Patent Application
20160287802
The present patent application is generally directed to pen-type injection devices and specifically the dose setting mechanisms for such drug delivery devices. Such devices provide for self-administration of medicinal product from a multi-dose cartridge and permit a user to set the delivery dose. The present application may find application in both disposable and reusable type drug delivery devices. However, aspects of the invention may be equally applicable in other scenarios as well.
Pen type drug delivery devices have application where regular injection by persons without formal medical training occurs. This is increasingly common among patients having diabetes where self-treatment enables such patients to conduct effective management of their disease. Diabetes has been shown to cause certain problems. For example, people with diabetes can get high blood pressure, kidney disease, nerve damage, heart disease, and even in certain circumstances blindness. The damage caused by these problems may occur in patients whose blood sugar has been out of control for years. Keeping blood sugar under control, by way of effective insulin administration, is one method that can help prevent this damage from occurring.
In addition, people with diabetes can go into “diabetic coma” if their blood sugar is too high. They can also develop blood sugar that is too low (i.e, hypoglycemia) if they don't get enough food, or they exercise too much without adjusting insulin or food. Both diabetic coma and hypoglycemia can be very serious, and even fatal, if not treated quickly. Closely watching blood sugar, being aware of the early signs and symptoms of blood sugar that is too high or too low, and treating those conditions early can prevent these problems from becoming too serious.
Pen type drug delivery devices have been designed and developed to help patients suffering from diabetes and other disease states so as to prevent such problems from occurring. The circumstances identified above highlight a number of design considerations and criteria for drug delivery devices, especially those that may be used to treat diabetes. As just one example, one requirement is that the drug delivery device must be robust in construction. The drug delivery device must also be easy to use both in terms of the drug delivery device manipulation and understanding of the device's operation. Diabetics, for instance, have to inject themselves repeatedly with insulin solution and the volume of insulin to be injected may vary from patient to patient and even from injection to injection. For at least this reason, certain diabetics may require drug delivery devices that allow the patient to inject successive measured dosages of the same or perhaps different preset volumes of insulin solution accurately and with minimum dexterity challenges. This presents a further design challenge since, in the case of certain diabetics, users may have impaired vision and/or may be physically infirm with limited dexterity.
Generally, pen type injection devices include a cartridge having a slidable piston and containing a multi-dose quantity of liquid medication. A lead screw extending from the dose setting mechanism of the injector pen is movable in a forward (i.e., distal direction) to advance the piston within the cartridge in such a manner as to dispense the contained medication from an outlet at the opposite cartridge end, typically through a needle that penetrates a stopper or septum at that opposite end. In disposable or prefilled pens where the cartridge is permanently sealed within the pen housing, after a pen has been utilized to exhaust the supply of medication within the cartridge, the entire pen is then discarded. In reusable pens, after a pen has been utilized to exhaust the supply of medication within the cartridge, the pen is disassembled to allow replacement of the spent cartridge with a fresh cartridge, and then the pen is reassembled for its subsequent use.
A number of pen type injection devices are commercially available and unfortunately a number of those devices suffer from one or more design flaws that may result in the improper use of the injection device or the delivery of an inaccurate dosing of the medicament. Inaccurate dose setting could lead to fatal results. Other design flaws allow the possibility that a counterfeiter can dissemble a disposable pen and insert bogus medicament cartridge. This pen is then reassembled and sold as new. In some cases, the initially designed device does not provide feedback to a user during dispensing of the preset dose or at the completion of the dose. For the users who are visually and/or hearing impaired the ability to receive audible or tactile feedback is very important in order that the user hears or feels that the preset dose is being delivered and importantly that the injection is completed. Knowledge of the completion of the injection is very important to ensure a proper delivery of medicament is performed because users are taught to leave the injection needle in the skin for 10 seconds at the end of dosing to make sure all the medicament is delivered. Without such feedback features the risk of an improper injection being performed or under dosing is greatly increased, especially if the user dose not know when to begin the 10 second countdown. Such design flaws may not be realized when a pen is first commercialized and may only become apparent after the injection device has been in commercial use by patients for an extended period of time. As such, there exists a need to evaluate existing pen designs to identify the design flaws and then take corrective action, which typically would include redesigning certain original mechanisms within the injection device.
One such pen injector lending itself to design improvements is described in WO 2005/018721. The following describes a number of such design flaws and presents corrective solutions to eliminate these flaws.
The disclosure concerns method and a system for drug delivery. The device comprises a drug delivery device housing and a medicament contained in the drug delivery device housing. A mid-body component is axially fixed inside of the housing and contains one section of a dose dispensing feedback component that cooperates with another section of the dose dispensing feedback component contained in a longitudinal keyway on the lead screw. The engagement of the two sections generates an audible signal during dose dispensing and prevents inadvertent proximal axial movement of the lead screw away from the cartridge piston, which can lead to dosing inaccuracies.
