Source: https://patents.google.com/patent/US8465460B2/en
Timestamp: 2019-04-24 21:17:27
Document Index: 536668435

Matched Legal Cases: ['§371', 'art 100', 'art 200', 'art 100', 'art 200', 'Application No. 60', 'Application No. 61', 'Application No. 60', 'art 200', 'art 200', 'art 200', 'art 200', 'art 100', 'art 100', 'art 100', 'art 200', 'art 200', 'art 200', 'art 200', 'art 200', 'art 200', 'art 200', 'art 200', 'art 200', 'art 200', 'art 200', 'Application No. 60', 'art 200', 'art 100']

US8465460B2 - Device for drug delivery - Google Patents
US8465460B2 US12/733,009 US73300908A US8465460B2 US 8465460 B2 US8465460 B2 US 8465460B2 US 73300908 A US73300908 A US 73300908A US 8465460 B2 US8465460 B2 US 8465460B2
US12/733,009
US20100292651A1 (en
2008-07-31 Priority to US12/733,009 priority patent/US8465460B2/en
2010-10-19 Assigned to MEDINGO LTD. reassignment MEDINGO LTD. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: IDDAN, GAVRIEL J., YODFAT, OFER, GESHEIT, ILLAI
2010-11-18 Publication of US20100292651A1 publication Critical patent/US20100292651A1/en
2013-06-18 Publication of US8465460B2 publication Critical patent/US8465460B2/en
Disclosed is an ambulatory therapeutic fluid delivery device (10). The device includes at least one housing (200) connectable to a cannula (250), the at least one housing retaining a reservoir (220) to hold the therapeutic fluid. The device also includes a mechanically powered pumping mechanism (150) to cause delivery of at least some of the fluid from the reservoir, and a power-transfer mechanism to transfer manually-delivered power provided by a user to mechanically actuate the pumping mechanism.
The present application is a 35 U.S.C. §371 national stage entry of PCT/IL2008/001058, which has an international filing date of 31 Jul. 2008 and claims priority to U.S. Provisional Patent Application Nos. 60/963,071, filed on 1 Aug. 2007 and 61/003,169, filed on 14 Nov. 2007. The present application incorporates herein by reference the disclosure of each of the above-referenced applications in its entirety.
In all MDI regimens, intermediate—or long-acting insulins (e.g., NPH, lente, ultralente, or glargine insulin) supply basal insulin, whereas short acting insulin (e.g., regular, insulin aspart, or lispro insulin) provides prandial insulin. Lispro and insulin aspart should be injected just before or just after a meal; regular insulin dosages are given 30 to 45 min prior to a meal. No insulin MDI regimen reproduces the precise insulin secretory pattern of the pancreatic islet. However, the most physiologic regimens entail more frequent insulin injections, greater reliance on short-acting insulin, and more frequent capillary plasma glucose measurements (Harrison's Principles of Internal Medicine, 16th edition, chapter 323).
The reservoir may be fellable by the user.
The method may further include determining extent of fluid delivered. Determining the extent of the fluid delivered may include detecting one or more markings disposed on a power-transfer mechanism to transfer the manually generated power. The detection of the one or more markings may be indicative that a pre-determined amount of fluid was delivered. Detecting the one or more markings may include illuminating a light beam towards a first surface of the power-transfer mechanism having one or more holes extending from the first surface to another surface of the power-transfer mechanism, and detecting light passing through the one or more holes.
FIG. 1 a is a schematic diagram of an exemplary single-part fluid delivery device.
FIG. 1 b is a schematic diagram of an exemplary two-part fluid delivery device.
FIGS. 2 a-c are views illustrating an exemplary fluid-delivery device being secured directly to the skin of the patient.
FIGS. 3 a-c are views illustrating connection of an exemplary fluid delivery device to a cradle unit.
FIGS. 4 a-c are views illustrating connection and disconnection of an exemplary fluid delivery device from a port unit.
FIGS. 5 a-c are schematic diagrams and views of an exemplary cradle unit.
FIGS. 6 a-c are schematic diagrams and views of an exemplary port unit.
