Patent ID: 12220565

DETAILED DESCRIPTION

Turning now toFIG.1, a schematic diagram of the components of a dose control system (1) according to the present invention is displayed. Such a dose control system comprises for example, an integrated control unit (2), for example, mounted on a printed circuit board, or equivalent on which various components are mounted and in connection with each other. The integrated control unit (2) could also be comprised of circuits engraved or etched in silicon or the like, as is known per se. In fact, virtually the whole dose control system could be engraved into a single, or multiple, interconnected blocks of silicon or other similar semi-conductor material as generally known in the art if so desired. The integrated control unit (2) comprises a central processing unit (CPU,3), which is responsible for processing and managing signals and communication between the various components of the system, and also for calculations, and execution of program code stored within the system, or operable remotely on said system. The integrated control unit (2) additionally comprises a real time clock (RTC,4), for keeping and measuring time within the dose control system. The real time clock (RTC,4) can also be integrated into the central processing unit (CPU,3), for example, using frequency measurements whilst the central processing unit (CPU,3) is powered with energy, in order to calculate time and time differences for various events within the system. The dose control system is also equipped with a communications subsystem (COM,5), for example a low power consuming bluetooth radio device, the communications subsystem allowing for the dose control system to communicate with a local or remote data processing system (not shown), e.g. a smartphone and corresponding smartphone application, used to provide information and feedback to the user on usage of the dose control system. Additionally, the system also has some form of memory storage (MEM,6), for storing information within the system, whether transiently or permanently, such information coming from a variety of sources, including the values or signals measured or determined from other endpoints of the system, values calculated or stored by the central processing unit (CPU,3), values or data received from the remote or local data processing system, such as the smartphone, factory settings for calibration of the system, a unique identifier means or data identifying the device uniquely, and the like. Such memory storage systems (MEM,6) are known per se to the skilled person.

The integrated control unit (2), and by extension, the central processing unit (CPU,3), is also in communication with at least one accelerometer (ACC,7) and at least one magnetometer (MGR,8). The accelerometer (ACC,7) is responsible for detecting and/or measuring changes in relative movement due to acceleration of the drug delivery device on which the dose control system is mounted, be it from a horizontal to vertical position as held by the user, or any position in between, with regard to a set of pre-determined and pre-programmed reference positions. The accelerometer (ACC,7) is also responsible for detecting and/or measuring changes in relative movement due to acceleration of the drug delivery device when a user sets a dosage via a dose selector shaft, which causes a vibration of the drug delivery device, i.e. a relative movement of acceleration, that is detectable by the accelerometer (ACC,7). The strength and frequency of the relative movements of acceleration, which are communicated from the accelerometer (ACC,7) to the central processing unit (CPU,3) are used to determine the type of operation that the user has effected. Such relative movements of acceleration can include vibrations caused by clicks produced by the drug delivery device, e.g. in the majority of autoinjector drug delivery devices, e.g. pens, for self-injection of various drugs, e.g. insulin, ATP, and the like, these clicks provide an audible cue signal for the user to indicate various operations undertaken by the latter, but the clicks also produce vibrations within the drug delivery device that can be suitably picked up by an accelerometer.

The mangetometer (MGR,8) is also connected to the central processing unit (CPU,3). This component is responsible for detecting changes in magnetic field, as produced by movement of the magnet (MAG,9) which is in a movable spaced relationship with the magnetometer (MGR,8). The magnetometer is capable of detecting changes of magnetic field along multiple axes, for example one, two, three or more axes, although detection of changes in magnetic field along two or three axes are preferred. Usually, these axes are perpendicular to one another, so as to provide a three-dimensional magnetic field detection zone. The at least one, and preferably two, magnetometers are located so as to be able to detect corresponding changes in magnetic field as the magnet (MAG,8) is displaced. As the drug delivery device on which the dose control system is mounted has a longitudinal axis, it is preferable to also locate the at least one magnetometer (MGR,7) along said longitudinal axis. In a preferred embodiment, the system includes two magnetometers and these are located in axial alignment along the longitudinal axis of the drug delivery device when the dose control system is mounted on said device. This allows the dose control system to remain compact in size and dimensions, and thereby not negatively influence or interfere with normal, habitual manipulation of the drug delivery device by the user. The magnetometer is also suitably configured to detect the earth's magnetic field, and any changes therein that might occur when the user travels with the drug delivery device, as the earth's magnetic field, and changes therein can influence the measurements made by the magnetometer (MGR,7) in regard to the magnetic field producing means of the dose control system.

