Drug delivery device comprising a prism

Abstract

The present disclosure relates to a drug delivery device comprising a dose setting member for setting user variable doses of a medicament and a display for indicating the dose set by the dose setting member. The display comprises a number wheel, which is rotationally coupled to the dose setting member and is provided with a series of markings on its outer circumference, and at least one prism deviating the image of the markings of the number wheel, e.g. by 90°.

Claims

1. A drug delivery device comprising: a dose setting member for setting variable doses of a medicament; and a display for indicating a dose set by the dose setting member, wherein the display comprises a number wheel rotationally coupled to the dose setting member and rotatable about an axis, the number wheel comprising an outer circumference comprising a series of markings; and at least one prism configured to deviate an image of the series of markings of the number wheel, wherein the series of markings of the number wheel are visible on the display when viewed through the at least one prism, and wherein the at least one prism is arranged such that the image of the series of markings of the number wheel is deviated to be viewed in a direction parallel to the axis of the number wheel.

2. The drug delivery device according to claim 1, wherein the at least one prism is a triangular prism, and the series of markings is provided mirrored on the outer circumference of the number wheel.

3. The drug delivery device according to claim 1, wherein the at least one prism comprises a penta-prism, and the series of markings is provided non-mirrored on the outer circumference of the number wheel.

4. The drug delivery device according to claim 1, wherein the at least one prism magnifies the series of markings on the number wheel.

5. The drug delivery device according to claim 1, comprising a housing having a longitudinal axis defined by a compartment, the compartment configured to receive a cartridge, wherein the dose setting member is configured to rotate within the housing about an axis of rotation, wherein the axis of rotation is perpendicular to the longitudinal axis of the housing.

6. The drug delivery device according to claim 1, comprising a drive mechanism, the drive mechanism comprising: a plunger configured to act on a bung of a cartridge; a pressure spring configured to act on the plunger; a retaining member coupled to the plunger; and a release member operable between a first state and a second state, wherein in the first state the release member is rotationally constrained, and in the second state the release member is rotatable, thus allowing movement of the plunger.

7. The drug delivery device of claim 6, wherein the retaining member is a flexible belt or cable.

8. The drug delivery device of claim 6, wherein the retaining member is attached to and wound on a drum which is in gear engagement with the release member.

9. The drug delivery device according to claim 6, wherein the dose setting member is configured to rotate relative to the release member during the dose setting and is configured to rotate together with the release member during a dose dispensing.

10. The drug delivery device according to claim 6, wherein rotation of the dose setting member is limited by a plurality of rotational stops defining a minimum dose position and a maximum dose position.

11. The drug delivery device according to claim 6, comprising a trigger being axially movable in the direction of an axis of rotation of the dose setting member, wherein actuation of the trigger switches the release member between the first state and the second state.

12. The drug delivery device according to claim 6, comprising: a dose dial grip; and a clutch, wherein the clutch rotationally couples the dose dial grip to the dose setting member during the dose setting, and the clutch rotationally de-couples the dose dial grip from the dose setting member and rotationally couples the dose setting member to the release member during a dose dispensing.

13. The drug delivery device according to claim 6, comprising a nut, wherein the nut is guided axially displaceable and non-rotatable with respect to one of the dose setting member and the release member, and the nut is in threaded engagement with the other of the dose setting member and the release member such that relative rotation between the dose setting member and the release member during the dose setting causes the nut to move towards an end stop.

14. The drug delivery device according to claim 13, wherein the nut prevents setting of a dose exceeding an amount of the medicament in the cartridge.

15. The drug delivery device according to claim 1, comprising a cartridge containing the medicament.

16. The drug delivery device according to claim 15, wherein the medicament comprises a pharmaceutically active compound.

17. The drug delivery device according to claim 1, wherein the at least one prism deviates the image of the series of markings of the number wheel by 90°.