In most, if not all, pen injection type devices dose accuracy is significantly affected if the distal end of the lead screw, through the associated bearing, is not in continuous engagement with the proximal end or face of the cartridge piston prior to the user setting a dose. Stated another way, in some dosing mechanism designs there is one or more flaws that allows the lead screw to move or other wise translate off the piston proximally after a dose is injected and before a subsequent dose is set. In these cases the bearing is no longer in contact with the proximal end of the piston thus creating a gap or void space between the distal face of the bearing and the proximal face of the piston. When a next dose is set and delivered, the lead screw would necessarily traverse this unintended gap before contacting and moving the piston. Because there is no movement of the piston during this gap closure, and hence no expulsion of medicament from the cartridge, the actual dose delivered will be less than that set by an amount directly proportional to the size of the gap. Accordingly, it is of prime importance to prevent any unintended proximal movement of the lead screw between dose delivery and the setting of the next dose. Stated differently, the dosing mechanism must include structures to prevent any proximal movement of the lead screw relative to the cartridge piston.
Pen type injection devices are designed to allow for self-administration of medicament in preset doses by the patient suffering from one or more disease state. Depending on treatment regime set by the caregiver, a patient may have to perform self injections several times a day. For this reason, pen type devices must be designed for all types of users, including the very young and the very old who may suffer from poor vision or hearing or manual dexterity. It is imperative therefore that the design of the injection device provide some type of feedback system to indicate to the user/patient that the injection is progressing correctly and that the injection is complete. For example, if there is no end of dose feedback signal provided, the user may inadvertently stop the injection process before the required full dose is delivered. This of course would lead to under dosing, which in some disease states could be very dangerous to the user.
A physical examination of the commercial pen injection device that is generally described in WO 2005/018721 shows that if a user pushes the dose knob in the distal direction and simultaneously rotates the dose knob in either direction (clockwise or counter clockwise) the lead screw is advanced in either the proximal and distal directions. Such a situation can develop as follows. The user begins to set a dose by rotating the dose knob causing the number sleeve to translate out proximally from the body. The user then grips the number sleeve preventing it from rotating and continues to rotate the dose knob while pushing the dose knob axially in the distal direction. This would cause the clutch to disengage from the dial link allowing relative rotation. Because the existing pen injection device is configured with the dose knob permanently attached to the dial link, rotation of the dose knob necessarily rotates the dial link. Since the dial link is rotationally engaged with the drive nut trough the extending fingers, the drive nut also rotates. Rotation of the drive nut while preventing the number sleeve, and hence the inner sleeve, from moving will cause the drive nut to rotate in a fixed axial position. Since the drive nut is prevented from translating or screwing up/down along the lead screw, the lead screw, which is rotational fixed by the mid-body, will be forced to translate axially relative to the threaded connection with the drive nut in either the distal or proximal direction depending on which way the dose knob is turned. If the lead screw translates distally it is possible to push the cartridge piston distally causing unwanted expulsion of medicament. If, however, the lead screw is caused to translate proximally then this will cause the bearing to disengage from the proximal face of the piston creating a gap that will lead to an inaccurate dose. To solve this problem, the present disclosure modifies the original design of dosing mechanism to prohibit this proximal motion of the lead screw.
Another problem with above-mentioned commercial pen is that a feedback signal is only provided during the setting of a dose and not during dose delivery. This problem is solved by the inclusion of a dose delivery clicker, preferably adding this feature with a lead screw anti-back up feature.
A drug delivery device being suitable for providing feedback comprises a housing and a lead screw having a longitudinal axis, a distal end and a proximal end that is rotatably fixed during dose setting and dose delivery and axially movable in a distal direction relative to the housing. The lead screw includes a threaded shaft and a bearing foot connected to the distal end, wherein the lead screw has a keyway positioned parallel to the longitudinal axis and containing a first section of a dose dispensing feedback component. The drug delivery device further comprises a cartridge with a movable piston at one end and an outlet at the other end, the piston engagable by the lead screw bearing foot to be advanced toward said outlet when the lead screw is moved distally. The drug delivery device further comprises a mid-body axially fixed inside of the housing, the mid-body including tabs that slidably fit within a keyway in the lead screw to prevent rotation of the lead screw within the housing, where the mid-body contains a second section of the dose dispensing feedback component.
The term “lead screw” shall preferably mean a component adapted to operate through/within a housing of the delivery device, which may be designed to move axially through/within the delivery device, for example for the purpose of discharging or dispensing an injectable product. It may be made of any suitable material known by a person skilled in the art and may be of unitary or multipart construction.
A key idea of invention is to provide a drug delivery device comprising a lead screw having a longitudinal axis, a distal end and a proximal end which is axially movable in a distal direction relative to a mid-body and preferably rotatably fixed during dose setting and dose delivery. The lead screw includes a threaded shaft, wherein the lead screw has a keyway positioned parallel to the longitudinal axis and containing a first section of a dose dispensing feedback component. A mid-body is designed to prevent rotation of the lead screw with respect to the mid-body, where the mid-body contains a second section of the dose dispensing feedback component.
The lead screw is coupled to the mid-body; the latter may be an integral part of a housing or may be fixed inside the housing in such a manner that rotation of the lead-screw within the housing is prevented.
In one embodiment, the first section of the dose dispensing feedback component comprises a linear arrangement of ratchet teeth. The second section of the dose dispensing feedback component may comprise a spring arm biased inwardly and configured to flex outwardly as the spring arm engages each tooth of first section of the dose dispensing feedback component as the lead screw is advanced distally through the mid-body.
The engagement of the teeth and spring arm produces an audible signal. Alternatively or additionally, the engagement of the teeth and spring arm produces a tactile signal.
