensing piston abuts the end surface, the drive element and drive coupling can move no further and, hence, collapsing of the drive coupling cannot be initiated. However, with the present 20 invention, even after the dispensing piston abuts the end surface, the drive element can continue to move whilst the dispensing piston is maintained at the end surface.

The present invention could be considered as a damped collapse of the drive coupling such that the force and motion of the drive element maintain the syringe and needle in position, even after the dispensing piston abuts the end surface, until the 25 drive element reaches the predetermined position.

Depending on the exact nature of the arrangement, the drive coupling may only start to collapse when the dispensing piston reaches the end surface or it may start to collapse at some predetermined point just before the piston reaches the end surface. Before it starts to collapse, it is preferably rigid.

30 Provided that there is sufficient length and that the drive element causes the dispensing piston to expel the contents of the syringe sufficiently quickly, it is

( -5 possible for the drive coupling to reduce in length gradually throughout the entire operation and the entire movement of the drive element. However, since the controlled collapsing of the drive coupling is only required in the region of the dispensing piston reaching the end surface, it is preferable that the drive coupling 5 remains of constant length before then. Thus, preferably, the drive coupling does not reduce in length until the dispensing piston has reached a position at least proximate the end surface.

The drive coupling may include a fluid chamber defined between first and second relatively movable walls, the first wall being movable by said drive element 10 and said second wall being operable to move the dispensing piston, and a bleed orifice for bleeding Quid from the fluid chamber.

In this way, drive from the drive element and the first wall is transmitted through fluid in the fluid chamber to the second wall and the dispensing piston. By means of the bleed orifice' fluid gradually bleeds from the fluid chamber such that 15 the first and second walls move gradually towards one another and the length of the drive coupling is reduced.

A bleed orifice could be included in the first wall so as to enable fluid to bleed from the fluid chamber when the drive element moves the first wall and compresses the drive coupling and fluid chamber.

20 The dimensions of any bleed orifice are chosen such that pressure of the fluid in the fluid chamber is maintained sufficient to force the dispensing piston to the end surface of the syringe.

Preferably, the drive coupling includes a main body for mounting on the syringe so as to have a position fixed relative to the bore and the needle, the main 25 body having a peripheral wall defining an elongate passage within which the first and second walls are both movable, the fluid chamber being defiecd by the peripheral wall and the first and second walls.

In this way, as the drive element moves towards the first end, both the first and second walls are moved within the elongate passage, the fluid chamber being 30 defined by the space between them.

-6 A bleed orifice may be formed at a predetermined longitudinal position along the peripheral wall such that it is only exposed to the fluid chamber once the second wall passes the predetermined longitudinal position.

In this way, until the second wall reaches the predetermined longitudinal 5 position, the fluid chamber remains of constant volume and the effective length of the drive coupling does not reduce. However, once the second wall reaches the predetermined longitudinal position, fluid bleeds through the bleed orifice so that the length between the first and second walls and the effective length of the drive coupling gradually reduces so as to ensure that the drive element triggers the delatch 10 and retract mechanism.

It should be appreciated that the present invention can be applied to injection devices which house conventional syringes or which house other mass produced cartridges of a standard design. However, it is also possible to form the drive coupling in the syringe itself.

15 The first and second walls may be movable in the bore of the syringe such that the fluid chamber is defined by the bore and the f rst and second walls.

In this way, the number of component parts may be reduced.

The second wall may form an integral part of the dispensing piston or may drive the dispensing piston through a spacer or the like.

20 As described above, a bleed orifice could be formed in the first wall so as to / enable fluid to bleed from the fluid chamber. However, preferably, the bleed orifice is formed at a predetermined longitudinal position along the bore and is only opened to the fluid chamber once the second wall passes the predetermined longitudinal position. 25 In this way, as described above, the fluid chamber remains of constant volume until the second wall reaches the predetermined longitudinal position such that the effective length of the drive coupling starts to reduce only in the region where the dispensing piston reaches the end surface.

The bleed orifice may be circular. Alternatively, it may have a crosssection 30 which is elongate and/or there may be an array of bleed orifices extending towards

( the end surface such that as a second wall moves towards the end surface, fluid bleeds faster from the fluid chamber.

The orifices may be arranged in this way such that, once the dispensing piston reaches the end surface, the second wall exposes a sufficient area of the bleed 5 orifice(s) to allow fluid to bleed from the fluid chamber at a rate appropriate to allow the resilient member to retract the syringe and needle.