FIGS. 7 a-b are schematic and isometric views of an exemplary disposable part of a fluid delivery device.
FIGS. 8 a-b are schematic and isometric views of an exemplary reusable part of a fluid delivery device.
FIGS. 10 a-b are schematic diagrams of exemplary disposable parts.
FIGS. 11 a-g are schematic diagrams and views depicting an exemplary reservoir-filling process using a plunger.
FIGS. 12 a-b are schematic diagrams illustrating exemplary connection of the therapeutic fluid container to an adapter.
FIGS. 13 a-f are views and diagrams illustrating an exemplary reservoir-filling process using a syringe.
FIGS. 14 a-c are schematic diagrams of an exemplary cannula cartridge unit before and after insertion.
FIGS. 15 a-b are schematic diagrams depicting connection of an exemplary fluid delivery device to an exemplary cradle.
FIGS. 17 a-b are schematic diagrams of an exemplary manually-powered delivery device with a piston-based pumping mechanism.
FIGS. 19 a-c are schematic diagrams of an exemplary fluid delivery device with a piston-based pumping mechanism and a limiter.
FIGS. 21 a-c are perspective views of an exemplary manually-powered actuation process using a spring mechanism.
FIGS. 23 a-c are perspective views illustrating operation of a pump-air fluid delivery device.
FIGS. 24 a-b are schematic diagrams of a fluid delivery device using a pump-air mechanism.
FIGS. 25 a-c are schematic diagrams of another exemplary configuration for a fluid delivery device with a piston-based mechanism.
FIGS. 26 a-b are perspective views of an exemplary fluid delivery device with a detachable counter.
FIGS. 27 a-c are schematic diagrams illustrating connection of an exemplary counter to a fluid delivery device.
FIGS. 28 a-b are schematic diagrams of an exemplary counter implemented with an optical sensing mechanism.
FIGS. 29 a-c are perspective views of an exemplary fluid delivery device with a detachable reservoir.
FIGS. 30 a-b are views of exemplary reservoirs of different sizes.
A dispensing patch unit having a reservoir and a driving mechanism (i.e., power-transfer mechanism). The dispensing patch unit (hereinafter referred to as the “patch unit” or the “dispensing device” or the “fluid delivery device”) may include one or more parts. The dispensing patch unit can be secured (e.g., adhered) directly to the skin of the patient.
A cradle unit that is securable (e.g., adherable) to the skin of the patient and configured to enable connection and disconnection of the dispensing patch unit.
Referring to FIGS. 1 a-6 c, schematic diagrams and views illustrating an exemplary fluid infusion device 10 and various exemplary configurations to attach the device 10 to the body of the patient are shown. FIG. 1 a is a schematic diagram of an exemplary single-part fluid delivery device 10. FIG. 1 b is a schematic diagram of an exemplary two-part fluid delivery device 10. The two-part device 10 may be configured to include a reusable part 100 and a disposable part 200. The reusable part 100 may include relatively expensive components of the device 10 such as, for example, a driving mechanism (i.e, a power transfer mechanism) to cause fluid delivery from the reservoir to the patient's body. The disposable part 200 may include the relatively cheaper and replaceable components of the device 10 such as, for example, the reservoir, cannula, etc.
Referring to FIGS. 2 a-c, views depicting exemplary ways of securing the device 10 to the skin 5 of a patient are shown. FIG. 2 a illustrates removal of an adhesive protection layer 101 from the dispensing device 10. FIG. 2 b illustrates securing the dispensing device 10 to the skin 5 of the patient. FIG. 2 c illustrates the device 10 being secured (e.g., adhered) to the skin 5 of the patient. The device 10 may be adhered directly to the skin 5 of the patient.
Referring to FIGS. 3 a-c, views illustrating an exemplary cradle unit 20 that is secured to the skin 5 of the patient are shown. The dispensing device 10 may be connected to and disconnected from the cradle unit 20 at the patient's discretion. FIG. 3 b shows exemplary connection of the dispensing device 10 to the cradle unit 20. FIG. 3 c illustrates an exemplary dispensing device 10 being connected to the cradle unit 20 and ready to operate.