Description

BRIEF DESCRIPTION OF THE FIGURES

(1) The present disclosure will now be described in further detail with reference to the accompanying schematic drawings, wherein

(2) FIG. 1 shows an exploded view of an injection device comprising a drive mechanism,

(3) FIG. 2 shows a perspective view of the device of FIG. 1,

(4) FIG. 3 shows a top view of components of the drive mechanism of FIG. 1,

(5) FIG. 4 shows a bottom view of components of the drive mechanism of FIG. 1,

(6) FIG. 5 shows a perspective view of components of the drive mechanism of FIG. 1,

(7) FIGS. 6a, 6b show sectional views of components of the device of FIG. 1,

(8) FIGS. 7a, 7b show details of the device of FIG. 1 in the minimum dose position and in the maximum dose position,

(9) FIG. 8 shows a detail of the device of FIG. 1,

(10) FIG. 9 shows a detail of the device of FIG. 1 in the dose setting condition,

(11) FIG. 10 shows a detail of the device of FIG. 1 in the dose dispensing condition,

(12) FIG. 11 shows a detail of the device of FIG. 1,

(13) FIG. 12 shows a sectional view of a detail of the device of FIG. 1,

(14) FIG. 13 shows the device of FIG. 1 with an empty cartridge,

(15) FIG. 14 shows the device of FIG. 1 with an empty cartridge,

(16) FIG. 15 shows the device of FIG. 1 with a full cartridge prior to dose setting,

(17) FIG. 16 shows the device of FIG. 1 with a full cartridge prior to dose setting,

(18) FIG. 17 shows the device of FIG. 1 with a full cartridge with maximum dose set,

(19) FIG. 18 shows the device of FIG. 1 with a full cartridge with maximum dose set,

(20) FIGS. 19a to 19c show a trigger actuation sequence of the device of FIG. 1,

(21) FIGS. 20a, 20b show details of the device of FIG. 1,

(22) FIGS. 21a to 21c show an end of dose click sequence of the device of FIG. 1,

(23) FIGS. 22a to 22c sectional views of a detail of a drug delivery device according to a second embodiment,

(24) FIG. 23 shows a partially cut-open side view of an injection device according to a further embodiment of the disclosure, and

(25) FIG. 24 shows a perspective view of the cartridge holder with attached prism of the embodiment of FIG. 23.

DETAILED DESCRIPTION

(26) FIGS. 1 and 2 show views of the drug delivery device. FIG. 1 illustrates the component parts incorporated into the injection device which are a body 10, a cartridge holder 20, a trigger 40, a dial member 50 comprising a dial 51 and a dial cover 52 a medicament cartridge 30, a last dose nut 60, a dial gear 70, a trigger spring 80, a prism 90, a number wheel 100, a release gear 110, a belt assembly 120, a belt gear 130, a main spring 140 and a chassis 150.

(27) The body 10 and the cartridge holder 20 form a housing which has a distal end at the side receiving the cartridge 30 (right hand side in FIG. 2) and an opposite proximal end. The cartridge holder defines a longitudinal axis of the housing. A rotational axis is provided perpendicular to this longitudinal axis with the trigger 40, the dial member 50, the last dose nut 60, the dial gear 70, the trigger spring 80, the number wheel 100 and the release gear 110 are arranged concentrically about this rotational axis.

(28) The medicament cartridge 30 is housed within the cartridge holder 20. The cartridge holder 20 is rigidly constrained in the body 10. The cartridge holder 20 provides location and containment of the medicament cartridge and prism 90.

(29) The belt assembly 120 comprises a belt 121 and a plunger 122. The belt 121 is a flexible element with high tensile modulus and strength. Suitable materials include glass or aramid fibre reinforced poly-urethane. Features at each end of the belt 121 provide axial constraint and allow it to carry a tensile load. The distal end of the belt 121 is connected to the plunger 122 via spline features as shown in FIG. 3. The opposite end of the belt 121 is restrained by the belt gear 130 and partially wound onto it. FIG. 3 shows the belt 121 assembled to the belt gear 130 in the “as delivered” condition (prior to any doses being delivered).

(30) The distal face of the plunger 122 abuts a bung of the medicament cartridge 30 and the main spring 140 acts directly on the proximal surface of the plunger 122. It is the main spring 140 acting on the plunger 122 that drives the bung axially in order to deliver medicament. Tension in the belt 121 prevents the main spring 140 releasing and, therefore, by controlling the release of the belt 121, accurate control of the medicament delivery can be achieved. FIG. 4 shows the main spring 140 in its fully compressed state, i.e. the state prior to dispensing the first dose, interposed between the plunger 122 and a bearing face of the chassis 150. The belt 121 is held in tension by the main spring 140 and follows a curved path in the device defined by a belt guide feature 151 on the chassis 150.

(31) The main spring 140 is supplied to the user in the fully charged state (near “coil bound”). It acts between the proximal face of the plunger 122 and an abutment on the chassis 150. Tension in the belt 121 prevents the energy stored in the main spring 140 from being released until a dose is dispensed.