Indeed, according to the present invention, there may be provided an injection device including: a housing containing a syringe with a syringe body having a bore extending 10 from an end surface, a needle communicating with the bore through the end surface and a dispensing piston movable in said bore towards said end surface so as to expel the contents of the syringe through the needle, the housing having an opening at one end through which the needle may extend; a resilient member for biasing the syringe and needle inwardly of the housing; 15 a drive element movable towards said one end so as to move the needle of the syringe out of the opening against the bias of the resilient member and to move the dispensing piston of the syringe towards the end surface; wherein the syringe further includes: a secondary piston movable in said bore, the dispensing piston and the 20 secondary piston defining a fluid filled chamber therebetween; and a bleed orifice communicating with said bore; wherein the bleed orifice is positioned at a distance from the end surface and the dispensing piston is of such a length that the dispensing piston exposes the bleed orifice to the fluid filled chamber as the dispensing piston reaches the end surface 25 and loss of fluid from the fluid chamber allows retraction of the needle by virtue of the bias of the resilient member.

Since the point of retraction is only dependent on the position of the bleed orifice and the length of the dispensing piston, the number of tolerances affecting the point ot retraction are reduced such that the syringe can be assuredly retracted at the 30 point at which the contents is fully dispensed.

( -8 Alternatively, the drive coupling may include a drive frictional surface engaging a driven frictional surface, the drive frictional surface being movable by the drive element and the driven Frictional surface being operable to move the dispensing piston such that, when the dispensing piston reaches the end surface, the first 5 frictional surface slips relative to the second frictional surface.

Thus, in this case, the drive coupling only reduces in length once the dispensing piston reaches the end surface. The drive element continues to apply a force to the drive coupling by virtue of the frictional resistance such that the frictional surfaces slip, the drive coupling reduces in length and the drive element 10 reaches the required position to trigger the return mechanism.

The drive frictional surface may be rotatable about an axis generally perpendicular to the surface and be moved by the drive element at a position offset from the axis.

Similarly, the driven frictional surface may be rotatable about an axis 15 generally parallel to the surface and may be operable to move the dispensing piston from a position offset from the axis.

In other words, drive to or from the rotational frictional surface may be by means of a crank mechanism such that, when the surfaces slip and rotate, the connection points to the drive element and the dispensing piston move closer 20 together.

The drive coupling may include a rack and a pinion gear wherein one of the rack and the pinion gear is movable by the drive element and the other of the rack and the pinion is operable to move the dispensing piston.

In this way, as the drive element exerts a compression force on the drive 25 coupling, the rack will tend to rotate the pinion gear.

The pinion gear may include a friction brake to prevent rotation and allow the drive element to move the dispensing piston. When the dispensing piston reaches the end surface, the friction brake slips and the length of the drive coupling is reduced.

Alternatively, the pinion gear can drive a fly wheel such that when the 30 dispensing piston reaches the end surface, the pinion gear is turned against the

-9- inertial resistance of the fly wheel. Thus, once again, the length of the drive coupling is reduced.

As explained above, previous injection devices drive the dispensing piston to first move the syringe as a whole and position the needle outside of the injection 5 device housing. This works well for fine needles where the back pressure on the fluid for injection is relatively high and the force required to insert the needle is relatively low. However, where there is more difficulty in inserting the needle, there is a possibility that some fluid will be dispensed from the needle before it is correctly inserted below the skin.

10 Hence, preferably, the injection device further includes an engagement for transferring drive directly from the drive coupling to the syringe body such that movement of the drive element towards said one end causes no relative movement of the dispensing piston in the syringe wherein the engagement is releasable once the needle of the syringe extends out of the opening such that movement of the drive 15 element towards said one end causes relative movement of the dispensing piston in the syringe body.

Thus, furthermore, according to the present invention, there is provided an injection device including: a housing for containing a syringe having a bore extending in a syringe body 20 from an end surface, a needle communicating with the bore through the end surface and a dispensing piston movable in said bore towards said end surface so as to expel the contents of the syringe through the needle, the housing having an opening at one end through which the needle may extend; a resilient member for biassing the syringe and needle inwardly of the 25 housing; a drive element movable towards to said one end so as to move the needle of the syringe out of the opening against the bias of the resilient member and to move the dispensing piston of the syringe towards the end surface; a drive coupling for extending from said drive element to the dispensing 30 piston of the syringe so as to transfer movement of said drive element to the dispensing piston; and

-10 an engagement for transferring drive directly from the drive coupling to the syringe body such that movement of the drive element towards said one end causes no relative movement of the dispensing piston in the syringe; wherein the engagement is releasable once the needle of the syringe extends out of the 5 opening such that movement of the drive element towards said one end causes relative movement of the dispensing piston in the syringe body.

This ensures that the drive element correctly positions the syringe with the needle protruding from the housing before the dispensing piston is moved to dispense the contents of the syringe.

l O Preferably, the housing includes a release portion which interacts with the engagement to release drive to the syringe.

In this way, engagement may be released by virtue of the relative position of the syringe in the housing.

Preferably, the release portion is located in the housing at a predetermined Is position and the engagement includes a trigger which is operated by the release portion to release drive to the syringe upon reaching the predetermined position.

In this way, the needle is assuredly extended by the right amount.