Referring to FIGS. 4 a-c, views illustrating an exemplary port unit 30 secured to the skin 5 of a patient are shown. The dispensing device 10 may be connected to the port unit 30 during operation of the device 10 (e.g., during drug delivery). After completion of the drug administration, the dispensing device 10 may be disconnected from the port unit 30 and kept away from the patient. A description of port units similar to the port unit 30 are provided, for example, in co-owned U.S. Provisional Application No. 60/963,039, filed Aug. 1, 2007, and entitled “Device and Method for the Infusion of Therapeutic Fluid and Sensing of Bodily Analytes,” U.S. Provisional Application No. 61/008,694, filed Dec. 21, 2007, and entitled “Device and Method for the Infusion of Therapeutic Fluid and Sensing of Bodily Analytes,” as well is in co-owned non-provisional U.S. patent application entitled “Device and Method for the Infusion of Therapeutic Fluid and Sensing of Bodily Analytes,” filed on the same day as the present application, the contents of all of which are hereby incorporated by reference in their entireties. The port unit 30 is configured to enable the patient/user to adhere a much smaller and less bulky item to the skin 5 instead of securing the larger cradle unit 20 to the skin 5. The port unit is coupleable to a cradle unit and/or a fluid delivery device. In some embodiments, the patient cannot leave the dispensing device 10 attached to the body when using the port unit 30. FIG. 4 a illustrates the port unit 30 being adhered to the body of the patient FIG. 4 b illustrates an exemplary connection of the dispensing device 10 to the port unit 30. FIG. 4 c illustrates the dispensing device 10 being disconnected from the port unit 30.
Referring to FIGS. 5 a-c, schematic diagrams and views of an exemplary cradle unit 20 are shown. FIG. 5 a is a cross-sectional view of the cradle unit 20 secured (e.g., adhered) to the skin 5 of the patient. The cradle unit 20 includes a flat surface 300 with an adhesive layer attached to its bottom (not shown in FIG. 5 a) and latches 302 and (304) to secure a dispensing device to the cradle unit 20. The cradle unit also includes a well 310 to enable passage of a cannula (not shown in FIG. 5 a) during its insertion into the skin (e.g., into the subcutaneous tissue). FIG. 5 b is a top view of the cradle unit 20. FIG. 5 c is an isometric view of the cradle unit 20.
Referring to FIGS. 6 a-c, diagrams of an exemplary port unit 30 are shown. FIG. 6 a is a cross-sectional view of the port unit 30 being secured (e.g., adhered) to the skin 5 of the patient. FIG. 6 b is a top view of the port unit 30. FIG. 6 c is an isometric view of the port unit 30. The port unit 30 includes a flat surface 401 having an adhesive layer attached to its bottom (not shown in FIGS. 6 a-c) and latches 402, 404 and 406 to secure the dispensing device 10 to the port unit 30. A cannula (not shown in FIGS. 6 a-c) may be inserted via the well 310 using an inserter such as an inserter described, for example, in co-owned International Patent Application No. PCT/IL08/000,860, filed Jun. 25, 2008, claiming priority to U.S. Provisional Patent Application No. 60/937,214, entitled “Insertion device for inserting a cannula into a body,” filed on Jun. 25, 2007, the content of which is hereby incorporated by reference in its entirety.
Referring to FIGS. 7 a-9, schematics and views of an exemplary two-part dispensing patch device 10 that includes a disposable part and a reusable part are shown.
FIG. 7 a illustrates an exemplary disposable part 200. The disposable part 200 includes a reservoir 220, a tube 230 and an outlet port 213 through which therapeutic fluid (e.g., insulin) can be injected to the body of the patient. FIG. 7 b is an isometric view of the disposable part 200. The disposable part 200 can be configured to be replaced either at predetermined time intervals (e.g., 3 day intervals), whenever the reservoir 220 becomes empty, or automatically.