In one embodiment, the lead screw has two keyways each containing a portion of the first section of the dose dispensing feedback component, both portions comprising a linear arrangement of ratchet teeth. The ratchet teeth of one keyway and the ratchet teeth of another keyway may be axially offset. There is an axial distance between the tip of a tooth of one portion of the first section of the dose dispensing feedback component and the tip of the adjacent tooth of the other portion of the first section. The offset may be half of a tooth's length. The flexible arms of the mid-body may be arranged to alternately engage with the teeth of one keyway and the teeth of the other keyway. The pitch of one portion of the linear arrangement of ratchet teeth has a pitch P1 and the other portion has a pitch P2. P1 may be different than P2. Alternatively P1 and P2 may be the same.
The spring arm and ratchet teeth may be configured to prevent the lead screw from moving in the proximal direction. In one embodiment the lead screw has at least two keyways, one containing the dose dispensing feedback component which comprises a linear arrangement of ratchet teeth; the other one containing means which prevents the lead screw from moving in the proximal direction, e.g. a linear arrangement of ratchet teeth. In other words, one linear arrangement of ratchet teeth serves as feedback component which allows to provide an audible and/or tactile feedback for the user. The other linear arrangement of ratchet teeth serves as blocking means preventing the proximal movement of the lead screw; the blocking means do not need to provide feedback. The design of the teeth may be optimized for their purpose, which are providing feedback and, on the hand, blocking. The teeth may differ in regard to their pitch, their steepness of the tooth's sides their shape, and their height and length. The mid-body may have two flexible arms, one engaging with the anti-back up ratchet teeth, the other engaging with the clicker ratchet teeth.
Modification is made to both the lead screw and the mid-body. The existing design of the mid-body provides a central opening having an inward facing anti-rotation mechanism formed from of a pair of diametrically opposed elements or tabs having squared off inward ends that each slidably fit within longitudinal flat keyways in lead screw. Spring arms projecting distally and slightly inwardly toward the longitudinal or centerline axis of the device are added to the central opening of the mid-body. Additionally, the flat keyways of the lead screw are changed to include ratchet teeth that are engaged with the spring arms in such a fashion that the lead screw can only be moved axially in a distal direction. During dose delivery as the lead screw is pushed distally the spring arms ride up (flexing radially outward) and over (snapping back to position) each ramped ratchet tooth in the lead screw keyway. This flexing and snapping back of the spring arms generates a “CLICK” noise and can also generate a tactile feedback signal to the device user that the injection is proceeding. The spacing between ratchet teeth can be chosen such that each click signifies one unit dose of medicament delivered. The combination of the spring arms and keyway ratchet teeth also provide an anti-back up feature. The ratchet teeth are designed to be unidirectional, meaning that the spring arm snaps back inwardly behind the ramp or wedge shape tooth. In this position the spring arm engages the backside of the wedge and prevents proximal movement of the lead screw, thus keeping the lead screw bearing in contact with the proximal face of the cartridge piston.
In another embodiment, the keyway ratchet teeth in one keyway can be offset or staggered from the ratchet teeth in the other keyway. This would allow smaller increments or more clicks for smaller set doses being injected. In such an arrangement the pitch (i.e., the distance between adjacent teeth) of the teeth in both keyways would be the same. In another embodiment the pitch of the teeth in one keyway could be different than the pitch of the ratchet teeth in the other keyway. In such a configuration, one spring arm would be configured for providing the audile and/or tactile dose delivery feedback and the other spring arm would provide the anti-back up feature.
The pen type delivery device drug including the above described design improvement includes a housing, a lead screw having a threaded shaft is rotatably fixed during dose setting and injecting that only moves axially in a distal direction relative to the housing during dose administration and is always prevented from moving proximally. The device also has a fluid container or cartridge defining a medicine-filled reservoir with a movable piston at one end and an outlet at the other end, where the piston is engaged by a bearing connected to the distal end of the lead screw. The piston is advanced toward the outlet or distal end of the cartridge when the lead screw is moved distally during dose administration.
A drive nut is threadedly engaged and screwable along the lead screw threaded shaft. The drive nut is threadedly engaged with the threads on the lead screw and can rotate and move proximally relative to the lead screw and housing during dose setting. A number sleeve is threadedly engaged with the housing to be screwable relative to the housing. The number sleeve is screwed outwardly in the proximal direction relative to the housing during dose setting. A dial link is slidably and rotationally engaged with the drive nut and is axially movable and rotatably fixed relative to the drive nut. In other words, the dial link is connected with the drive nut and axially movable and rotatably fixed relative to the drive nut. The dial link is rotatably fixed with number sleeve when the dial link and number sleeve are in a first axial arrangement, the number sleeve being rotatable relative to the dial link when the dial link and number sleeve are in a second axial arrangement. In one embodiment, the dial link is rotatably fixed with the number sleeve through a clutch when the dial link and number sleeve are in a first axial arrangement and when in a second axial position the clutch, and hence the number sleeve, are disengaged from the dial link and the dial link becomes rotatable relative to the number sleeve. An inner sleeve is threadedly engaged with the number sleeve, were the inner sleeve is axially movable but rotatably fixed relative to the housing. The inner sleeve may be axially movable and rotatably fixed relative to the mid-body, e.g. by at least one lug of the mid-body that slidably fits within at least one slot formed in the inner sleeve.
