Patent Application
20240374838
The invention relates to an auto-injector for administering a dose of a liquid medicament.
Administering an injection is a process which presents a number of risks and challenges for users and healthcare professionals, both mental and physical.
Injection devices (i.e. devices capable of delivering medicaments from a medication container) typically fall into two categories-manual devices and auto-injectors.
In a manual device—the user must provide the mechanical energy to drive the fluid through the needle. This is typically done by some form of button/plunger that has to be continuously pressed by the user during the injection. There are numerous disadvantages to the user from this approach. If the user stops pressing the button/plunger then the injection will also stop. This means that the user can deliver an underdose if the device is not used properly (i.e. the plunger is not fully pressed to its end position). Injection forces may be too high for the user, in particular if the patient is elderly or has dexterity problems.
The extension of the button/plunger may be too great. Thus it can be inconvenient for the user to reach a fully extended button. The combination of injection force and button extension can cause trembling/shaking of the hand which in turn increases discomfort as the inserted needle moves.
Auto-injector devices aim to make self-administration of injected therapies easier for patients. Current therapies delivered by means of self-administered injections include drugs for diabetes (both insulin and newer GLP-1 class drugs), migraine, hormone therapies, anticoagulants etc.
Auto-injectors are devices which completely or partially replace activities involved in parenteral drug delivery from standard syringes. These activities may include removal of a protective syringe cap, insertion of a needle into a patient's skin, injection of the medicament, removal of the needle, shielding of the needle and preventing reuse of the device. This overcomes many of the disadvantages of manual devices. Injection forces/button extension, hand-shaking and the likelihood of delivering an incomplete dose are reduced. Triggering may be performed by numerous means, for example a trigger button or the action of the needle reaching its injection depth. In some devices the energy to deliver the fluid is provided by a spring.
US 2002/0095120 A1 discloses an automatic injection device which automatically injects a pre-measured quantity of fluid medicine when a tension spring is released. The tension spring moves an ampoule and the injection needle from a storage position to a deployed position when it is released. The content of the ampoule is thereafter expelled by the tension spring forcing a piston forward inside the ampoule. After the fluid medicine has been injected, torsion stored in the tension spring is released and the injection needle is automatically retracted back to its original storage position.
High viscosity medicaments require high forces for expelling them through the relatively thin injection needle. To achieve these forces strong drive springs are needed. This can lead to a high impact felt by the user when inserting the needle into the skin and to high forces felt by the user when triggering the injection.
It is an object of the present invention to provide an improved auto-injector.
The object is achieved by an auto-injector according to claim 1.
Preferred embodiments of the invention are given in the dependent claims.
In the context of this specification the term proximal refers to the direction pointing towards the patient during an injection while the term distal refers to the opposite direction pointing away from the patient. The term inwards refers to a radial direction pointing towards a longitudinal axis of the auto-injector whereas the term outwards refers to the opposite direction radially pointing away from the longitudinal axis.
According to the invention an auto-injector for administering a dose of a liquid medicament, comprises:
The control spring is arranged to bias the case against the chassis in a distal direction so as to extend the chassis out of a proximal end of the case. An insertion depth of the needle is defined by the carrier abutting the chassis in a predefined position. The case is arranged to release or allow release of the control spring for needle insertion on translation of the case in the proximal direction relative to the chassis against the bias into an advanced position.
In the context of this specification the chassis is generally considered as being fixed in position so motion of other components is described relative to the chassis.
The needle insertion depth is defined by the carrier relative to the chassis not relative to the case, so if the user flinches or fails to hold the auto-injector hard against the injection site, only the case will move in the distal direction while the injection depth remains constant as the chassis is still being pressed against the injection site by the control spring. Maintaining the insertion depth is thought to avoid unnecessary pain to a patient as opposed to the needle being translated back and forth if the user flinches, e.g. due to tremor.
The carrier may be arranged to be translated in the distal direction for retracting the inserted needle when the case is moved in the distal direction relative to the chassis by a predefined distance. Retraction may be achieved by the control spring being released from the carrier at its proximal end and switched to the chassis or case instead and by the distal end of the control spring being switched from the case to the carrier. As long as the case motion does not exceed the predefined distance the case does not yet switch the control spring for needle retraction, i.e. the user may move the case below this distance without triggering retraction or altering the insertion depth.