Referring to FIG. 8 a, a schematic diagram of an exemplary reusable part 100 of a fluid-dispensing device is shown. The reusable part 100 includes a mechanical driving and pumping mechanism (collectively designated 150 in FIG. 8 a), a counter 900 and one or more actuation units 14 to, for example, transfer manual-power provided by the user to power the driving and/or pumping mechanisms. The driving and pumping mechanism 150 may be configured as low-cost mechanisms manufactured from relatively inexpensive components. FIG. 8 b is an isometric view of the reusable part 100.
Referring to FIGS. 10 a-13 f, diagrams depicting an exemplary piston-type pumping mechanism and exemplary ways of filling the reservoir 220 with therapeutic fluid are shown.
Referring to FIG. 10 a, a schematic diagram of an exemplary disposable part 200, functioning by itself as a reservoir 220, is shown. In this configuration, the volume of the reservoir 220 is limited by the volume of the disposable part 200. The device includes a piston-type pumping mechanism. The pumping mechanism is provided with a piston 112 which includes a plunger rod 110 and a plunger head 111. The piston is configured to push fluid towards an outlet port 213 that is typically situated at the bottom of the disposable part 200. FIG. 10 b depicts another implementation of an exemplary disposable part 200 that includes dedicated reservoir 220 and a piston 112. In the shown embodiment of FIG. 10 b, the piston 112 includes a plunger rod 110 and a plunger head 111. The piston 112 can be situated inside the reservoir 220. A tube 230 is provided to deliver therapeutic fluid from the reservoir 220 to the outlet port 213.
Referring to FIG. 11 a, a cross-sectional schematic diagram of an exemplary disposable part 200, similar to the disposable part 200 depicted in FIG. 10 b, is shown. The disposable part is depicted prior to filling of the reservoir 220 with fluid. Filling of the reservoir 220 is performed using a plunger rod 110 and a plunger head 111. Referring to FIG. 11 b, a diagram of an exemplary drug vial 9 prior to its connection to the disposable part 200 is shown. FIG. 11 c illustrates the vial 9 connected to the outlet port 213. As shown, the disposable part 200 may include a connecting lumen 250 to pierce the vial septum 7 to enable fluid to be drawn from the vial 9 to the reservoir 220 using, for example, a retractable plunger. FIGS. 11 d-11 f illustrate an exemplary filling procedure of the reservoir 220. The amount of fluid to be drawn may be determined based on the patient's daily dose requirement to thus reduce therapeutic fluid waste. FIG. 11 g illustrates exemplary priming (e.g., air purging) of the reservoir 220. Air bubbles can be purged by holding the disposable part 200 in a substantially upright position (i.e., when the outlet port 213 is generally elevated) and gently pressing the plunger 112 until fluid 8 is seen to be dripping from the outlet port 213.
Referring to FIG. 12 a-b, schematic diagrams of another exemplary reservoir filling procedure using an auxiliary adapter 216 are shown. FIG. 12 a depicts the adapter 216 having two ports: an upper port 211 and a lower port 211′. The upper port 211 is configured to be connected to the vial 9 and may be provided with a needle 215 to pierce the vial's septum 7. The lower port 211′ is configured to be connected to the reservoir 220 and can be sealed with a rubber septum 217 that is pierceable by a lumen 250 disposed in the outlet port 213. A displaceable piston 112 may be received (at least partially) within the volume of the reservoir 220 of the disposable part 200. FIG. 12 b illustrates an exemplary connection of the adapter 216 to the disposable part 200 and the vial 9. To draw fluid from the vial 9, the piston 112 is retracted outwardly from the inner volume of the reservoir 220 to cause fluid from the vial to be received.