In one embodiment, the threading of the number sleeve to the housing is of a first lead, the threading of the inner sleeve to the number sleeve is of a second lead, and the threading of the lead screw threaded shaft is of a third lead, and the first lead, the second lead and the third lead are not equal.
During dose setting, the dial link and the number sleeve are in the first axial arrangement, whereby a screwing motion of dial link and number sleeve relative to the housing screws the dial link and the number sleeve a first axial distance from a home position, which screwing motion of dial link screws said drive nut along the lead screw threaded shaft a second axial distance that is different than the first axial distance. During dose setting, the dial link and the number sleeve are in the first axial arrangement, whereby a screwing motion of the dose knob that is connected to the dial link and number sleeve relative to the housing screws the dial link and the number sleeve a first axial distance from a home position causing the number sleeve to extend in the proximal direction outwardly from the housing or body of the device. The screwing motion of the dial link screws the drive nut along the lead screw threaded shaft a second axial distance different than the first axial distance.
During dose dispensing, the dial link and the number sleeve element are in the second axial arrangement, whereby a screwing motion of the number sleeve relative to the housing back or inward toward the home position advances the inner sleeve without rotation in the distal direction to axially advance the drive nut that is axially fixed to the inner sleeve and thereby the lead screw and the moveable fluid container piston to dispense medicine or fluid from the cartridge outlet. The pen injector disclosed herein can be provided with a mechanical advantage that makes it easier for the user to push the dose knob during the dispensing of medication, which mechanical advantage can be very high and conveniently selected by the manufacturer during apparatus design. This mechanical advantage allows the number sleeve to travel a greater axial distance than the lead screw it advances, thus allowing for small doses to be delivered.
These as well as other advantages of the various aspects of our improved drug delivery device, and the manner of attaining them, will become apparent to those of ordinary skill in the art by reading the following detailed description, with appropriate reference to the accompanying drawings.
Exemplary embodiments are described herein with reference to the drawings, in which:
Corresponding reference characters indicate corresponding parts throughout the several views. Although the drawings represent embodiments of the present invention, the drawings are not necessarily to scale, and certain features may be exaggerated or omitted in some of the drawings in order to better illustrate and explain the present invention.
Referring first to
The drug delivery device 1 and the housing have a distal end and a proximal end. The term “distal end” designates that end of the drug delivery device 1 or a component thereof which is or is to be arranged closest to a dispensing end of the drug delivery device 1. The term “proximal end” designates that end of the device 1 or a component thereof which is or is to be arranged furthest away from the dispensing end of the device 1. The distal end and the proximal end are spaced apart from one another in the direction of an axis. The axis may be the longitudinal axis or rotational axis of the device 1.
The proximal end of the cartridge holder 2 and the distal end of the main housing 4 are secured together by appropriate retaining features depending on whether the pen injector is designed as a reusable device or as a disposable device. In the latter case, the retaining feature would be permanent using the connection means described below. If the device is reusable, the retaining meaning would be a screw type connection, a Luerlok, snap fit, bayonet, or the like type or combination of fittings that allow the user to easily disassemble the device to replace the empty cartridge with a fresh new cartridge. In this illustrated arrangement, the cartridge holder 2 is secured within the proximal end of the main body 4.
A cartridge 8 from which a number of doses of a medicinal product may be dispensed is provided in the cartridge holder 2. Preferably, the cartridge 8 contains a type of medicament that must be administered often, such as once or more times a day. One such medicament is insulin. A piston 10 shown in
The dose setting mechanism of the drug delivery device 1 illustrated in
The previously mentioned removable or replaceable cap 14 is used to cover the cartridge holder 2 extending from the main housing 4. Preferably, the outer dimensions of the replaceable cap 14 are similar to or identical to the outer dimensions of the main housing 4 so as to provide an impression of a unitary whole part when the replaceable cap 14 is in position covering the cartridge holder 2. In use, the removable cap 14 is removed and a pen needle assembly 16 comprising a double-ended needle mounted in a hub may be screwed or pushed onto the distal end of the cartridge holder 2 or alternatively may be snapped onto this distal end.
Cartridge 8 is of conventional design and defines a medicine-filled reservoir that is closed at its proximal end by the piston 10 that is axially slidably and sealably engaged with the cartridge interior wall to hold the fluid medication within the reservoir. The distal, outlet end of the cartridge reservoir is sealed by a septum 11 held by a cap 13 that is secured to a stepped-down diameter neck portion 15 of the cartridge 8. When the pen needle assembly 16 is mounted on the distal end of the cartridge holder 17, the proximal point of injection needle passes through a central opening in the distal end of the cartridge holder 17, an opening in the cap 13, and penetrates the cartridge septum 11 to provide a fluid flow outlet by which medicine within cartridge reservoir can be dispensed from the distal needle tip during operations of injector pen 1. The fluid medicine cartridge 8 shown and described above is illustrative and not intended to be limiting as other constructions may be employed within the scope of this invention.