The auto-injector may furthermore comprise:
The carrier subassembly with the integrated drive spring allows for employing a strong drive spring without any impact on the user when triggering the auto-injector or during needle insertion since these actions are achieved or opposed by the control spring which can be specified considerably weaker than the drive spring. This allows for delivering highly viscous medicaments.
There are a number of significant benefits of separating the functions between the drive spring and the control spring in this way. The auto-injector is always needle safe, i.e. the needle can be retracted before the injection is complete. The reliability of the auto-injector is improved as the components for needle advance and retraction are not loaded by the high impact of a freely expanding high force drive spring. The auto-injector is well suited to serve as a platform as the drive spring can be swapped to deliver different viscosity drugs without affecting the insertion or retraction functions. This is particularly advantageous for high viscosity fluids.
Releasing the drive spring upon the needle reaching the insertion or injection depth avoids a so called wet injection, i.e. medicament leaking out of the needle which is a problem in conventional art auto-injectors, where both needle insertion and injection are achieved by pushing on the stopper. The auto-injector solves the wet injection problem by the separate springs for translation of the carrier and for drug delivery.
The auto-injector has a particularly low part count compared to most conventional auto-injectors thus reducing manufacturing costs. The arrangement with separate control spring and drive spring for fluid injection allows for using one design for different viscosity liquids by just changing the drive spring, and for different volumes just by changing the length of the plunger. This is an advantage over conventional art designs where the main spring also powers needle insertion and/or retraction.
In an initial as delivered state of the auto-injector the proximal end of the control spring is coupled to the chassis by the needle insertion control mechanism while the distal end is coupled to the case by the syringe retraction control mechanism, release of the drive spring is prevented by the plunger release mechanism, decoupling of the chassis from the carrier is prevented by the detent mechanism.
In order to trigger an injection the auto-injector has to be pressed against an injection site, e.g. a patient's skin. A user, e.g. the patient or a caregiver, grabs the case with their whole hand and pushes the chassis protruding from the proximal end against the injection site.
When pushed against the injection site, the case translates in the proximal direction relative to the chassis against the force of the control spring. When the case has at least almost reached an advanced position the detent mechanism is unlocked thereby allowing translation of the carrier relative to the chassis.
The carrier can now be translated, preferably manually by depressing the trigger button forcing the carrier in the proximal direction. The carrier translates in the proximal direction relative to the case and to the chassis thereby switching the needle insertion control mechanism depending on the relative position of the carrier in the chassis so as to decouple the proximal end of the control spring from the chassis and couple it to the carrier, thereby releasing the control spring for advancing the carrier for needle insertion.
Alternatively the control spring could initially be coupled to the carrier by the needle insertion control mechanism so that the carrier would be immediately advanced when the detent mechanism is unlocked by translation of the case into the advanced position.
As the needle translated with the carrier subassembly at least almost reaches an injection depth the drive spring is released by the plunger release mechanism thereby allowing the drive spring to advance the plunger and the stopper for at least partially delivering the medicament. The release of the drive spring is preferably triggered by the carrier reaching a predefined relative position within the case.
If the auto-injector is removed from the injection site after the stopper has bottomed out in the syringe or mid injection, the case is translated in the distal direction under load of the control spring relative to the carrier subassembly.
As the case reaches a defined position relative to the carrier during that motion the proximal end of the control spring is decoupled from the carrier and coupled to the chassis by the needle insertion control mechanism. Furthermore the distal end of the control spring is decoupled from the trigger sleeve and coupled to the carrier by the syringe retraction control mechanism. As the control spring now pushes against the chassis in the proximal direction and against the carrier in the distal direction the carrier subassembly is retracted into the chassis into a needle safe position by the control spring.
According to one embodiment the needle insertion control mechanism may comprise a first collar biased by the control spring in the proximal direction, wherein at least one resilient beam is proximally arranged on the first collar, wherein respective recesses are arranged in the carrier and case, wherein a transversal extension of a head of the resilient beam is wider than a gap between the carrier and the chassis causing the head of the resilient beam to abut a distal face on the recess in the chassis while being prevented from deflecting in an inward direction by the carrier or to abut a distal face on the recess in the carrier while being prevented from deflecting in an outward direction by the chassis thereby forwarding load from the control spring to the carrier for needle insertion, wherein the resilient beam is arranged to be switched between the chassis and the carrier by ramped engagement of the head to the distal faces under load of the control spring depending on the relative longitudinal position between the chassis and the carrier. As the head of the resilient beam may be inwardly and outwardly ramped it may be referred to as an arrowhead.