In some embodiments, the reservoir 220 of the dispensing device may be filled using a syringe. Referring to FIGS. 13 a-f, diagrams depicting an exemplary reservoir-filling procedure using a syringe 80 are shown. FIG. 13 a illustrates fluid being drawn from the vial 9. FIG. 13 b illustrates the reservoir 220 having an outlet port 213 at its bottom surface. In some embodiments, the reservoir 220 can be connected to the outlet port 213 via a tube (not shown in FIG. 13 a). The syringe needle 218 is configured to pierce the rubber septum 219 of the inlet port 212 to enable filling. Referring to FIGS. 13 c-13 e, diagrams depicting another exemplary reservoir-filling procedure using a syringe are shown. FIG. 13 f illustrates an exemplary priming procedure of the reservoir 220. As shown in FIG. 13 f, the reservoir is filled until fluid drops 8 begin to drip from the outlet port 213.
Referring to FIG. 14 a, a schematic diagram of an exemplary cannula cartridge unit 400 is shown. The cannula cartridge unit 400 includes a cannula hub 414, a septum 311 and a cannula 6. FIG. 14 b illustrates an exemplary port unit 30 configured to receive the cannula cartridge unit 400. The port unit includes a well 310 through which the cannula cartridge unit 400 is inserted. The cannula cartridge unit 400 can be inserted using, for example, an inserter (e.g., manual, semi-automatic and/or automatic). A description of such an exemplary inserter is disclosed, for example, in co-owned International Patent Application No. PCT/IL08/000,860, filed Jun. 25, 2008, claiming priority to U.S. Provisional Patent Application No. 60/937,214, entitled “Insertion device for inserting a cannula into a body,” filed on Jun. 25, 2007, the content of which is hereby incorporated by reference in its entirety. FIG. 14 c illustrates cannula cartridge unit 400 that has been inserted into the well 310 of the port unit 30 and the cannula 6 subcutaneously inserted into the patient's skin.
Referring to FIG. 15 a, a schematic diagram of an exemplary fluid delivery device 10 positioned to being connected to the port unit 30 is shown. FIG. 15 b illustrates the exemplary device 10 connected to the port unit 30. As shown, a connecting lumen 214, provided in the fluid delivery device, is configured to pierce the septum 311 of the port unit to thus enable fluid to flow from the reservoir 220 to the cannula 6 and to the subcutaneous layer 4.
FIG. 16 is a perspective view of an exemplary dispensing device 10. The dispensing device 10 can be provided with any of the above-described components/units and/or with a dedicated controller to perform manual/semi-automatic/automatic/or otherwise regulate fluid delivery to the body of the patient. In some embodiments, such a controller enables manual actuation of a driving and/or pumping mechanism of the device 10 and may include, for example, an activation wheel 195. As will become apparent below, rotation of the activation wheel (also referred to as an actuation wheel) 195 causes fluid infusion/delivery. A counter 900 may be disposed on the dispensing patch unit to enable control of to be delivered dose(s). Manual rotation of the activation wheel 195 may cause actuation of the pumping mechanism (e.g., piston-type or peristaltic-type pumping mechanism) to thus cause fluid infusion to be performed. For an accurate control of fluid delivery, an indicator producing a signal (e.g., a click sound, a visual indication such as flashing light, or any other indication) may be provided to accompany activation/actuation of the wheel 195. In some embodiments, the activation wheel rotation is rotatable in a unidirectional manner to prevent retraction of delivered therapeutic fluid back into the reservoir. Alternatively and/or additionally, the pumping mechanism may be retracted in particular situations, such as, for example, during reservoir filling, reservoir replacement, to verify the driving mechanism proper functionality, etc.
Referring to FIG. 17 a, a schematic diagram of an exemplary fluid delivery device 10 that includes an activation/actuation wheel 195 operatively coupled to a piston-type pumping mechanism 151 is shown. The activation wheel 195 may be connected to a power-transfer mechanism (also referred to as a driving mechanism) to transfer manually-delivered power provided by a user to mechanically actuate a pumping mechanism. The delivery device may thus be implemented without using electrically-generated power. The driving mechanism may include, in some embodiments, one or more gears. For example, the one or more gears may include a small-size cog-wheel 606 having teeth that can engage with teeth of a larger cog-wheel 615. Rotation of the wheel 195 causes the larger cog-wheel 615 to turn and to consequently rotate a worm 610. One end of the worm 610 is rigidly connected to one side of a rod 612. The other side of the rod 612 is connected to a cog-wheel 608. Rotation of the cog-wheel 608 urges a screw-nut 614 operatively coupled therewith to turn. By turning the screw-nut 614, the threaded rod of piston 112 of the pumping mechanism, which is operatively coupled to the screw-nut, is linearly displaceable in a forward direction. When linearly displaced, the piston 112 is configured to push fluid within the reservoir 220 and force it to pass through the tube 230 and exit from the outlet port 213.