A main body 4 of the injector pen 1 houses an axially advanceable lead screw 22, a drive nut 23, a inner sleeve 29, a dial link 25, a number sleeve 24, a clutch 26, and a compression spring 27. A dose knob 28 is connected to the dial link 25 and is used to set the dose and then to inject the set dose. Housing or main body 4 is formed from a lightweight material, such as injection molded plastic. The housing 4 may be molded as a single, tubular piece for robustness. A window 51 in the housing 4 near its proximal end can be filled with a magnifying lens that snaps fits to the housing 4 and allows dosage indicating markings (not shown) on number sleeve 24 to be readily visible during use. Near the interior distal end of the housing 4 is mounted a mid-body 20 that is formed with a central opening having an inward facing anti-rotation mechanism formed from a pair of diametrically opposed elements or tabs 31 having squared off inward ends that each slidably fit within longitudinal keyways 32 in lead screw 22. In alternate embodiments, features other than tabs and keyways, for instance a lead screw with flats that fits within a complementarily shaped hole in the collar, may be used to prevent rotation. The tabs 31 prevent the lead screw 22 from rotating within the housing 4 during pen use, but permit the lead screw 22 to be shifted longitudinally, such as in the distal direction towards the cartridge 8. A snap fit or sonic welding connection of the mid-body 20 to the tubular housing 4 can be used to prevent axial and rotational relative motion of the mid-body 20 to housing 4.
The lead screw 22 is in the form of a screw that is axially translatable and rotatably fixed during dosing and injecting. The term “rotatably fixed” shall mean in this context that the lead screw 22 is prevented from rotation during dosing and injecting. The lead screw 22 includes a shaft with a helical threading 33 along its length, which threading 33 is interrupted by the longitudinally extending keyways or grooves 32. A thread stop 34 shown at the proximal end of the threading 33 is provided and is used in preventing the pen from being set by a user to deliver a dose of medicine larger than remains in cartridge 8. Other forms of stopping the screw motion may be substituted within the scope of the invention, for example, the threading at the proximal screw end could stop near the proximal end where it can not be cammed in, and such solid screw with thread stop better ensures the nut 23 will not be torqued off the screw during dose setting. The distal end of lead screw 22 includes an enlarged, disc-shaped foot or bearing 21 to distribute loading on the cartridge piston 10 that the bearing 21 contacts and thereby directly engages during piston advancing. The separate bearing foot 21 can be attached, such as with a snap fit 20 that may permit relative rotation, to the lead screw 22. The lead screw 22 is shown as being a one-piece plastic injection molding, but alternate materials of construction and multiple pieces are possible.
The drive nut 23 includes a cylindrical, tube-shaped body with flexible fingers 36 and clicker teeth 35. The distal region of the drive nut 23 is formed with an internal threading 37 that threadedly engages in a friction locking fashion the threading 33 on the lead screw 22. Threadings 33 and 37 are shown as a double start threading but may be differently formed while still providing suitable friction locking capabilities, such as a single start threading or another multiple start threading. The drive nut 23 is located within the inner sleeve 29 and is axially, but not rotationally fixed, to the inner sleeve 29. As the drive nut 23 is rotated relative to the inner sleeve 29 during dose setting, the clicker teeth 35 engage in a ratchet fashion flexible arms 38 that project radially on the inside of inner sleeve 29. As the drive nut 23 rotates the flexible arms 38 ride over the teeth 35 creating an audible clicking noise. The teeth 35 are configured so that each click is equal to one dose volume being set. As few as one flexible clicker arm 38 may be provided, but the use of four equally angularly spaced arms 38 aids in centering the drive nut 23 within the inner sleeve 29. The hollow interior of the drive nut body 23 located proximally of the threading 37 allows free passage of the proximal end of the lead screw 22. The exterior surface of the drive nut 23 is designed to cooperatively engage with the dial link 25 so that the dial link 25 is axially free and rotatably fixed relative to the drive nut 23. Thus, during use the dial link 25 is axially moveable relative to, but rotatably locked with, the threaded drive nut 23. This connection is possible because of the cooperation of the proximally extending fingers 36 on the drive nut 23 and the distally extending fingers 43 of the dial link 25. These two sets of fingers 36, 43 move axially relative to each other but engage each other rotationally during dose setting when the dial link 25 is rotated by turning the dose knob 28, which is fixed to the dial link 25. The drive nut 23 is shown as being a one-piece plastic injection molding, but other constructions are within the scope of the invention.
In the shown embodiment, the dial link 25 is formed in one piece of an injection molded plastic and which fits within the body 4. A flange 40 that rings a central region of the dial link body includes splines or teeth 39 that extend from the distal face of the flange 40, and teeth 41 that extend from the proximal face of the flange 40. A stepped-down portion of the proximal end of the dial link 25 forms an axially and proximally extending stem 42. The distal end of the dial link body includes a pair of fingers 43 that fit with the fingers 36 of the drive nut 23 to allow axial motion but not rotational motion of the drive nut 23 relative to the dial link 25, thereby rotationally locking the pieces together within the same annular space. Fingers 36 and 43 extend sufficiently axially to ensure they do not disengage during the setting of the maximum pen dose for injection.
An injection molded plastic dose knob 28 with a proximal face, and having a distally facing and centrally located bearing collar and alignment post 55 is provided. A dose knob skirt 50 distally extends from the radial periphery of the dose knob distal face to serve as a grip portion for a user during dose setting. The stem 42 of the of the dial link 25 receives the dose knob alignment post and can be ultrasonically welded within the bearing collar during manufacturing assembly, so as to axially and rotatably fix together the dose knob 28 and the dial link 25. The term “rotatably fix” shall mean in this context that any relative rotational movement between the dose knob 28 and the dial link 25 is prevented.