The plunger release mechanism may comprise at least one resilient arm on the carrier arranged to be in a ramped engagement to the plunger so as to disengage them under load of the drive spring, wherein a peg protrudes from a distal end face of the trigger button in the proximal direction in a manner to support the resilient arm preventing disengagement of the carrier from the plunger and thus release of the drive spring when the carrier is in a distal position. The trigger button is arranged to remain in position relative to the case when the carrier is translated for advancing the needle. That means, the trigger button, initially coupled to the carrier, pushes the carrier in the proximal direction when depressed. As soon as the control spring takes over further advancing the carrier the trigger button may abut the case and decouple from the carrier, staying in position as the carrier moves on. Hence the resilient arm is pulled away from the peg thus allowing deflection of the resilient arm due to the ramped engagement under load of the drive spring for disengaging the plunger from the carrier and releasing the drive spring for drug delivery when the carrier has reached a predefined position during needle advancement.
The detent mechanism may be arranged to provide a resistive force which has to be overcome to advance the carrier in the proximal direction for needle insertion. Once the user applies a force on the trigger button which exceeds a pre-determined value the detent mechanism releases, initiating the injection cycle. If the pre-determined value is not overcome the detent mechanism pushes the carrier and trigger button back into their prior position. This ensures that the auto-injector is always in a defined state, either triggered or not triggered, not half triggered by the user hesitating.
The detent mechanism may also be arranged to provide a resistive force resisting translation of the carrier in the distal direction relative to the chassis for keeping the carrier in a defined position in a transitional state with both ends of the control spring decoupled from the carrier. This transitional state may be required for retracting the needle on removal from the injection site. As the carrier is biased against the injection site by the control spring before removal from the injection site it has to be decoupled from the proximal end of the control spring and coupled to the distal end for retraction. The sequencing of this switching is critical as retraction will fail if both ends of the control spring are attached to the carrier at the same time. This is overcome by separating the switching of the ends by a significant displacement of the case, which moves in the distal direction relative to the chassis on removal of the injection site under load of the control spring. As the switching of the distal end of the control spring to the carrier depends on the relative position of the case to the carrier the carrier has to be fixed in the transitional state which is achieved by the detent mechanism.
In one embodiment the detent mechanism comprises a resilient beam on the chassis and a rhomboid ramp member on the carrier, the resilient beam being essentially straight when relaxed and having a first beam head arranged to interact in a ramped engagement with a proximal fourth ramp or a distal fifth ramp on the rhomboid ramp member in such a manner that application of a translative force on the carrier relative to the chassis in the proximal direction with the first beam head engaged to the fourth ramp deflects the resilient beam in one transversal direction, e.g. outwards when a predetermined value of the translative force, at least depending on the resilience of the resilient beam, is overcome so as to allow the first beam head to travel along one transversal side of the rhomboid ramp member on continued relative translation of the components. The beam head may protrude transversally from the resilient beam in a manner to distort the resilient beam by lever action when pushed against the rhomboid ramp member thereby also defining the predetermined value of the translative force to be overcome by the carrier. Furthermore, the contacting faces of the first beam head and the rhomboid ramp member may have their friction adapted to define the required force by appropriately choosing their shape and material properties. The resilient beam is allowed to relax when the first beam head has reached the fifth ramp thereby engaging it in a manner that application of a translative force on the carrier in the distal direction deflects the resilient beam in the other transversal direction, e.g. inwards when a predetermined value of the translative force, at least depending on the resilience of the resilient beam, is overcome so as to allow the first beam head to travel along the other transversal side of the rhomboid ramp member on continued translation of the carrier. The first beam head may also be allowed to relax behind the fourth ramp at the end of this motion for preventing the carrier from being advanced again, e.g. when the auto-injector is being heavily shaken after use.
It goes without saying that the positions of the resilient beam on the chassis and the rhomboid ramp member on the carrier may be switched without altering the function of the detent mechanism.