FIG. 17 b further illustrates the piston-type pumping mechanism during movement of the piston 151, which forces fluid to exit through the outlet port 213. After completing the infusion operation and depleting the reservoir, the user (e.g., patient) can manually retract the piston 112 (e.g., using a handle coupled to the piston 112) backward until the piston is in its initial position, whereupon the reservoir and/or the entire disposable part 200 may be replaced with a new one.
Referring to FIG. 19 a, a schematic diagram of another exemplary fluid delivery device with a manually-powered driving and pumping mechanism, similar to those depicted in FIGS. 17 a-b, and that further includes a limiter 616 is shown. The limiter 616 is configured to prevent displacement of the piston beyond a pre-set spatial position defined by the limiter. The pumping mechanism is provided with a screw-nut 613 and a limiter's nut 614. The rotating screw nut 613 rotates the limiter's nut 614 which consequently displaces the limiter 616 in a forward direction or by actuating the piston with the driving mechanism. The limiter 616 position sets the allowed distance for piston displacement. The displacement of the piston 112 may be performed, for example, by pushing the handle 197 in a forward direction. Piston displacement can be halted when the piston's bottom end 618 comes in contact with the limiter 616. In some embodiments, additional safety measures may be employed to enable the patient to press the handle 197 in a downward direction prior to displacement of the handle 197. Such safety measures would prevent unintentional bolus delivery. FIG. 19 b illustrates an exemplary device 10 after dose adjustment, performed by rotating the activation/actuation wheel 195 which causes the limiter 616 to advance an to initial position. FIG. 19 c illustrates the piston 112 at the end of the drug delivery operation when the bottom end 618 of the piston reaches the point of contact with the limiter 616. In some embodiments, the limiter may be actuated separately from the driving mechanism. Alternatively and/or additionally, the limiter may be used as a safety mechanism to lock the driving mechanism and to thus prevent accidental fluid delivery.
Referring to FIGS. 21 a-c, diagrams of an exemplary fluid delivery device 10 having a spring-based mechanism to actuate the power-transfer and/or pumping mechanism of the device is shown. The spring mechanism is provided with a spring, loadable upon pulling a spring handle 702 connected to a pulling string 704 to enable delivery of a pre-determined dosage (e.g., bolus dosage). This mechanism thus frees the patient/user from having to continually manually actuate the device until delivery of the required dosage is completed. Thus, after the spring of the spring mechanism is loaded (i.e., the string is pulled), the release of the spring (e.g., to cause delivery of bolus dosage) requires no additional operational intervention from the patient. FIG. 21 a illustrates dispensing device 10 prior to commencement of delivery operations. FIG. 21 b illustrates the device 10 in operation, i.e., during the pulling action. As shown, the string coupled to the spring is pulled, using a pulling-spring handle 702 to an initial position. Particularly, the string coupled to the spring is pulled in a rotational direction opposite the rotational direction at which the spiral spring is biased. FIG. 21 c illustrates retraction of the pulling string 704 upon release of the pulling handle 702. Release of the string causes the spiral spring to rotate in the direction in which the spiral spring is biased to thus cause rotation of the at least one gear coupled to the spring-based mechanism.