Preferably, the engagement includes a resilient latch and the release portion includes at least a recess in a wall of the housing allowing deflection of the resilient 20 latch to release the drive to the syringe.

A Hence, the wall of the housing may maintain the resilient latch in a position of engagement until it reaches a recess or even an opening in the wall.

Preferably, the at least a recess engages the resilient latch so as to prevent further relative movement of the syringe body in the housing.

25 Thus, when the resilient latch moves into the recess or opening it may then engage with the recess or opening so as to fix the relative position between the syringe anal the housing.

As described above, the drive coupling may include a fluid chamber defined between first and second relatively movable walls, the first wall being part of a piston 30 and the resilient latch operating on the piston.

( -11 By engaging with either the dispensing piston or a secondary piston (forming with the dispensing piston a fluid chamber), the relative position between the dispensing piston and the syringe body can be fixed, such that any drive applied to the drive coupling or dispensing piston will result in movement of the syringe rather 5 than the dispensing piston relative to the syringe.

The drive coupling may include a rigid element extending from the drive element, the engagement may include at least one protrusion on a surface of the rigid element and a latch fixed relative to the syringe body engaging the protrusion and the release portion may include a stop on the housing for engaging the latch wherein the 10 rigid element moves the latch with the protrusion until the latch abuts the stop, whereupon the latch releases from the protrusion.

The latch may be deflected resiliently past the protrusion. However, alternatively, the latch may be hinged as a cantilever at a point between an end engaging protrusion and an opposite end wherein the stop deflects the opposite end 15 so as to release engagement with the protrusion.

The latch may be hinged at the point at which it is attached to the syringe or alternatively to a part of the drive coupling mounted to the syringe with a fixed relative position to the needle.

The engagement may releasably connect the drive coupling to the syringe.

20 Alternatively, the engagement may releasably connect a part of the drive coupling movable with the drive element to a part of the drive coupling to be mounted to the syringe in a fixed relative position to the needle.

The invention will be more clearly understood from the following description, given by way of example only, with reference to the accompanying

25 drawings, in which: Figure I illustrates a known construction for an injection device; Figure 2 illustrates a drive coupling according to the present invention; Figure 3 illustrates the drive coupling of Figure 2 incorporated into an injection device similar to that illustrated in Figure 1; 30 Figure 4 illustrates schematically an injection device in which the drive coupling is incorporated into the syringe cartridge itself;

f -12 Figure 5 illustrates an embodiment providing direct drive to the syringe; Figure 6 illustrates an alternative embodiment providing direct drive to the syringe. Figure 7 illustrates schematically a friction plate embodiment, 5 Figure 8 illustrates schematically a rack and pinion embodiment; and Figure 9 illustrates schematically a rack and pinion construction using a fly wheel. As will be apparent from the above, the present invention concerns injection devices and is based on driving the dispensing piston of a syringe with a drive 10 coupling which can gradually reduce in length so as to ensure that the dispensing piston is moved fully along the length of the syringe and that the needle is held in its extended position by an appropriate force until that time.

Figure 2 illustrates an embodiment of a suitable drive coupling.

The drive coupling is for use with a syringe 30, such as a standard syringe or l 5 cartridge, which includes a bore 32 extending from an end surface 34 within that bore and a needle 36 which communicates with the bore 32 through the end surface 34. A dispensing piston 38 is movable along the bore 32 towards the end surface 34. In particular, by moving the dispensing piston alone; the length of the syringe until it abuts the end surface 34, the entire contents of the syringe may be expelled through 20 the syringe needle 36.

/ As illustrated, the drive coupling 40 includes a main body 42 which mates with the end of the syringe 30.

The main body 42 includes an elongate through passage along which a first piston 44 and a second piston 46 may move. The first piston 44 defines a first wall 25 48 facing a second wall 50 defined by the second piston 46.

The first wall 48 and second wall 50, together with the elongate passage 43, define a fluid chamber 52 filled with fluid. This fluid is preferably liquid and substantially incompressible.

The first piston 44 and, hence, the first wall 48 may be driven by the drive 30 element of an injection device. I-his is illustrated more clearly in Figure 3.

-13 As the first piston 44 is moved along the elongate passage 43, since the fluid in the fluid chamber 52 is substantially incompressible, the second wall 50 and, hence, the second piston 46, is also moved along the elongate passage.

For convenience of design, a spacing element S4 transfers drive from the == 5 second piston 46 to the dispensing piston 38 of the syringe 30.

Thus, the drive coupling 40 transfers movement to the dispensing piston 38.

At a predetermined position along the length of the passageway 43, a bleed orifice 56 is provided. Once the second wall 50 passes the bleed orifice 56, fluid is able to bleed from the fluid chamber 52 to outside the main body 42. As this fluid l 0 bleeds away, the volume of the fluid chamber 52 will be reduced and the distance between the first wall 48 and the second wall 50 will also be reduced.