Coaxially mounted around the dial link 25 is number sleeve 24. The number sleeve 24 has a cylindrical exterior surface 30 with a threading 52 formed as a helical groove that engages a corresponding threading 62 formed on the interior surface of body 4 to threadedly engage the number sleeve 24 to the pen housing. Threadings 52 and 62 are shown as a single start threading but may be differently formed. Threading 62 abuts the end 63 of threading 52 on the the number sleeve 24 at the maximum pen dose, assuming the cartridge 8 is sufficiently full for such a maximum dose. A stop surface 64 on the distal end of the outer surface of the number sleeve 24 is positioned in slightly spaced apart relationship with a projecting stop at the zero dose position, and another stop surface is to be abutted by the stop if a user attempts to manually screw the screw element below a zero dose position. A hollow interior 65 of the number sleeve 24 is defined by a cylindrical interior surface provided with a helical threading 67.
The outside diameter of the number sleeve 24 is selected such that it can fit inside dose knob 28. The proximal end region of number sleeve 24 includes a number of notches 70 and corresponding windows 71 that are alternately spaced around the circumference. The number sleeve 24 includes around its exterior surface 30 suitable indicia of therapeutic dose size as visible through the body opening 51. A clutch 26 fits within the open proximal end of the number sleeve 24. Ears 72 on the clutch 26 fit within notches 70 and assembly fingers 73 snap lock into the windows 71 to axially and rotatably lock the number sleeve 24 and the clutch 26 together during manufacturing assembly. A ring of axially extending teeth 54 on the clutch 26 formed in the interior surface of a flange cooperate with the dial link teeth 41 proximally facing on the dial link 25. Disposed between the clutch 26 and the inside portion of the dose knob 28 is a spring 27 that urges the clutch 26 to engage the teeth 41 on the dial link 25. During injection, when a user manually applies a plunging force onto proximal face of the dose knob 28, the spring 27 is elastically compressed, thus disengaging the clutch 26 and the number sleeve 24 from the dial link 25. The flange teeth 41 on the dial link 25 and clutch teeth 54 mesh when the spring 27 has biased the clutch 26 and the attached number sleeve 24 to the dose knob 28 and the dial link 25. The dose knob 28 and the dial link 25 are not meshed with the clutch 26 and the number sleeve 24 when the spring 27 has been sufficiently compressed during injecting. While a helically coiled metal wire spring 27 is shown, other forms of commonly known biasing elements may be substituted.
The inner sleeve 29 is injection molded from plastic and includes a tubular body that fits into the hollow 65 of the number sleeve 24. The inner sleeve 29 has a helical threading 75 on its outer surface that engages the internal threading 67 on the inside surface of the number sleeve 24. Threadings 67 and 75 are shown as a single start threading, but may be differently formed. The proximal most portion of the end of inner sleeve 24, which end is partially helically shaped corresponding to the threading, is notched to form a partial ring of axially projecting teeth 76 that, when meshed with dial link distally facing teeth 39, serve to rotatably lock together the dial link 25 and the inner sleeve 29. The inner sleeve 29 is keyed to the pen body 4 through the intermediate mid-body 20 that is axially and rotationally fixed to the body 4. The distal end of the inner sleeve 29 has a pair of ridge-defined slots 77 on the periphery of the inner sleeve 29 which axially, slidably receive lugs 78 radially inwardly projecting from the mid-body 20. Openings molded into the inner sleeve 29 define four resilient fingers 38 having radially inwardly projecting teeth that are axially oriented and shaped to project into a recess in the distal end of the drive nut 23 that has radially projecting teeth or ridges 35 such that the inwardly projecting teeth click over, in either rotational direction, teeth 35 during dose setting. The fingers 38 with teeth cooperate with the recess on the drive nut 23 to hinder the nut 23 from coming off the inner sleeve 29 after being assembled thereto during manufacture.
To facilitate back-driving during dose delivery, the threaded connections of the number sleeve 24 and the body 4, and the number sleeve 24 and the inner sleeve 29, are non-binding and provided by projecting 60° face angle threads that slide within correspondingly designed recessed grooves. With these threadings, it is preferred that the mechanical advantage is 3.4 or greater, and the screw lead of the drive member or drive nut 23 is 0.108 inch.
The operation of the above described embodiment will now be explained. The pen 1 with a needle 16 attached should first be primed to remove any trap air in the cartridge 8 and to ensure the bearing 21 is in contact with the proximal end of the cartridge stopper or piston 10. In particular, typically while clutching the pen body 4 in one hand, a user manually grips the dose knob skirt 50 and then begins to turn the dose knob 28 relative to the body 4. At the zero dose arrangement, and as long as the dose knob 28 is not also being plunged which is improper, the dose knob 28 can only be rotated in a dose increasing direction due to the number sleeve 24 not being further movable distally. A user stops the rotating after a short amount of number sleeve travel that is associated with a small delivery volume, such as one or two units, which is indicated by the markings visible through the window 51. Then, and after removing the cap 14 and any other needle cap present, and while pointing the needle tip upward, the user applies a plunging force on the dose knob 28 to drive it distally until the number sleeve 24 returns to the zero dose position, at which the number sleeve threading 52 has reached the distal end of the body threading 62, during which plunging action the piston 10 is shifted forward within the cartridge 8. If a user sees that the piston movement has caused liquid to reach the needle distal tip, the priming process is complete. If no liquid is visible at the needle tip, the priming steps are repeated as needed. After priming, the pen 1 is ready to be used for an actual injection.