Referring to FIG. 22, a schematic diagram of a driving mechanism (power-transfer mechanism) 152 actuated by a spiral spring 706 (in a manner similar to that shown in relation to FIGS. 21 a-c) is shown. A handle 702 is connected to the spiral spring 706 by a string 704. By pulling the handle 702, the patient loads the spiral spring 706. Upon release of the handle 702, the spiral spring 706 is discharged and drives one or more gears, for example, the cogwheels 714, 716 and 718. The one or more gears of the driving mechanism cause, in turn, a rotor 512 of the peristaltic-based mechanism to be rotated. Rotation of the rotor 512 causes dispensation of fluid via the tube 230 to the outlet port 213 and to the body of the patient. Each string pulling and releasing action corresponds to the discharge of a predetermined dose (e.g., 1 IU of insulin) into the body of the patient. In some embodiments, this driving mechanism 152 can be employed to actuate a piston-type pumping mechanism (not shown in FIG. 22). The driving mechanism 152 may be configured to impart to the dispensing patch unit an ability for autonomous control of fluid delivery, i.e. the dispensing is completely controlled by the patient (e.g., the user provides entirely the actuation required to cause operation of the driving mechanism and/or the pumping mechanism).
Referring to FIGS. 23 a-c, perspective views of an exemplary fluid delivery device including a user-actuated “pump-air” infusion pump is shown. FIG. 23 a illustrates fluid pumping by pressing buttons 15 provided on both sides of the device 10. FIG. 23 b illustrates pumping by pressing a pumping button 16 situated on the top of the device 10. FIG. 23 c illustrates pumping by using activation/actuation mechanism configured as a blower 17. A transparent window 950 enables monitoring of the content of reservoir 220.
Referring to FIGS. 24 a-b, schematic diagrams of an exemplary fluid delivery device 10 that includes a “pump-air”-based mechanism 153 is shown. The pump-air mechanism includes an inflatable air container 802 to actuate the reservoir 220, and at least one air-injection device to deliver air to the inflatable air container. In some embodiments, each of the at least one air injection device includes an air tube in communication with the air container and an air compression chamber in communication with the air tube. The air compression chamber includes a plunger displaceable by the user within an inner volume of the air compression chamber. In some embodiments, the plunger is implemented as a user-actuatable button 15 coupled to an outwardly biased spring. Actuation of the button to push it inwards into the air compression chamber causes air to be pumped into the air container. When the user releases the button, the outwardly biased spring causes the button to be displaced outwardly to its initial position to thus cause ingress of ambient air into the air compression chambers 808. FIG. 24 a illustrates a dispensing device 10 in its initial state prior to operation, at which point the buttons 15 are not pressed and the displaceable plungers (e.g., the buttons coupled to the springs 806) are in their released positions. As shown, the inflatable air container 802 is connected via air tubes 810 and unidirectional valves 803 to the air compression chambers 808. In the schematic of FIG. 24 a, the air container is substantially empty. FIG. 24 b illustrates the device 10 in operation. By pressing the buttons 15, air is pushed from the chambers 808 via the air tubes 810 and the unidirectional valves 803 into the air container 802. The air container 802 inflates and causes actuation of the reservoir 220 to thus cause dispensation of the fluid from the reservoir 220. The air container 802 remains inflated as the air movement out is limited by the unidirectional valves 803. In some embodiments, air movement into the air compression chambers is directed by unidirectional valves enabling entrance of ambient air into the chamber and preventing its release from the air compression chambers.
Referring to FIG. 25 a, a schematic diagram of an exemplary device 10 prior to its connection to an indicator (counter) 900 is shown. As shown in FIG. 25 a, racks of the rod 58 and racks of the gear 56 are not engaged at that point. Thus, rotating the gear 56 will not move the plunger 55. FIG. 25 b illustrates an exemplary device 10 after connection of the counter 900. The connection of the counter 900 to its housing 907 engages the gear 56 and the threaded rod 58. FIG. 25 c illustrates the device 10 in operation. By turning the rotation wheel 50, a set of gears (cog wheels) are actuated. The teeth of the gear 56 and the thread of the threaded rod 58 are configured to engage and cause the plunger 55 to move in a forward direction, which causes infusion to occur.