The predetermined position of the bleed orifice 56 is chosen such that' with the main body 42 mated to the syringe 30 and having a fixed relative position, the second wall 50 will pass the bleed orifice 56 just before the dispensing piston 38 15 reaches the end surface 34.

It will be appreciated that, theoretically, the second wall 50 could open the He bleed orifice 56 just as the dispensing piston 38 reaches the end surface 34.

However, the present invention is based on a recognition that tolerances, particularly the compound effect of tolerances of different components, mean that such design 20 cannot be guaranteed. Therefore, the second wall 50 exposes the bleed orifice 56 A.' when the dispensing piston 38 is at a position proximate the end surface 34 so as to ensure that the bleed orifice 56 is open by the time the dispensing piston 38 abuts the -

end surface 34.

It will be appreciated that, even with the bleed orifice 56 open, some driving 25 force will still be transmitted to the second piston 46 such that the dispensing piston 38 will be driven the final small distance to the end surface 34 to dispense the remaining contents of the syringe 30.

With the dispensing piston 38 abutting the end surface 34, the second piston 46 and second wall 50 will move no further. However, as fluid bleeds from the fluid -

30 chamber 52, the first wall 48 and first piston 44 will continue to move towards the -14 end surface 34 until a return delatch mechanism is operated to retract

the syringe 30 and needle 36 back into the housing of the injection device.

The particular nature of the return delatch mechanism is not essential to the present invention and any suitable mechanism may be employed. Similarly, the 5 drive element may be operated in any known manner, for instance using springs, gas pressure, manual operation, etc. Nevertheless, Figure 3 illustrates an injection device similar to that of Figure l incorporating a drive coupling like that of Figure 2.

The syringe 30 is contained within the housing 60 of the injection device.

The housing 60 has a first end 62 in which an opening 64 is formed.

l O In use, a drive element 66 is released using a button 68 and a drive spring moves the drive element 66 towards the end 62.

As with the device of Figure], a latch 72 in the form of resiliently deflectable arms, is provided between the drive coupling 40 and the drive element 66. By means of the latch arrangement 72 and the drive coupling 40, the syringe 30 is driven l 5 towards the end 62 against the bias of the return spring 74 so that the needle 36 extends out of the device.

In particular, a rubber seal 37 is provided over the needle 36 so as to maintain sterility. The rubber seal 37 abuts the surround of opening 64, the needle pierces the rubber seal 3 7 and then the rubber seal concertinas as the syringe moves forward. It 20 will be appreciated that the rubber seal provides some resistance to movement of the syringe and that the coupling 40 needs to overcome the resistance.

As explained above, the drive coupling 40 then enables the dispensing piston 38 to be moved all the way to the end surface 34 so as to expel the entire contents of the syringe 30. By means of the drive coupling, in this embodiment using the fluid 25 chamber 52 and bleed orifice 56, the drive coupling reduces in length under the force of the drive element 66 and drive spring 70 until the collar 76 deflects the arms of the latch mechanism 72 allowing the drive coupling to move within the drive element 66 and the return spring 74 to retract the syringe 30 and needle 36.

Thus, the drive coupling acts as a controlled collapsing element which 30 remains rigid during the majority of the dispensing piston travel. When the dispensing piston 38 nears the end surface 34 of the syringe, the controlled collapsing

-15 element collapses in such a way that it can continue to transfer force (and motion) from the drive mechanism to the dispensing piston while it collapses. This enables the dispensing piston to be pushed to the end of the syringe (expelling all of the contents) before the delatching mechanism 72 has travelled far enough to reach the trigger point. After the dispensing piston 38 has reached the end of the syringe, the controlled collapsing element 40 continues to collapse under the force of the drive mechanism. This enables the delatching mechanism 72 to continue to move forwards until it reaches the trigger point 76, when it will delatch and allow needle retraction to occur. In other words, the drive coupling reduces in length or the 10 controlled collapsing element collapses over a finite and controllable period of time, enabling the continued forward travel of the delatch mechanism after the dispensing piston has reached the end of the syringe.

It will be appreciated that fluid escaping from the bleed orifice will have to be captured. Although not illustrated, this may be achieved by any suitable means, for 15 instance wicking it on to a suitable absorbent material (held within the device) or trapping it between seals in the device.

Although the preferred embodiment as described above allows the drive coupling to reduce in length only when the dispensing piston approaches the end surface of the syringe, where the drive coupling reduces in length at a rate which is 20 relatively slow with respect to movement of the dispensing piston 38, it is possible I/ for the drive coupling to gradually reduce in length throughout the entire dispensing operation. As a modification of the embodiment described above, one or more bleed orifices along the length of the passageway 43 may achieve this or, alternatively, bleed orifices through one or both of the first piston 44 and second piston 46.

25 Indeed, any other suitable fluid damped collapsing arrangement could be used.

The description given above principally concerns the use of a drive coupling

with standard unmodified known syringes or cartridges. However, by providing syringes or cartridges intended specifically for this use, a drive coupling according to the present invention may be implemented as part of the syringe itself. This is 30 illustrated schematically in Figure 4(a).