(32) The belt gear 130 controls release of the belt 121 through a geared interface with a pinion 111 of the release gear 110. It is radially constrained by the chassis 150 via a combination of abutments. The combined effect of these abutments ensure that the resultant force acting on the belt gear 130 from the belt 121 biases the geared interface with pinion 111 of the release gear 110 into engagement as shown in FIG. 5. This acts to minimize backlash between the gears and also reduce the risk of disengagement in the event of shock loading.

(33) The chassis 150 locates the mechanism within the body 10 and is rigidly fixed into the body 10 via spline and spring clip features. It provides location for the belt gear 130 and belt 121. Flexible features within the chassis 150 (chassis locking arms 152) fix the release gear 110 rotationally during dialing (FIG. 6a) but disengage to allow rotation during triggering (FIG. 6b). Abutments adjacent to these chassis locking arms 152 provide tangential support and prevent excessive deflection when loaded by the release gear 110.

(34) The number wheel 100 incorporates stop features 101, 102 which engage with abutments 153, 154 on the chassis 150 and correspond with the minimum (FIG. 7a) and maximum (FIG. 7b) dose set. This restricts the maximum dose that may be set and creates the end of dose stop when the mechanism returns to the zero unit position. The number wheel 100 is printed with a series of numbers on the external surface which create the dose display when viewed through the prism 90. The number wheel 100 is rotationally coupled to the dial gear 70 as shown in FIG. 8. Further, the number wheel is axially located between the chassis 150 and the body 10 and radially constrained by the body 10.

(35) The dose set is displayed on the outer surface of the device to provide feedback to the user. In this embodiment, the prism 90 reflects the display from the number wheel 100 so that the dose is displayed on the front face of the device (upper side in FIG. 2). The prism 90 is retained within the cartridge holder 20 and body 10 once assembled as shown in FIG. 10. The prism 90 uses the phenomenon of “Total Internal Reflection” to achieve reflection of the number without any special treatment to the surfaces (such as metal coating). The nature of this prism is that the display is mirrored. To account for this, the printing on the number wheel 100 is reversed so the net effect provides a conventional dose number display. An additional function of the prism 90 is that the surfaces can be designed to also provide magnification, in addition to the primary function of reflection.

(36) Alternative prism arrangements (for example a penta-prism) could perform the same function without mirroring the display if required. An alternative embodiment negates the requirement for the prism 90 component and displays the dose on the side of the device. The number wheel 100 is then printed with conventional, non-mirrored, text and a small window is formed in the side of the body 10.

(37) The dial gear 70 is rotationally coupled to the dial member 50 during dialing (FIG. 9) and rotationally coupled to the release gear 110 during dispense (FIG. 10). The dial gear 70 may translate axially between abutments provided by the release gear 110 and the dial member 50 and is biased into contact with the dial member 50 via the trigger spring 80 when the trigger 40 is not depressed. The trigger spring 80 acts between the dial gear 70 and release gear 110. The chassis locking arms 152 are axially coupled to the dial gear 70 with snap clips which permit relative rotation.

(38) The dial member 50 comprises the dial 51 and the dial cover 52 which are permanently and rigidly fixed together. The dial member 50 is axially and radially located in the body 10 via snap clips and the rotational position is detented via a flexible cantilever arm 53 locating in radial ratchet teeth 11 within the body 10 (FIG. 11). These detent features provide positive feedback to the user during dialing and align the dial member 50 and number wheel 100 with the body 10 so the units of the dose display accurately align with the prism 90.

(39) The trigger 40 is snap fitted into the dial member 50 and axially constrained between abutments on the dial member 50 and dial gear 70. The user may axially translate the trigger 40 between these abutments by overcoming the force of the trigger spring 80 which is transferred through the dial gear 70 (FIG. 12).

(40) During dose setting, the release gear 110 is in toothed engagement with the belt gear 130 and rotationally fixed by the chassis locking arms 152. When the trigger 40 is depressed, the release gear 110 is rotationally coupled to the dial gear 70 and is released from the chassis locking arms 152. It is axially constrained between the dial gear 70 and chassis 150 and is biased toward the chassis 150 abutment by the trigger spring 80.

(41) The mechanism incorporates a last dose nut 60 to prevent setting of a dose greater than that which remains within the medicament cartridge. This is positioned between the dial gear 70 and release gear 110 since the dial gear 70 rotates relative to the release gear 110 during dose set and not during dispense. The last dose nut 60 is splined to the inner surface of the dial gear 70 and threaded to the release gear 110 such that clockwise rotation of the dial member 50 rotates the last dose nut 60 and translates it towards the last dose stop on the release gear 110.