The magnetic field producing means in the present exemplary device include a magnet (MAG,9). In one particularly preferred embodiment, the magnet produces a three dimensional magnetic field along three perpendicularly positioned axes (x, y, z). As mentioned above, the magnetometer (MGR,7) detects changes in magnetic field produced by the magnet (MAG,9), when the latter is displaced proximally, and away from, or distally and towards, a proximal extremity of the drug delivery device. This detection of magnetic field changes occurs without any form of electrical or electronic or physical contact between the magnetometer(s) (MGR,7) and the magnet (MAG,9), leading to the designation of the dose control system as a contactless system. The magnet preferably has a substantially annular shape, with a hole in the middle, and can be made of any suitable magnetic or magnetizable material, details of which are given elsewhere in the present specification. The magnet (MAG,9) can thus be mounted on a dose selector shaft of the drug delivery device, which is in longitudinal axial alignment with both the longitudinal axis of the drug delivered device and the magnetometer(s). The dose selector shaft is generally rod shaped, such that the substantially annular magnet can be removably slid onto the shaft, and produce a three-dimensional magnetic field around the proximal extremity of the drug delivery device. The magnet is removably mounted on the dose selector shaft in such a way that it can impart rotational movement to said shaft when turned by a user. Rotation can occur in both clockwise and counter-clockwise directions. The magnet has two opposing poles, each substantially constituting a half, or hemi-spherical part of the annular magnet. As the magnet rotates, the opposing poles also rotate about the longitudinal axis of the device. A first reference point of known magnetic field strength along one, two or three axes, is detected by the magnetometer(s) and this information is stored in the dose control system, for example in memory (MEM,6), via the central processing unit (CPU,3). Generally, this first position will correspond to a position of the magnet (MAG,9) in which it is closest to the proximal extremity of the drug delivery device, and beyond which further rotation of the dose selector shaft in a given direction is impossible. When the user rotates the magnet (MAG,9), in an allowed direction of rotation, and correspondingly indexed rotational movement of the dose selector shaft, the magnet and proximal extremity of the dose selector shaft move longitudinally in a proximal direction away from the proximal extremity of the body of the drug delivery device, but along the longitudinal axis of the device in general. As the magnet (MAG,9) rotates around said longitudinal axis, and translates there along, changes in magnetic field and polarity are detected by the suitably positioned magnetometer(s) (MGR,8). The variations in magnetic field can be resolved into mathematical components comprising vectors and moduli by the central processing unit (CPU,3), and therefrom an angular position of rotation calculated, allowing for extremely precise determination of the angular position and distance of the magnet with respect to the magnetometer(s) MGR,8). These positions are correlated to a dose selected or selectable by the user in a lookup table which is preferably stored within the system, or alternatively stored within a remote data processing unit, such as a smartphone, wherein the maximum and minimum distances of allowed travel and rotation of the magnet (MAG,9) along the longitudinal axis correspond to the maximum and minimum dosages allowed by the drug delivery device. In this way, the dose control system is able to present to the user an exact representation of the dose selected by the user at any given rotational and translational movement point of the magnet (MAG,9), without interfering or changing the usual modus operandi of the drug delivery device. In an exemplary dose control system of the invention, the magnetometer(s) are configured to be able to detect magnetic fields from between +4 gauss to +16 gauss, with a sensitivity, or resolution, of between about 6842 LSB/gauss at +4 gauss to about 1711 LSB/gauss at +16 gauss. This means that the dose control system preferably has a resolution that is able to detect changes in magnetic field corresponding to an angular rotation of the magnet and dose selector shaft of 0.9° about the longitudinal axis, but as mentioned above, the resolution and sensitivity of the various components can be configured to correspond to any drug delivery device that functions in the same way via a rotatable dose selector shaft.

Also represented inFIG.1are a power supply (POW,10), which is generally a portable, autonomous power supply, for example, one or more batteries, or rechargeable power elements, capable of supplying sufficient electrical power to the entire system, even when for example, the device is not being directly manipulated. The integrated control unit (2) can additionally comprise a power management unit, that regulates power supply voltage to the system, including its various components, in order to maximise the longevity of said autonomous power supply. The power supply can also communicate with a user-activated wake-up button (WAK,11) which allows the dose control system to be woken up by the user from a hibernating or sleeping state.

The dose control system can also further comprise a light emitting signal (LIG,12), for example, a LED, which indicates a status of the device according to detected events or conditions and managed by the central processing unit (CPU,3), e.g. green, red, blue and white colour emission, each colour corresponding to a certain state or condition of the dose control system.