-16 Rather than provide a separate body and passageway for the fluid chamber, as illustrated, a fluid chamber 80 is provided within the bore 82 of the syringe 84 itself.

The fluid chamber 80 is formed between a first wall 86 and a second wall 88.

However, although the first wall 86 is formed on a first piston 90, the second wall 88 5 is formed on the dispensing piston 92. Of course, it would also be possible to provide a second piston in the bore 82 for driving the dispensing piston 92.

In a manner equivalent to that described for the embodiment of Figure 3, a bleed hole 94 is provided through the wall of the syringe 84. Thus, in the same way, the bleed orifice 94 is positioned such that it connects with the fluid chamber 80 just l O before the dispensing piston 92 contacts the end surface 96 of the syringe 84. After the dispensing piston 92 contacts the end surface 96 bleeding of fluid from the fluid chamber 80 will allow the first piston 90 to continue moving along the syringe until an appropriate retract mechanism is operated.

For the illustrated embodiment, it will be appreciated that the moment at l 5 which the bleed orifice 94 opens to the fluid chamber 80 is dependent only on 3 tolerances of the dispensing piston 92 and the position of the bleed orifice 94.

Following on from this, it is possible to make further use of the bleed orifice 94.

In particular, by providing a bleed orifice 94 which is elongate in the direction of travel of the dispensing piston 92 or by providing an array of orifices 20 extending in that direction, it means that, as the dispensing piston 92 moves towards A/ the end surface 96, the crosssectional area available for bleeding increases. Hence, increased bleeding can be obtained as the dispensing piston 92 reaches the end surface 96. This may enhance or decrease the time needed to actuate the retraction mechanism. Indeed, by providing a large bleed cross-sectional area at exactly the 25 position where the dispensing piston 92 reaches the end surface 96, it is possible to empty fluid from the fluid chamber 80 at a sufficient rate to allow the return spring 98 to retract the syringe 84 and needle l DO. Hence, the Buid chamber 80 and bleed orifice 94 effectively forms the return mechanism with the return spring 98.

Figure 4(b) illustrates a possible triangular cross-section for the bleed orifice 30 94.

-17 Figure 5(a) illustrates schematically a similar device having a latch mechanism illustrated more clearly in Figure 5(b), the outer wall of the syringe 84 includes latches 102 which are deflected inwardly by the inner surface 104 of the housing l 06 of the injection device. As a result, the first piston 90, for instance by 5 means of a flange l 08 engages the inwardly deflected latch l 02. Thus, when the first piston 90 is moved to operate the syringe 84, it is not able to move relative to the syringe 84 by sliding within the bore 82. Instead, it pushes upon the latches 102 and directly moves the syringe 84 so as to move the needle 100 through the opening l l 0 in the injection device.

l 0 Openings l 12 are provided in the housing 106 at radial positions corresponding to the positions of the latches l 02. Thus, when the first piston 90 moves the syringe 84 forward to the point where the latches l 02 reach the openings I l 2, the latches l 02 move outwardly into the openings l l 2, thereby releasing the first piston 90. In this embodiment, the latches 102 also prevent further forward l 5 movement of the syringe 84 itself. Subsequent movement of the first piston 90 will cause compression of the fluid in the fluid chamber 80 and movement of the dispensing piston 92 in the manner described above.

By virtue of the sloped profile of the latches 102, when the syringe 84 is retracted, the latches are once again deflected inwardly of the housing l 06 out of the 20 openings 1 12, thereby allowing movement of the syringe 84.

/ Figure 6 illustrates an embodiment similar to that of Figure 4(a) but incorporating an alternative to the latch of Figure 5(b).

As illustrated two or more latch levers 200 extend forwardly from a rear portion of a drive coupling 202. They engage with the drive coupling by means of a 25 detent arrangement. As illustrated, the drive coupling includes one or more protrusions 204.

In use, when the drive element 206 starts to travel along the device, the detent arrangement, for instance the protrusions 204, engage the ends of the levers 200. The levers in turn push on the housing 2 l 0 of the syringe, for example by the ends of the 30 levers 200 abutting the end of the syringe body. Hence, the syringe is assuredly pushed forward until the needle 2 l 2 extends from the opening 2 l 4.

-18 When the opposite ends of the levers 200 reach abutments 214 in the housing, further movement of the drive element 206 overcomes the detent such that the piston is then driven.

This may be achieved by forming the ends of the levers 200 as a single 5 resilient ring which merely deflects around the protrusions 204. However, as illustrated, the levers 200 are actually provided with hinges 218, such that the inwardly sloping walls of the housing cause the levers to disengage from the protrusions 204. The hinges may attach the levers 200 to the syringe body and indeed the levers, hinges and syringe body may be formed integrally as a single unit.