When the auto-injector or the syringe is assembled a protective needle sheath may be attached to the needle for keeping the needle sterile and preventing both, damage to the needle during assembly and handling and access of a user to the needle for avoiding finger stick injuries. Removal of the protective needle sheath prior to an injection usually requires a relatively high force for pulling the protective needle sheath off the needle and needle hub in the proximal direction. In order to maintain pre injection needle safety and prevent exposure of the needle translation of the syringe in the proximal direction due to this force has to be avoided. For this purpose the case may be arranged to lock the detent mechanism prior to being translated in the proximal direction relative to the chassis when the chassis is being pressed against the injection site so as to avoid translation of the carrier. This may be achieved by a rib in the case preventing deflection of the resilient beam of the detent mechanism by supporting it outwardly. Translation of the case is translated into the advanced position in the proximal direction on contact to the injection site is arranged to unlock the detent mechanism rendering it operable. This may be achieved by the rib being moved with the case so as to no longer outwardly supporting the resilient beam of the detent mechanism. In order to ensure that the case is not moved in the proximal direction unlocking the detent mechanism before the protective needle sheath is removed a cap may be attached to the proximal end of the case so as to make the chassis inaccessible before the cap is removed. The cap preferably engages the protective needle sheath by means of a barb in a manner to remove the protective needle sheath when the cap is being pulled off the auto-injector. In order to facilitate removal of the cap it may have a profiled surface mating with a surface on the case so that the cap is pulled off when rotated. The barb may be connected to the cap in a manner allowing them to rotate independently so as to avoid torque on the protective needle sheath when the cap is rotated in order not to distort the needle inside the protective needle sheath.
The distally arranged trigger button may be at least initially coupled to the carrier, wherein the case is arranged to abut the trigger button in the initial state preventing depression of the trigger button. On translation of the case into the advanced position when the chassis is being pressed against the injection site the trigger button remains coupled to the carrier thus emerging from the case which has been moved relative to the chassis, carrier and trigger button so as to allow depression of the trigger button for starting an injection cycle. Thus a sequence of operation is defined for the auto-injector to be actuated, first pressing it against the injection site and then to push the trigger button. This reduces the risk of finger stick injuries particularly if the user were to be confused which end of the auto-injector to apply against their skin. Without a sequence the user would risk inserting the needle into their thumb which is significantly less probable with the forced sequence.
The syringe retraction control mechanism may comprise a second collar bearing against the distal end of the control spring and having a resilient proximal beam with a second beam head having an inward boss. The second beam head is arranged to be in a ramped engagement with a second case detent in the case in a manner ramping the second beam head in the inward direction under load of the control spring in the distal direction. The inward boss is arranged to inwardly abut the carrier for preventing inward deflection of the second beam head and keep the second collar locked to the case. A third recess is arranged in the carrier for allowing the inward boss to be inwardly deflected on translation of the case in the distal direction relative to the carrier on removal of the auto-injector from the injection site.
In an alternative embodiment the first collar and/or the second collar may also be threaded to one of the components which they are intended to couple to the control spring wherein the case would be arranged to prevent the threads from decoupling in some relative longitudinal positions while allowing the collar to rotate out of the threaded engagement in other relative longitudinal positions so as to allow the collars to switch to the respective other component to be coupled to the control spring.
In an alternative embodiment the trigger button may be arranged distally, wherein the case is arranged as a wrap-over sleeve trigger having a closed distal end face covering the trigger button. In an initial state a clearance is provided between the distal end face of the sleeve trigger and the trigger button allowing for some travel of the sleeve trigger against the bias of the control spring in the proximal direction in a first phase before abutting the trigger button. As soon as the sleeve trigger has contacted the trigger button the trigger button is pushed by the sleeve trigger on further translation in a second phase. This embodiment allows for keeping the majority of the components of the auto-injector while only the described features need modification allowing to customize a platform device to particular requirements. An auto-injector with a sleeve trigger is particularly well suited for people with dexterity problems since, as opposed to conventional art auto-injectors, triggering does not require operation of small buttons by single fingers. Instead, the whole hand is used.