In yet a further embodiment, the dose control system can also comprise an alarm (ALA,13) system, in communication with the central processing unit (CPU,3), which can be configured to emit an audible alarm, say, in the case of malfunction of the system, or in the case of a failed injection, or for any other suitable condition or event detected within the system.FIG.2is a schematic block diagram representation of the functioning of a dose control system according to the invention. In a first step, wheel click detection (14) of the rotating dose selector shaft is effected by the accelerometer, as the click generates vibrations which are picked up by the accelerometer (ACC,7). The magnetic field values detected (15) by the magnetometer(s) (MGR,8) of the magnet (MAG,9) which rotates at the same time as the dose selector shaft are then read into the central processing unit (CPU,3). Next, the angle and modulus of the magnetic field are calculated (16) by the central processing unit (CPU,3). These values are correlated with, or compared to (17) a predetermined set of values that has been preprogrammed into the dose control system. Finally, a determination (18) of the selected dose is made. These steps are repeated as necessary, each time the user causes the dose selector shaft to rotate about the longitudinal axis. Once the user has decided which dose it wishes to inject itself with, a click caused by the user pressing a proximally located injector end button, which causes a vibration and corresponding movement of acceleration within the drug delivery device, is registered by the accelerometer. The frequency, or interval between each end button click is used to determine whether an injector button click is compared to a known list of pre-determined movements of acceleration to determine whether the end button click was intentional, or else the result of accidental activation of the end button or movement in the drug delivery device. If the movement of acceleration and frequency thereof do correspond to a situation in which the dose is recognized as having been deliberately selected, ready for injection, this dose is registered within the system, e.g. within memory, and communicated via the communication means to the data processing unit, for example, a smartphone application, along with the time at which said event occurred. In this way, the smartphone application is able to process that information and provide it to the user in the form of tracking or observance information.

FIG.3is a schematic cross-sectional representation of a dose control system mounted on an injectable-drug delivery device, indicated generally by the reference numeral20. The injectable-drug delivery device (20) generally comprises a substantially elongate drug delivery body (21), having a longitudinal axis (25), at least one injectable drug held by the body (not shown), usually within a cartridge, the body (21) having a distal extremity (23) and a proximal extremity (22), and an outer peripheral surface (24). InFIG.3, at the distal extremity (23), a cap (26), similar to a pen cap, is provided to cover the otherwise exposed needle and prevent the user from accidentally stabbing or otherwise injuring themselves. The drug delivery device further comprises, at the proximal extremity (22), a dose selector shaft (27), which is connected to a dose selector wheel (28), rotatable about the longitudinal axis, and an end button which can be pressed by the user to arm the device, thereby validating a selected dose, and effect drug injection via usual, known methods and means. This type of drug delivery device is similar to majority of drug delivery devices known to the skilled person.

The dose control system is indicated inFIG.3by the general reference numeral30. As is apparent fromFIG.3, the dose control system (30) is located substantially at a proximal extremity of the drug delivery device (20), and is positioned on and around the outer peripheral surface (24) of the body of said device. In this particular example, the central processing unit (CPU,3), real time clock (RTC,4), storage memory (MEM,6) and communications subsystem or communication means (COM,5) are located on a printed circuit board to form the integrated control unit (2) which is encased within a polymer resin block (31). The dose control system has an autonomous power supply (POW,10) in this example andFIGS.3and4illustrated as two batteries (32,33), for example lithium ion batteries. The dose control system further comprises magnetic field producing means (MAG,9), illustrated inFIG.3as a substantially annular shaped object which is located at the proximal extremity (22) of the device, and in a proximally spaced relationship to said extremity (22), whereby the magnet (MAG,9) is removably mounted on the dose selector wheel (28), which in turn is connected to the dose selector shaft. As the wheel (28), shaft (27) and magnet (MAG,9) can be caused to rotate around the longitudinal axis (25) of the drug delivery device (20), the magnet (MAG,9) will be displaced both rotationally around said axis thereby also effecting a translational movement away from, in a proximal direction, or alternatively, towards, i.e. in a distal direction, the proximal extremity of the body (21) of the drug delivery device (20). The maximum distance of linear travel of the wheel (28), shaft (27) and magnet (MAG,9), will generally substantially correspond to the maximum allowable dose that can be injected, and also therefore correspond to the maximum distance of travel of a piston that is usually provided to eject the drug from the cartridge in which it is held. As an example, the position nearest to the proximal extremity of the body of the drug delivery device will correspond to either no dose, or the minimum dosage. The wheel (28), shaft (27) and magnet (MAG,9) will be blocked from rotating in a direction that would be likely to bring the latter even closer to the proximal extremity (22) of the body (21). In the opposite direction, however, i.e. in the proximal direction, the wheel (28), shaft and magnet will be able to be caused to rotate, e.g. via a user turning the magnet (MAG,9) and wheel (28) with their fingers as many times as is allowed by the configuration of the system, and corresponding to the maximum dosage that can be injected. As the magnet, and wheel are turned, the shaft also rotates, and generates an audible clicking sound. The audible clicks correspond to a movement of acceleration transmitted through the body of the device and detected by the accelerometer (7). The rotation and longitudinal displacement of travel of the magnet (MAG,9) causes changes in the produced magnetic field which are detected by the magnetometers (34,35). The values detected by the magnetometers (34,35) are communicated to the central processing unit (CPU,3), and used to calculate angular position of the magnet (MAG,9) and wheel (28) on the dose selector shaft (27) and thereby determine the dose which has been selected by the user. Priming of the injector system, via a push from the user on the end button (29), which also raises an audible click, and a corresponding linear movement of acceleration along the longitudinal axis of the device (20), is registered by the accelerometer (7). The central processing unit (CPU,3) calculates the frequency and number of clicks produced and compares them to stored values in a lookup table to determine whether or not the device is effectively primed for injection, and if it is determined by the central processing unit that such is the case, the value of the calculated dose obtained from the changes in magnetic field is stored in memory (MEM,6) and validated as the dose selected for injection. This value is then communicated via the communication means (COM,5) to the smartphone application.