First, a user prepares the pen by setting the desired dose, as visible in the window 51, by turning of the dose knob 28. If the user dials up too large of a dose, and without expelling any medicine, the user can rotate down the dial by turning the dose knob 28 in the opposite direction, all the way back to zero if desired. To set a dose, the dose knob 28 is turned in a clockwise direction. Because the dose knob 28 and the dial link 25 are fixed rotationally, the dial link 25 is rotated causing the distally facing fingers 43 to engage the proximally facing fingers 36 of the drive nut 23 to thereby turn the drive nut 23 in the same direction. Rotation of the drive nut 23 causes the nut 23 to rotate relative to the stationary lead screw 22 whereby the nut 23 moves or climbs up the lead screw 22 in the proximal direction. The drive nut 23 rotates relative to the inner sleeve 29 that is held rotationally fixed relative to the body 4 through the splined connection to the mid-body 20. Because the drive nut 23 and the inner sleeve 29 are axially fixed, proximal axial movement of the drive nut 23 causes the inner sleeve 29 to slide proximally relative to the mid-body 20. Because the clutch 26 is rotationally fixed with the dial link 25 the clutch 26 rotates causing the number sleeve 24 to rotate and to spin out proximally away from the body 4. Because the pitch of the threads on the number sleeve 24 are greater than the pitch of the threads 75 on the inner sleeve 29, the number sleeve 24 and the dial link 25 will translate a larger axially distance compared to the inner sleeve 29 and the drive nut 23.
To inject the dose, after the pen 1 is manipulated so the injection needle distal tip properly penetrates, for example, a user's skin, an axial, distal plunging force is applied to the knob face 53 to force the dial link 25 axially in the distal direction toward the body 4, such as with a thumb or index finger of the hand which grasps the housing 4. Initially during injecting, the dial link 25 is shifted axially, which shifting motion compresses the biasing spring 27 to close the gap between the knob surface and the proximal end of the number sleeve 24. The biasing spring 27 is designed to compress prior to the number sleeve 24 moving relative to the body 4. When the dial link 25 shifts relative to the number sleeve 24 to the axial arrangement of the drive nut 23, the clutch teeth 54 and the dial link teeth 42 disengage to allow a backdriving rotation of the number sleeve 24 relative to the dial ink 25. During the axial movement of the dial link 24, the drive nut 23 does not move axially or rotationally. When the number sleeve 24 and the clutch 26 rotatably uncouple from the dial link 25, as the dial link 25 is continued to be axially plunged without rotation by the user by the plunging of the dose knob 28, the number sleeve 24 screws into the body 4 as it spins relative to the dose knob 28 and the dose markings on the number sleeve 24 that indicate the amount still remaining to be injected are visible through the window 51.
As it screws down, the number sleeve 24 causes the inner sleeve 29 to in essence screw up the internal thread inside of the number sleeve threading as the inner sleeve 29 advances distally a lesser distance than the number sleeve 24. The advancement of the inner sleeve 29, due to the abutting or direct engagement with the distal end of the drive nut 23, advances the drive nut 23 without rotation, which due to its threaded connection with the lead screw 22 advances the lead screw 22 axially without rotation, which lead screw advancement shifts cartridge piston 10 to expel medication from the cartridge reservoir. The injection is completed when the number sleeve threading 52 has reached the distal end of the body 4, at which time pen 1 is once again arranged in the ready state or zero dose position.
The pen 1 can continue to be used to deliver any desired dose until the medicine remaining in the cartridge 8 is insufficient for a proper dosing. This insufficiency is indicated to the user by the inability to fully set the desired dose due to drive nut threading 37 abutting the thread stop 34 of the lead screw 22, at which time the drive nut 23 and the dial link 25 cannot be rotated proximally any farther. When insufficient medicine remains, the pen 1 is to be disposed of and replaced with a similar but entirely new pen.
The terms “medicament” or “medicinal product”, as used herein, mean a pharmaceutical formulation containing at least one pharmaceutically active compound,
wherein in one embodiment the pharmaceutically active compound has a molecular weight up to 1500 Da and/or is a peptide, a proteine, a polysaccharide, a vaccine, a DNA, a RNA, an enzyme, an antibody or a fragment thereof, a hormone or an oligonucleotide, or a mixture of the above-mentioned pharmaceutically active compound,
wherein in a further embodiment the pharmaceutically active compound is useful for the treatment and/or prophylaxis of diabetes mellitus or complications associated with diabetes mellitus such as diabetic retinopathy, thromboembolism disorders such as deep vein or pulmonary thromboembolism, acute coronary syndrome (ACS), angina, myocardial infarction, cancer, macular degeneration, inflammation, hay fever, atherosclerosis and/or rheumatoid arthritis,
wherein in a further embodiment the pharmaceutically active compound comprises at least one peptide for the treatment and/or prophylaxis of diabetes mellitus or complications associated with diabetes mellitus such as diabetic retinopathy,
wherein in a further embodiment the pharmaceutically active compound comprises at least one human insulin or a human insulin analogue or derivative, glucagon-like peptide (GLP-1) or an analogue or derivative thereof, or exendin-3 or exendin-4 or an analogue or derivative of exendin-3 or exendin-4.