Retraction of the needle requires the user to lift the auto-injector far enough from the injection site to allow the case or sleeve trigger to translate back in the distal direction to switch the control spring. As it may be difficult for the user to know if the injection is finished or not a releasable noise component may be provided, capable of, upon release, generating an audible and/or tactile feedback to the user, wherein the noise component is arranged to be released when the plunger reaches a position relative to the syringe in which the stopper is located in proximity of a proximal end of the syringe, i.e. when the injection is at least almost finished. The released noise component then impacts on a housing component, such as the case, sleeve trigger or trigger button indicating the end of the injection. Impacting a directly accessible component allows for high perceptibility of the noise and direct access to the user's hand or finger for generating the tactile feedback. Preferably the noise component may impact the trigger button which may be shaped as a drum for providing a loud noise.
The auto-injector may be operated by a number of key mechanical operations:
The auto-injector may preferably be used for subcutaneous or intra-muscular injection, particularly for delivering one of an analgetic, an anticoagulant, insulin, an insulin derivate, heparin, Lovenox, a vaccine, a growth hormone, a peptide hormone, a proteine, antibodies and complex carbohydrates.
The term “medicament”, as used herein, means a pharmaceutical formulation containing at least one pharmaceutically active compound,
Insulin analogues are for example Gly (A21), Arg (B31), Arg (B32) human insulin; Lys (B3), Glu (B29) human insulin; Lys (B28), Pro (B29) human insulin; Asp (B28) human insulin; human insulin, wherein proline in position B28 is replaced by Asp, Lys, Leu, Val or Ala and wherein in position B29 Lys may be replaced by Pro; Ala (B26) human insulin; Des (B28-B30) human insulin; Des (B27) human insulin and Des (B30) human insulin.
Insulin derivates are for example B29-N-myristoyl-des (B30) human insulin; B29-N-palmitoyl-des (B30) human insulin; B29-N-myristoyl human insulin; B29-N-palmitoyl human insulin; B28-N-myristoyl LysB28ProB29 human insulin; B28-N-palmitoyl-LysB28ProB29 human insulin; B30-N-myristoyl-ThrB29LysB30 human insulin; B30-N-palmitoyl-ThrB29LysB30 human insulin; B29-N—(N-palmitoyl-Y-glutamyl)-des (B30) human insulin; B29-N—(N-lithocholyl-Y-glutamyl)-des (B30) human insulin; B29-N-(ω-carboxyheptadecanoyl)-des (B30) human insulin and B29-N-(ω-carboxyheptadecanoyl) human insulin.
Exendin-4 for example means Exendin-4 (1-39), a peptide of the sequence H-His-Gly-Glu-Gly-Thr-Phe-Thr-Ser-Asp-Leu-Ser-Lys-Gln-Met-Glu-Glu-Glu-Ala-Val-Arg-Leu-Phe-Ile-Glu-Trp-Leu-Lys-Asn-Gly-Gly-Pro-Ser-Ser-Gly-Ala-Pro-Pro-Pro-Ser-NH2.
Exendin-4 derivatives are for example selected from the following list of compounds:
Hormones are for example hypophysis hormones or hypothalamus hormones or regulatory active peptides and their antagonists as listed in Rote Liste, ed. 2008, Chapter 50, such as Gonadotropine (Follitropin, Lutropin, Choriongonadotropin, Menotropin), Somatropine (Somatropin), Desmopressin, Terlipressin, Gonadorelin, Triptorelin, Leuprorelin, Buserelin, Nafarelin, Goserelin.
A polysaccharide is for example a glucosaminoglycane, a hyaluronic acid, a heparin, a low molecular weight heparin or an ultra low molecular weight heparin or a derivative thereof, or a sulphated, e.g. a poly-sulphated form of the above-mentioned polysaccharides, and/or a pharmaceutically acceptable salt thereof. An example of a pharmaceutically acceptable salt of a poly-sulphated low molecular weight heparin is enoxaparin sodium.
Pharmaceutically acceptable salts are for example acid addition salts and basic salts. Acid addition salts are e.g. HCl or HBr salts. Basic salts are e.g. salts having a cation selected from alkali or alkaline, e.g. Na+, or K+, or Ca2+, or an ammonium ion N+(R1)(R2)(R3)(R4), wherein R1 to R4 independently of each other mean: hydrogen, an optionally substituted C1-C6-alkyl group, an optionally substituted C2-C6-alkenyl group, an optionally substituted C6-C10-aryl group, or an optionally substituted C6-C10-heteroaryl group. Further examples of pharmaceutically acceptable salts are described in “Remington's Pharmaceutical Sciences” 17. ed. Alfonso R. Gennaro (Ed.), Mark Publishing Company, Easton, Pa., U.S.A., 1985 and in Encyclopedia of Pharmaceutical Technology.