(42) The last dose nut 60 is successively translated towards the stop as doses are set until the cartridge dose limit is reached. At this point the last dose nut 60 contacts the abutment 112 on the release gear 110 which prevents further clockwise rotation of the last dose nut 60 and, therefore, rotation of the dial gear 70 and dial member 50. FIGS. 13 and 14 show the device shortly before the nut contacts abutment 112. The number of permissible rotations of the last dose nut 60 is determined by the capacity of the cartridge 30.

(43) The dial member 50 is rotated by the user in a clockwise direction to set a dose starting from the position shown in FIGS. 15 and 16. The dose can be cancelled by rotating the dial member 50 in a counter-clockwise direction either before any dispense or, alternatively, if the trigger 40 is released mid-dispense, the remaining dose may be cancelled.

(44) The selected dose is displayed through the body 10 via the number wheel 100 and prism 90 as described previously. Irrespective of whether the dial member 50 is rotated clockwise or counter-clockwise the dose displayed will always indicate the dose to be dispensed. In addition, the dose display also decrements as the dose is dispensed and thus displays the dose remaining to be dispensed. As the dose is dialed up the number wheel 100 is driven away from the zero unit stop 153 on the chassis 150 and towards the maximum unit stop 154. The dial member 50 can be rotated by the user in both clockwise and counter-clockwise directions when the number wheel 100 is not in contact with the zero dose stop abutment 153 or maximum dose stop abutment 154 of the chassis 150. The zero unit abutment 153 prevents counter-clockwise rotation of the dial member 50 below the zero unit position. The maximum dose abutment 154 prevents setting of a dose greater than the mechanism maximum which is depicted in FIGS. 17 and 18.

(45) The detent features 11, 53 between dial member 50 and body 10 controls the position of the dial member 50 to ensure that discrete units are selected and that the spline features between dial member 50 and release gear 110 are correctly aligned to permit spline meshing when the device is triggered.

(46) During dose setting, the release gear 110 is biased by the trigger spring 80 into engagement with the locking arms 152, which then couple the release gear 110 to the chassis 150. The release gear 110 is therefore fixed rotationally during dose set. This in turn prevents rotation of the belt gear 130 and, therefore, release of the belt 121.

(47) The device may be triggered by the user through application of an axial force on the trigger 40 (FIG. 19a). The trigger 40 acts on the dial gear 70, translating the dial gear 70 and chassis locking arms 152, compressing the trigger spring 80. As the dial gear 70 translates it first decouples from the dial member 50 as the face teeth disengage. At this stage (mid trigger position, FIG. 19b) the dial member 50 can no longer be rotated in either direction since the dial member 50 detent arm 53 is prevented from deflecting by an annular abutment on the dial gear 70. Further translation of the trigger 40 couples the dial gear 70 to release gear 110 via splines and finally decouples the release gear 110 from the chassis 150 (FIG. 19c).

(48) On triggering, the release gear 110 rotates, controlled by the dial gear 70 and number wheel 100. The belt gear 130 rotates, due to the torque generated by the main spring 140 acting through the belt 121. As the main spring 140 extends, the plunger 122 is driven against the bung, creating a distal translation and causing medicament to be dispensed. Since the release gear 110, dial gear 70 and number wheel 100 are rotationally coupled, the number wheel 100 also rotates during dispense in a counter-clockwise direction, returning towards the zero unit stop 101, 153. At the zero unit position the number wheel 100 contacts the abutment 153 on the chassis 150, preventing further rotation of the dial gear 70, release gear 110 and belt gear 130, stopping release of the belt 121 and any further dispense of medicament.

(49) The trigger 40 is subsequently released, re-engaging the chassis locking arms 152 to lock the rotational position of the release gear 110, belt gear 130, belt 121, plunger 122 and main spring 140 independently from the zero unit stop between chassis 150 and number wheel 100. This allows the next dose to be set without immediate release of the main spring 140. Aside from the last dose nut 60, release gear 110, belt gear 130, belt 121, plunger 122 and main spring 140 all other components in the device return to their original positions once the entire dose has completed dispense.

(50) The release gear 110 splines that engage with the chassis locking arms 152 are angled so the release gear 110 is turned against the torque induced by the main spring 140 as they re-engage when the trigger 40 is released (FIGS. 20a, 20b). Back-winding the release gear 110 ensures that the chassis locking arms 152 react the main spring 140 force in place of the zero unit stop as the trigger 40 is released. This prevents the release gear 110 rotating to take up clearance at this interface when the subsequent dose is dialed (and the zero unit stop is disengaged), which could lead to the dispense of some fluid.