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-Phe-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.
Antibodies are globular plasma proteins (˜150 kDa) that are also known as immunoglobulins which share a basic structure. As they have sugar chains added to amino acid residues, they are glycoproteins. The basic functional unit of each antibody is an immunoglobulin (Ig) monomer (containing only one Ig unit); secreted antibodies can also be dimeric with two Ig units as with IgA, tetrameric with four Ig units like teleost fish IgM, or pentameric with five Ig units, like mammalian IgM.
The Ig monomer is a “Y”-shaped molecule that consists of four polypeptide chains; two identical heavy chains and two identical light chains connected by disulfide bonds between cysteine residues. Each heavy chain is about 440 amino acids long; each light chain is about 220 amino acids long. Heavy and light chains each contain intrachain disulfide bonds which stabilize their folding. Each chain is composed of structural domains called Ig domains. These domains contain about 70-110 amino acids and are classified into different categories (for example, variable or V, and constant or C) according to their size and function. They have a characteristic immunoglobulin fold in which two β sheets create a “sandwich” shape, held together by interactions between conserved cysteines and other charged amino acids.
There are five types of mammalian Ig heavy chain denoted by α, δ, ε, γ, and μ. The type of heavy chain present defines the isotype of antibody; these chains are found in IgA, IgD, IgE, IgG, and IgM antibodies, respectively.
Distinct heavy chains differ in size and composition; α and γ contain approximately 450 amino acids and δ approximately 500 amino acids, while μ and ε have approximately 550 amino acids. Each heavy chain has two regions, the constant region (CH) and the variable region (VH). In one species, the constant region is essentially identical in all antibodies of the same isotype, but differs in antibodies of different isotypes. Heavy chains γ, α and δ have a constant region composed of three tandem Ig domains, and a hinge region for added flexibility; heavy chains μ and ε have a constant region composed of four immunoglobulin domains. The variable region of the heavy chain differs in antibodies produced by different B cells, but is the same for all antibodies produced by a single B cell or B cell clone. The variable region of each heavy chain is approximately 110 amino acids long and is composed of a single Ig domain.
In mammals, there are two types of immunoglobulin light chain denoted by λ and κ. A light chain has two successive domains: one constant domain (CL) and one variable domain (VL). The approximate length of a light chain is 211 to 217 amino acids. Each antibody contains two light chains that are always identical; only one type of light chain, κ or λ, is present per antibody in mammals.
Although the general structure of all antibodies is very similar, the unique property of a given antibody is determined by the variable (V) regions, as detailed above. More specifically, variable loops, three each the light (VL) and three on the heavy (VH) chain, are responsible for binding to the antigen, i.e. for its antigen specificity. These loops are referred to as the Complementarity Determining Regions (CDRs). Because CDRs from both VH and VL domains contribute to the antigen-binding site, it is the combination of the heavy and the light chains, and not either alone, that determines the final antigen specificity.
An “antibody fragment” contains at least one antigen binding fragment as defined above, and exhibits essentially the same function and specificity as the complete antibody of which the fragment is derived from. Limited proteolytic digestion with papain cleaves the Ig prototype into three fragments. Two identical amino terminal fragments, each containing one entire L chain and about half an H chain, are the antigen binding fragments (Fab). The third fragment, similar in size but containing the carboxyl terminal half of both heavy chains with their interchain disulfide bond, is the crystalizable fragment (Fc). The Fc contains carbohydrates, complement-binding, and FcR-binding sites. Limited pepsin digestion yields a single F(ab′)2 fragment containing both Fab pieces and the hinge region, including the H—H interchain disulfide bond. F(ab′)2 is divalent for antigen binding. The disulfide bond of F(ab′)2 may be cleaved in order to obtain Fab′. Moreover, the variable regions of the heavy and light chains can be fused together to form a single chain variable fragment (scFv).
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.
While this invention has been shown and described as having various designs, the present invention may be modified within the spirit and scope of this disclosure. For example, to deliver a fixed dose, the pen 1 would preferably be modified such that the maximum that the dial could be screwed out to prepare the pen 1 for injection would correspond to the fixed dose. Such a fixed dose pen could eliminate numerical dosage indicating marking, and instead provide user cues in the form of, for example, instructions and a graphical dosing indicator. This disclosure is therefore intended to cover any variations, uses or adaptations of the invention using its general principles. Further, this disclosure is intended to cover such departures from the present disclosure as come within known or customary practice in the art to which this invention pertains.
| Number | Date | Country | Kind |
|---|---|---|---|
| 14165752.8 | Apr 2011 | EP | regional |
The present application is a U.S. National Phase Application pursuant to 35 U.S.C. §371 of International Application No. PCT/EP2014/074709 filed Nov. 17, 2014, which claims priority to U.S. Provisional Patent Application No. 61/907,470 filed Nov. 22, 2013 and European Patent Application No. 14165752.8, filed Apr. 24, 2014. The entire disclosure contents of these applications are herewith incorporated by reference into the present application.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP2014/074709 | 11/17/2014 | WO | 00 |
| Number | Date | Country | |
|---|---|---|---|
| 61907470 | Nov 2013 | US |