Pharmaceutically acceptable solvates are for example hydrates.
The drive spring and control spring may be compression springs. However, they may likewise be any kind of stored energy means such as torsion springs, gas springs etc.
Further scope of applicability of the present invention will become apparent from the detailed description given hereinafter. However, it should be understood that the detailed description and specific examples, while indicating preferred embodiments of the invention, are given by way of illustration only, since various changes and modifications within the spirit and scope of the invention will become apparent to those skilled in the art from this detailed description.
The present invention will become more fully understood from the detailed description given hereinbelow and the accompanying drawings which are given by way of illustration only, and thus, are not limitive of the present invention, and wherein:
Corresponding parts are marked with the same reference symbols in all figures.
A ramped engagement in the terminology of this specification is an engagement between two components with at least one of them having a ramp for engaging the other component in such a manner that one of the components is flexed aside when the components are axially pushed against each other provided this component is not prevented from flexing aside.
A drive spring 8 in the shape of a compression spring is arranged in a distal part of the carrier 7. A plunger 9 serves for forwarding the force of the drive spring 8 to the stopper 6.
The drive spring 8 is loaded between a distal carrier end face 10 of the carrier 7 and a thrust face 11 arranged distally on the plunger 9.
The carrier 7 is a key element housing the syringe 3, the drive spring 8 and the plunger 9, which are the components required to eject the medicament M from the syringe 3. These components can therefore be referred to as a drive sub-assembly.
The chassis 2 and the carrier 7 are arranged within a tubular case 12. A trigger button 13 is arranged at a distal end of the case 12. In a plunger release mechanism 27 a peg 14 protrudes from a distal end face of the trigger button 13 in the proximal direction P between two resilient arms 15 originating from the distal carrier end face 10 thus preventing them from flexing towards each other in an initial state A illustrated in
The carrier 7 is locked to the chassis 2 for preventing relative translation by a detent mechanism 18 illustrated in more detail in
The trigger button 13 is initially engaged to the case 12 by a button release mechanism 26 and cannot be depressed. The button release mechanism 26 is illustrated in detail in
Referring again to
In the state as delivered as shown in
A sequence of operation of the auto-injector 1 is as follows:
A user pulls the cap 22 from the proximal end of the case 12. The barb 23 joins the protective needle sheath 5 to the cap 22. Hence, the protective needle sheath 5 is also removed on removal of the cap 22.
Referring again to
Referring again to
Referring again to
In the state as in
In the state as in
Once the carrier 7 slides far enough in the proximal direction P relative to the first collar 20 the needle insertion control mechanism 24 is switched to a state B as illustrated in
The detent mechanism 18 relies on the user applying a force rather than a displacement. Once the force applied exceeds the force required to switch the detent the user will push the trigger button 13 fully, ensuring that the first collar 20 will always switch. If the user fails to pass the detent, the trigger button 13 returns to its unused state ready for use as illustrated in
The carrier 7 coupled to the first collar 20 is translated in the proximal direction P driven by the control spring 19. As the syringe 3 is arranged for joint axial translation with the carrier 3 the syringe 3 and needle 4 are also translated resulting in the needle 4 protruding from the proximal end P and being inserted into the injection site. The trigger button 13 returns to its initial position relative to the case 12 and latches back to the case 12 from the carrier 7 as in state A in
Immediately prior to the needle 4 reaching full insertion depth as illustrated in
While the plunger 9 moves and closes a gap to the stopper 6 the movement of the carrier 7 in the proximal direction P is completed by the control spring 19 pushing the first collar 20. As the carrier 7 moves with respect to the chassis 2 during needle insertion the needle insertion mechanism 24 arrives in a state D illustrated in
The needle 4 is now fully inserted into the injection site as illustrated in
As soon as the plunger 9 has closed the gap to the stopper 6 under force of the drive spring 8 the stopper 6 is pushed in the proximal direction P within the syringe 3 displacing the medicament M through the needle 4 into the injection site.