(51) Feedback is provided to the user during dose setting by the interaction between the dial member 50 detent arm 53 and the body 10 ratchet features 11. Dispense feedback is created through interaction between the chassis 150 and ratchet features on the release gear 110. A cantilever arm on the chassis 150 rides over the ratchet features on the release gear 110.

(52) A single, distinctive click is created as the device returns to the zero unit stop. This provides clear feedback to the user that the dose has been completed in addition to the dispense clicker ceasing. A cantilever arm 155 in the chassis 150 engages with the dial gear 70 when in the dispense condition. This arm is deflected as the dial gear 70 approaches the zero unit stop and rapidly released as the dial gear 70 engages the zero unit stop (FIGS. 21a to 21c).

(53) It is possible to incorporate a mechanism that allows the user to control the speed of dispense by the distance that they move the trigger 40. In this second embodiment the features and functions are identical to the first embodiment as described above. However, an additional system 160 is included as shown in FIGS. 22a to 22c.

(54) The embodiment shows a multiplate clutch system 160 integrated into the device acting between the dial member 50 (which is locked during dispense) and dial gear 70. The system comprises a carrier 161 which is splined to the dial member 50, a clutch spring 162 and a clutch pack comprising rotating plates 163 which are splined to the dial gear 70 and static plates 164 which are splined to the dial member 50 via carrier 161.

(55) For the embodiment shown in FIGS. 22a to 22c, force applied to the clutch pack 163, 164 from the clutch spring 162 reduces as the trigger 40 is depressed. Multiple clutch plates 163, 164 increase the torque capacity of the clutch for a given clutch spring force. In this embodiment, the overall trigger 40 travel is increased by addition of the user variable speed control.

(56) The facility for removing the need for a user to prime the device when first used can also be incorporated. This involves removing the variable distance (dependent on component and cartridge tolerances) between the cartridge bung 31 and the plunger 122 during manufacture such that the plunger 122 is in contact (and applies a small force) to the bung when assembled. This “prime elimination” is achieved using the following method: The cartridge holder 20 is divided into two separate components (cartridge holder 20 and rear body) and the device assembled omitting the rear body.

(57) A small dose of approximately 10 units is dialed by rotating the dial member 50 as the user would. The belt gear 130 is rotationally coupled to an assembly tool with torque measurement capability. The trigger 40 is depressed to release the mechanism and the torque generated in the belt gear 130 is measured as it is rotated clockwise via the assembly tool, thus releasing belt 121. As the belt 121 is released, the plunger 122 approaches the bung 31 under the main spring 140 force. When the plunger 122 contacts the bung, the bung 31 will begin to react a proportion of the main spring 140 force, thus reducing the belt gear 130 torque. Measurement of this change in torque as the belt 121 is released allows a specific force to be applied to the bung by the main spring 140. Release of the trigger 40 subsequently locks the mechanism and any set doses remaining are then dialed to zero. Finally the rear body is clipped into position to complete the assembly.

(58) FIGS. 23 and 24 show a further embodiment of the present disclosure having a different drive mechanism compared with the embodiments of FIGS. 1 to 22c. As can be seen in FIG. 23, the injection device has a different geometry of the casework defined by body 10′ and cartridge holder 20′ with chassis 150′ being elongated to extend towards the needle end of the cartridge within cartridge holder 20′. The last dose nut 60′ is splined to a component part 100′ having functions of the number wheel and the dial gear of the further embodiments included in one single part. Further, last dose nut 60′ is threaded to the coupling gear 70′. The compression spring of the further embodiments is replaced by a power spring 140′ in the form of a coiled band located between chassis 150′ and release gear 110′, which is separated from the pinion. A different dial ratchet 160′ is arranged between trigger 40′ and coupling gear 70′. In addition, the geometry of prism 90′ is refined enhancing visibility and clarity of the dialed dose whilst reducing parallax errors of the display. The design of prism 90′ is shown in FIG. 24 in more detail with the prism 90′ being assembled to the cartridge holder 20′.

(59) Comment: This embodiment comprises a totally different drive mechanism which requires a more detailed description. In contrast to the remark on slide 193 of HM65pre167_iss2.ppt, the layout of the last dose nut seems to be identical to e.g. FIG. 16, 19 or 22. Presently, I do not see major differences in the designs of the prisms. Please explain the amendments with respect to FIGS. 1 to 22 and advantages resulting from these amendments in more detail.