10 It will be appreciated that other detent or latch arrangements are also possible, for instance with the ends of the levers 200 engaging in recesses in the drive coupling 202. It is also possible to make use of a resilient o-ring to provide an inward bias to the levers 200.

15 I his general construction ensures that the syringe is fully extended from the injection device before any fluid is expelled from the syringe. It will be appreciated that equivalent mechanisms may be used in conjunction with the other embodiments, for instance providing latches in the main body of the drive coupling. Indeed, this construction could also be used in other arrangements without the arrangement of the 20 drive coupling which reduces in length.

/ The present invention need not be implemented only with a collapsible fluid chamber. Any other suitable collapsible arrangement may also be used.

Figure 7 illustrates schematically an alternative arrangement. A drive plate 300 is rotatable about an axis 302 and includes a frictional surface mating with the 25 frictional surface of a driven plate 304. As illustrated, the driven plate 304 is to be connected to a dispensing piston of a syringe, whereas the drive plate 300 is moved by a drive element of an injection device.

As illustrated, the drive element connects to the drive plate 300 at a position offset from the rotational axis 302 so as to form a crank arrangement.

30 In use, the drive element applies a tangential force to the drive plate 300, but, because of the frictional resistance between the frictional surfaces of the drive plate

-19 300 and the driven plate 304, the drive plate 300 does not rotate about its axis 302.

Instead, the entire arrangement is moved in the direction of the force so that the driven plate 304 moves the dispensing piston of the syringe. Once the dispensing piston reaches the end of its travel and the driven plate 304 can move no further, the 5 frictional resistance between the plate 304 is overcome and the drive plate 300 starts to rotate about its axis 302. Because of the offset connection to the drive plate 300, this allows the drive element of the ejection device to move further and the retraction mechanism to be operated. The frictional resistance between the two plates will maintain the force on the dispensing piston of the syringe.

10 Figure 8 illustrates schematically an embodiment in which the drive coupling includes one component having a rack gear 400 and another component rotatably supporting a pinion gear 402. The pinion gear is provided with some means to resist rotation, for instance by means of friction contact.

When the drive coupling is used to move the dispensing piston of a syringe, l 5 the pinion gear 402 will resist rotation and, hence, the drive coupling will maintain its length. However, once the dispensing piston reaches the end of its travel in the syringe, the drive coupling will come under a compressive load and the pinion gear 402 will be rotated by the rack gear 400. In this way, the length of the drive coupling will gradually be reduced whilst the frictional resistance of the pinion gear 402 will 20 maintain the force on the dispensing piston of the syringe. Hence, the drive element a/ will continue to move until an appropriate retract mechanism is operated.

Figure 9 illustrates a development of the embodiment of Figure 8 in which the frictional resistance to the pinion gear 402 is replaced by the inertial resistance of a fly wheel 404 or the like.

Claims (34)