Immediately prior to the end of injection with the stopper 6 having almost bottomed out in the syringe 3 as illustrated in
Note: the noise component 28 is not illustrated in
As mentioned above the user is able to let the case 12 move by a few millimetres in the distal direction D under the force of the control spring 19 without affecting the position of the needle 4 as long as that motion is below a predefined distance. If the user wishes to end the injection, at any time, they must allow the case 12 to move in the distal direction D beyond that distance.
The switching of the first collar 20 is illustrated in
As the case 12 is moving further in the distal direction D on removal from the injection site the syringe retraction control mechanism 25 switches from its state A (cf.
Starting from the position C of the detent mechanism 18 (cf.
The control spring 19 is grounded at its proximal end in the case by the first collar 20 being abutted against the chassis 2. The distal end of the control spring 19 moves the second collar 21 in the distal direction D taking with it the carrier 7 and hence the syringe 3 with the needle 4 overcoming the detent mechanism 18 as illustrated in
As the movement allowed of the noise component 28 is limited relative to the carrier 7 it is no longer in contact with the trigger button 13 which has moved in the distal direction D with the case 12 on removal from the injection site. When the retraction begins the noise spring 29 does not provide any retarding force. Once the noise component 28 hits the trigger button 13 again on retraction of the carrier 7 the noise spring 29 must be recompressed, reducing the force driving the final part of retraction. In order to ensure a reliable retraction despite this reducing force the control spring 19 must be appropriately dimensioned.
The retraction ends when the distal collar 21 meets a first back stop 12.4 on the case 12 as in
The detent mechanism 18 returns to state A as in
A tab 20.4 on the first collar 20 is now visible through an indicator window 32 in the case 12—indicating the auto-injector 1 has been used.
In the embodiment of
The button release mechanism 26 illustrated in
The first clip 7.12 is arranged as an outwardly biased resilient beam on the carrier 7 extending from the carrier 7 in the proximal direction P. the first clip 7.12 is arranged to prevent the carrier 7 from being moved in the proximal direction P prior to the chassis 2 being depressed or rather the case 12 being translated on skin contact. The first clip 7.12 is composed of two sections side by side. A first section 7.14 prevents movement of the carrier 7 in the proximal direction P by abutting the chassis 2 in a recess. A second section 7.15 is arranged as an outwardly protruding clip head arranged to be ramped inwards by a ramp feature 12.6 on the chassis 12 for releasing the first clip 7.12 thereby unlocking the carrier 7 from the chassis 2 when the case 12 is being translated in the proximal direction P on skin contact. A longitudinal slot 2.7 in the chassis 2 is arranged for allowing the second section 7.15 to slide in the proximal direction P once the lock has been released. A slight friction force between the first clip 7.12 and the chassis 2 provides the retarding force required to ensure retraction.
The second clip 7.13 is arranged as a resilient beam on the carrier 7 extending in the distal direction D having an outwardly protruding third beam head 7.16 with a proximal ramp. The third beam head 7.16 serves as a back stop against a third rib 2.9 on the chassis 2 for preventing the carrier 7 moving in the distal direction D from its initial position. The carrier 7 and chassis 2 are assembled with the second clip 7.13 in this position prior to inserting the syringe 3 into the carrier 7 which is facilitated by the proximal ramp on the third beam head 7.16. The syringe 3 locks the clip in place by preventing inward deflection thus creating a fixed stop.
The third clip 2.6 is a resilient beam on the chassis 2 extending in the distal direction D. A ramped fourth beam head 2.8 on the third clip 2.6 is arranged to inwardly engage in a fifth recess 7.17 in the carrier 7. Once the first clip 7.12 is unlocked, the user can load the third clip 2.6 by pressing the carrier 7 in the proximal direction P on depression of the trigger button 13. The third clip 2.6 is loaded in compression, i.e. it will bend outwards and release suddenly due to its ramped engagement to the carrier 7 providing the detent functionality similar to that illustrated in
A fifth clip 2.10 on the chassis 2 abuts a block 20.7 on the first collar 20 prior to use preventing the first collar 20 and hence the carrier 7 engaged to the first collar 20 from moving in the proximal direction P. In order to release, the fifth clip 2.10 must be deflected outwards and over the block 20.7. Outward deflection of the fifth clip 2.10 is initially prevented by the case 12. Once the case 12 has moved on skin contact a second window 12.8 in the case 12 appears outwardly from the fifth clip 2.10 allowing outward deflection. The fifth clip 2.10 is then deflected by a fourteenth ramp 7.19 on the carrier 7 when the carrier 7 is pushed in the proximal direction P on button depression as the fourth clip 20.5 does allow translation of the carrier 7 in the proximal direction P relative to the first collar 20 but not the other way round. The detent for needle insertion is provided by having to deflect the fifth clip 2.10 when it is loaded by the control spring 19.