The magnetic field detectors can be configured to function in various ways. For example, in a serial configuration of magnetometers, i.e. when the magnetometers are aligned axially along the longitudinal axis, in a spaced apart relationship, and when the magnet (MAG,9) is closest to the proximal extremity of the body (21) of the drug delivery device, the force of the magnetic field produced by the magnet can exceed the upper limit of the magnetometer (8a) closest to the magnet. In such a case, the magnetomer (8a) is considered to be “saturated”. At this point, it is unnecessary to factor in any values detected by the second magnetometer (8b), since saturation of the first, proximal magnetometer (8a) allows for complete resolution of the angular moment and modulus when the magnet is rotated about the longitudinal axis. If the dose selector shaft is designed to also effect lateral displacement along said longitudinal axis, proximally, and away from said proximal extremity, as the magnet also moves away proximally, so does the saturation of the first proximal magnetometer (8a) drop. Once a predetermined level of magnetic field has been reached, the system is configured to activate the second, more distal magnetometer (8b), so that both magnetometers (8a,8b) can be used to effect fine detection of smaller and smaller changes in magnetic field and angular moment, including taking into account any effects due to the earth's own magnetic field which, at the earth's surface is generally between 0.25 and 0.65 gauss. In a similar and reverse manner, when the dose selector shaft, and magnet, move distally back towards the proximal extremity of the body of the device, the second, more distal magnetometer (8b) can be automatically switched off when a predetermined higher level of magnetic field is detected. In an alternative, parallel, configuration, on the other hand, both magnetometers (8a,8b), whilst still aligned along the longitudinal axis of the drug deliver device, are both operational throughout all of the displacements of the magnet, and all changes in magnetic field are detected by both magnetometers (8a,8b).

FIG.4is a schematic cross-sectional representation of a housing suitable for including the dose control system of the present invention and illustrating one of several ways in which the dose control system can be mounted on an injectable-drug delivery device such as those currently known. Reference numerals remain the same betweenFIGS.3and4for like elements of the dose control system. The housing (35a,35b) is designed to encase and enclose the drug delivery device (20), around and along its longitduinal axis (25) and sits removably on a peripheral outer surface (24) of said device (20). The housing is designed to snap or push fit onto the device (20) and preferably comprises at least two mating components, which engage with each other and encase the device along its body (21), along the longitudinal axis (25), at a proximal extremity (22) thereof. The housing (35a,35b) further comprises grip facilitating means, for example a zone (36a,36b) of compressible elastomer, locate on an inner wall of the housing, and which facilitates and increases the grip of the housing containing the dose system on the outer peripheral surface (24) of the body (21) of the drug delivery device (20) to provide a snug fit that will prevent the housing (35a,35b) from moving relative to the body of the drug delivery device until such time as the housing is to be removed, for example, if the drug delivery device malfunctions, or the cartridge is empty or quite simply if it is desired to switch the dose control system to another drug delivery device (20). The housing is designed preferably to be snap fit, enabling it to be removed according to a predetermined set of steps, wherein each part of the housing (35a,35b) is removed according to a sequence, without destroying or damaging the dose control system (30) contained therein, or the drug delivery device (20). The zone of compressible elastomer (36a,36b) can further comprise compression facilitating ridges or dips (37a,37b), i.e. added or removed elastomeric material in spaced apart arrangement along the the length and breadth of the zone (36a,36b) so as to increase or decrease grip of the housing (35a,35b) on the outer peripheral surface (24) of the device (20). The housing (35a,35b) additionally provides a window (39) allowing a user to see an analog or digital representation of the selected dose, which is generally located and displayed on the outer peripheral surface (24) of the body (21) of the drug delivery device (20). The dose control system containing the magnetic field producing means (MAG,9) is housed in a separate housing (38) that is located, and fits snugly with, the wheel (28). This magnet housing (38) is designed in a similar way to the housing (35a,35b) of the other components of the dose control system to able to be removably snap or push fit onto the wheel (28) of the dose selector shaft (27) and can also advantageously comprise grip facilitating means, for example a zone of elastomeric material enabling the magnet housing (38) to surround and encase the wheel (28).