( -20. CLAIMS
1. An injection device including: a housing for containing a syringe having a bore extending from an end 5 surface, a needle communicating with the bore through the end surface and a dispensing piston movable in said bore towards said end surface so as to expel the contents of the syringe through the needle, the housing having an opening at one end through which the needle may extend; a resilient member for biassing the syringe and needle inwardly of the I O housing; a drive element movable towards said one end so as to move the needle of the syringe out of the opening against the bias of the resilient member and to move the dispensing piston of the syringe towards the end surface; a delatch mechanism operable to release the syringe such that the needle 15 moves inwardly of the housing; a drive coupling for extending from said drive element to the dispensing piston of the syringe so as to transfer movement of said drive element to the dispensing piston; wherein the drive coupling is compressible in length whilst overcoming the bias of the 20 resilient member such that, after the drive element has moved the dispensing piston a/ to the end surface, the drive coupling gradually reduces in length whilst the dispensing piston is maintained at the end surface until said delatch mechanism releases the syringe.
2. An injection device according to claim I wherein the delatch 25 mechanism is operable when the drive element reaches a predetermined position in said housing and the drive coupling gradually reduces in length such that, aRer the dispensing piston reaches the end surface, the drive element continues to move in said housing to said predetermined position.
3. An injection device according to claim I or 2 wherein the drive 30 coupling includes:
( -21 a fluid chamber defined between first and second relatively movable walls, the first wall being movable by said drive element and said second wall being operable to move the dispensing piston; and a bleed orifice for bleeding fluid from the fluid chamber.
5
4. An injection device according to claim 3 wherein the drive coupling includes: a main body for mounting on the syringe relative to the bore and the needle, the main body having a peripheral wall defining an elongate passage within which the first and second walls are both movable, the fluid chamber being defined by the 10 peripheral wall and the first and second walls.
5. An injection device according to claim 4 wherein the bleed orifice is formed at a predetermined longitudinal position along the peripheral wall and is only exposed to the fluid chamber once the second wall passes the predetermined longitudinal position.
I 5
6. An injection device according to claim 3 including a syringe contained in the housing, the syringe having a bore extending from an end surface, a needle communicating with the bore through the end surface and a dispensing piston movable in said bore towards said end surface so as to expel the contents of the syringe through the needle wherein: 20 the drive coupling is formed in the syringe.
/
7. An injection device according to claim 6 wherein the first and second walls are movable in said bore and the fluid chamber is defined by the bore and the first and second walls.
8. An injection device according to claim 7 wherein the bleed orifice is 25 formed at a predetermined longitudinal position along the bore and is only opened to the fluid chamber once the second wall passes the predetermined longitudinal position.
9. An injection device according, to claim 5 or 8 wherein the bleed orifice has a cross-section which is elongate such that, as the second wall moves 30 towards the end surface, fluid bleeds faster from the fluid chamber.
-22
10. An injection device according to claim 5, 8 or 9 further including an array of bleed orifices extending towards said end surface such that, as the second wall moves towards the end surface, fluid bleeds faster from the fluid chamber.
11. An injection device according to claim 1 or 2 wherein the drive S coupling includes: a drive frictional surface engaging a driven frictional surface, the drive frictional surface being movable by said drive element and said driven frictional surface being operable to move the dispensing piston such that when the dispensing piston reaches the end surface the drive frictional surface slips relative to the driven 10 Fictional surface.
12. An injection device according to claim 11 wherein the drive frictional; surface is rotatable about an axis generally perpendicular to the surface and is moved by said drive element at a position offset from the axis.
13. An injection device according to claim I I or 12 wherein the driven 15 frictional surface is rotatable about an axis generally perpendicular to the surface and is operable to move the dispensing piston from a position offset from the axis.
14. An injection device according to claim I or 2 wherein the drive coupling includes: a rack; and 20 a pinion gear; wherein a/ one of the rack and the pinion gear is movable by said drive element and the other of the rack and the pinion gear is operable to move the dispensing piston.
15. An injection device according to claim 14 wherein the pinion gear includes a friction brake such that, when the dispensing piston reaches the end 25 surface, the friction brake slips.
16. An injection device according to claim 14 wherein the pinion gear drives a lly wheel such that, when the dispensing piston reaches the end surface, the pinion gear is turned against the inertial resistance of the fly wheel.
17. An injection device according to any preceding claim wherein the 30 drive coupling does not reduce in length until the dispensing piston has reached a position at least proximate the end surface.
-23
18. An injection device according to any one of claims 3 to 10 wherein the main body is fabricated out of plastic, for instance by injection moulding, and the bleed orifice is formed by drilling, for instance mechanically, fluid or laser, or in the injection moulding process itself.
5
19. An injection device according to any one of claims 3 to 10 further including an absorbent wicking material to retain fluid which has escaped from the bleed orifice.
20. A drive coupling for use in an injection device according to any preceding claim, the drive coupling having: 10 a length for extending from the drive element to the dispensing piston of the syringe so as to transfer movement of the drive element to the dispensing piston;; wherein the drive coupling is compressible in length whilst overcoming the bias of the resilient member such that, after the drive element has moved the dispensing piston 15 to the end surface, the drive coupling gradually reduces in length whilst the dispensing piston is maintained at the end surface until the delatch mechanism releases the syringe.
21. An injection device according to any one of claims 1 to 19 further including: 20 an engagement for transferring drive directly from the drive coupling to the it/ syringe body such that movement of the drive element towards said one end causes no relative movement of the dispensing piston in the syringe; wherein the engagement is releasable once the needle of the syringe extends out of the opening such that movement of the drive element towards said one end causes 25 relative movement of the dispensing piston in the syringe body.
22. An injection device including: a housing for containing a syringe having a bore extending in a syringe body from an end surface, a needle communicating with the bore through the end surface and a dispensing piston movable in said bore towards said end surface so as to expel 30 the contents of the syringe through the needle, the housing having an opening at one end through which the needle may extend;
( -24 a resilient member for biassing the syringe and needle inwardly of the housing; a drive element movable towards to said one end so as to move the needle of the syringe out of the opening against the bias of the resilient member and to move 5 the dispensing piston of the syringe towards the end surface, a drive coupling for extending from said drive element to the dispensing piston of the syringe so as to transfer movement of said drive element to the dispensing piston; and an engagement for transferring drive directly from the drive coupling to the O syringe body such that movement of the drive element towards said one end causes no relative movement of the dispensing piston in the syringe; wherein; the engagement is releasable once the needle of the syringe extends out of the opening such that movement of the drive element towards said one end causes relative movement of the dispensing piston in the syringe body.
15
23. An injection device according to claim 21 or 22 wherein the housing includes a release portion which interacts with the engagement to release drive to the syringe.
24. An injection device according to claim 23 wherein the release portion is located in the housing at a predetermined position and the engagement includes a 20 trigger which is operated by the release portion to release drive to the syringe upon I/ reaching the predetermined position.
25. An injection device according to claim 23 or 24 wherein the engagement includes a resilient latch and the resilient portion includes at least a recess in a wall of the housing allowing deflection of the resilient latch to release the 25 drive to the syringe.
26. An injection device according to claim 25 wherein the at least a recess engages the resilient latch so as to prevent further relative movement of the syringe body in the housing.
27. An injection device according to claim 25 or 26 wherein the drive 30 coupling includes a fluid chamber defined between first and second relatively
-25 movable walls, the first wall being part of a piston and the resilient latch operating on the piston.
28. An injection device according to claim 23 or 24 wherein: the drive coupling includes a rigid element extending from the drive element; S the engagement includes at least one protrusion on a surface of the rigid element and a latch fixed relative to the syringe body engaging the protrusion; and the release portion includes a stop on the housing for engaging the latch; wherein the rigid element moves the latch with the protrusion until the latch abuts the 10 stop, whereupon the latch releases from the protrusion.
29. An injection device according to claim 28 wherein the latch is deflected resiliently past the protrusion.
30. An injection device according to claim 28 wherein the latch is hinged as a cantilever at a point between an end engaging the protrusion and an opposite end 15 and wherein the stop deflects the opposite end so as to release engagement with the protrusion.
31. An injection device according to any one of claims 21 to 30 wherein the engagement releasably connects the drive coupling to the syringe.
32. An injection device according to any one of claims 21 to 30 wherein 20 the engagement releasably connects a part of the drive coupling movable with the drive element to a part of the drive coupling for mounting to the syringe in a fixed relative position to the needle.
33. An injection device constructed and arranged substantially as hereinbefore described with reference to and as illustrated by Figures 2 to 9 of the 25 accompanying drawings.
34. A drive coupling constructed and arranged substantially as hereinbefore described with reference to and as illustrated by Figures 2 to 9 of the accompanying drawings.
GB0210123A 2002-05-02 2002-05-02 Automatic injection device Withdrawn GB2388033A (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
GB0210123A GB2388033A (en) 2002-05-02 2002-05-02 Automatic injection device