The fourth clip 20.5 is identical to that in
The fifth clip 2.10 provides the detent for needle insertion and releases the first collar 20 from the chassis 2, initiating needle insertion. The fifth clip 2.10 prevents the first collar 20 and hence the carrier 7 engaged to the first collar 20 from moving in the proximal direction P prior to use by abutting the block 20.7 on the chassis 2. In order to release, the fifth clip 2.10 must be deflected outwards and over the block 20.7. Outward deflection of the fifth clip 2.10 is initially prevented by the case 12. Once the case 12 has moved on skin contact the second window 12.8 in the case 12 appears outwardly from the fifth clip 2.10 allowing outward deflection. The fifth clip 2.10 is then deflected by the fourteenth ramp 7.19 on the carrier 7 when the carrier 7 is pushed in the proximal direction P on button depression as the fourth clip 20.5 does allow translation of the carrier 7 in the proximal direction P relative to the first collar 20 but not the other way round. The detent for needle insertion is provided by having to deflect the fifth clip 2.10 when it is loaded by the control spring 19.
The wrap-over sleeve trigger 12 is the same component as the case 12 which has a closed distal end face 12.10 other than the one in
As the auto-injector 1 does not differ from the auto-injector of
As the chassis 2 is placed against the injection site the sleeve trigger 12 translates in the proximal direction P relative to the chassis 2 into the advanced position in a first phase of sleeve travel removing the clearance 33 between the distal end face 12.10 of the sleeve trigger 12 and the internal trigger button 13. As in the embodiment of
From a user perspective, the detent mechanism 18 is arranged to provide a resistive force when the user reaches the second phase of sleeve travel. Internally, there is no difference to the embodiment of
Needle insertion is triggered by the user fully advancing the sleeve trigger 12 in the second phase of sleeve travel thereby fully depressing the internal trigger button 13 and overcoming the detent mechanism as in the embodiment of
As the control spring 19 takes over on button depression fully advancing the carrier 7 for needle insertion the internal trigger button 13 bottoms out on an internal fifth rib 12.11 in the sleeve trigger 12 and the internal trigger button 13 switches back to being locked to the sleeve trigger 12 as in
The embodiment of
It goes without saying that in all ramped engagements between two components described in the above embodiments there may be just one ramp on one or the other component or there may be ramps on both components without significantly influencing the effect of the ramped engagement.
| Number | Date | Country | Kind |
|---|---|---|---|
| 11155040.6 | Feb 2011 | EP | regional |
The present application is a continuation of U.S. patent application Ser. No. 18/487,215, filed Oct. 16, 2023, which is a continuation of U.S. patent application Ser. No. 17/126,962, filed Dec. 18, 2020, now U.S. Pat. No. 11,819,670, which is a continuation of U.S. patent application Ser. No. 15/897,872, filed Feb. 15, 2018, now U.S. Pat. No. 10,894,132, which is a continuation of U.S. patent application Ser. No. 13/983,809, filed Aug. 6, 2013, now U.S. Pat. No. 9,925,344, which is a U.S. National Phase application pursuant to 35 U.S.C. § 371 of International Application No. PCT/EP2012/052647 filed Feb. 16, 2012, which claims priority to European Patent Application No. 11155040.6 filed Feb. 18, 2011. The entire disclosure contents of these applications are herewith incorporated by reference into the present application.
| Number | Date | Country | |
|---|---|---|---|
| Parent | 18487215 | Oct 2023 | US |
| Child | 18755814 | US | |
| Parent | 17126962 | Dec 2020 | US |
| Child | 18487215 | US | |
| Parent | 15897872 | Feb 2018 | US |
| Child | 17126962 | US | |
| Parent | 13983809 | Aug 2013 | US |
| Child | 15897872 | US |