Applications Claiming Priority (23)

Application Number Priority Date Filing Date Title
GB0210123A GB2388033A (en) 2002-05-02 2002-05-02 Automatic injection device
US10/513,159 US7476217B2 (en) 2002-05-02 2003-05-02 Injection device
AU2003229994A AU2003229994B2 (en) 2002-05-02 2003-05-02 Injection device
PCT/GB2003/001946 WO2003092771A1 (en) 2002-05-02 2003-05-02 Injection device
MXPA04010861A MXPA04010861A (en) 2002-05-02 2003-05-02 Injection device.
NZ53630603A NZ536306A (en) 2002-05-02 2003-05-02 Injection device
DK03722834T DK1503816T3 (en) 2002-05-02 2003-05-02 injection device
CA 2483935 CA2483935C (en) 2002-05-02 2003-05-02 Injection device
AT03722834T AT353021T (en) 2002-05-02 2003-05-02 injection device
DE2003611571 DE60311571T2 (en) 2002-05-02 2003-05-02 injection device
PT03722834T PT1503816E (en) 2002-05-02 2003-05-02 Injection device
CN 03812676 CN100444908C (en) 2002-05-02 2003-05-02 Injection device
EP20030722834 EP1503816B1 (en) 2002-05-02 2003-05-02 Injection device
ES03722834T ES2279947T3 (en) 2002-05-02 2003-05-02 Injection device.
JP2004500952A JP4413772B2 (en) 2002-05-02 2003-05-02 Injection device
EA200401459A EA006960B1 (en) 2002-05-02 2003-05-02 Injection device
KR1020047017648A KR101009270B1 (en) 2002-05-02 2003-05-02 Injection device
UA20041008850A UA79777C2 (en) 2002-05-02 2003-05-02 Injection device and dispensing piston for use in injection device
BRPI0309876A BRPI0309876B1 (en) 2002-05-02 2003-05-02 injection device and drive coupling for use in the same
BRPI0309876A BRPI0309876A2 (en) 2002-05-02 2003-05-02 injection device
ZA200408816A ZA200408816B (en) 2002-05-02 2004-11-01 Injection device.
IL16496904A IL164969A (en) 2002-05-02 2004-11-01 Injection device
CY20071100455T CY1107591T1 (en) 2002-05-02 2007-04-02 provision enchyseos

Publications (2)

Publication Number Publication Date
GB0210123D0 GB0210123D0 (en) 2002-06-12
GB2388033A true GB2388033A (en) 2003-11-05

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ID=9935991

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Application Number Title Priority Date Filing Date
GB0210123A Withdrawn GB2388033A (en) 2002-05-02 2002-05-02 Automatic injection device

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Country Link
GB (1) GB2388033A (en)
UA (1) UA79777C2 (en)
ZA (1) ZA200408816B (en)

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UA79777C2 (en) 2007-07-25
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