Referring to FIGS. 26 a-b, perspective views of an exemplary detachable digital counter 900 to facilitate reservoir content monitoring and control is shown. Detaching the counter 900 enables the patient to estimate the status of the dispensing device 10 without suspending its operation. FIG. 26 a illustrates the digital counter 900 being detached from its housing 907. The counter 900 can be detached by, for example, pressing a release button 903. FIG. 26 b illustrates the counter clock 900 being grasped by the patient (e.g., held in the patient's hand). The patient can connect and/or disconnect the digital counter 900 while the pump 10 remains attached to the body and in continued operation. The counter 900 may be a mechanical, electrical, optical or electrochemical counter. In some embodiments, the counter and the dispensing device may communicate wirelessly, enabling status update of the dispensing device when the counter is detached from the device.
Referring to FIGS. 27 a-28 b, schematic diagrams of exemplary durable optical counter 900 are shown.
FIG. 27 a is a schematic diagram of an exemplary embodiment of a counter 900. The counter 900 includes of a power source (e.g., a battery 62), and two connectors 65 and 65′, a counting controller 64 to perform the counting operations and a display 66. FIG. 27 b is a schematic diagram of an exemplary fluid delivery device 10 (e.g., a device implemented using a peristaltic-based pumping mechanism) without the counter 900 being connected to the device. The reusable part 100 of the device 10 includes a measurement unit to determine the extent of fluid delivery. Such a measurement unit may include an optical sensing unit 70 and two connectors 67 and 67′. The optical sensing unit 70 is configured to detect one or more markings disposed on the power-transfer mechanism (the driving mechanism). Detection of the one or more marking is indicative that a pre-determined amount of therapeutic fluid was delivered. The optical sensing unit includes a source of light and a detector. The source of light and the detector can be configured to be located on each side of one of the gears constituting the driving mechanism (e.g., the cog wheel 69). In some embodiments, the markings on the cog wheel 69 may be holes 73 and 73′. FIG. 27 c depicts the counter 900 being connected to the device 10. By connecting the counter 900 to the device 10, the device's electrical circuit is closed and thereby enables measurement of data by the optical sensor 70, wherein such data is forwarded to the counter 900 and displayed. Specifically, the light source of the optical unit 70 is configured to illuminate a light beam towards one surface of the cog wheel 69. As the cog wheel rotates, the position of at least one of the holes will cross the path of the illuminated light beam, and as a result the light beam will pass through the hole and be detected by the sensor. Detection of the light beam will thus indicate that a particular amount of fluid (corresponding to the amount of fluid resulting from rotation of the cog wheel 69 by a certain amount) has been delivered.
FIG. 28 a illustrates light 2000 passing through one of the holes 73′ in the cog-wheel 69 from the light source 71 to the optical detector 72. FIG. 28 b illustrates light 2000 being blocked when it cannot pass through the cog wheel 69 (thus indicating that the pre-determined amount of fluid has not yet been fully delivered).
FIGS. 29 a-c illustrate exemplary ejection of a replaceable reservoir. Patients of Type 2 DM pumps use reservoirs with different reservoir volumes (e.g., different amount of insulin) depending on various medical and body conditions/needs. Replacing only the reservoir within the dispensing device 10 enables the patient to use the same dispensing patch unit 10 and change the amount of fluid to be delivered without replacing the whole patch unit 10. FIG. 29 a illustrates an exemplary reservoir cover 222 opened by pressing a button 224. FIG. 29 b illustrates the reservoir 220 inside its chamber 226 while the chamber cover 222 is open. FIG. 29 c illustrates ejection of the reservoir 220 from the chamber 226.
FIG. 30 a-b illustrate exemplary various-size reservoirs 220 that may be employed in the dispensing device 10. Particularly, FIG. 30 a shows a 2 IU size insulin reservoir 220, while FIG. 30 b shows a 5 IU insulin reservoir 220.
at least one housing connectable to a cannula;
a counter for displaying a value representative of an amount of therapeutic fluid delivered by operation of the device, the counter comprising a mechanically detachable counter housing configured for attaching and detaching from the at least one housing; and
a cradle securable to the patient's skin, wherein the cradle is configured for releasably receiving the at least one housing enabling connection and disconnection of the at least one housing therefrom;
the at least one housing including:
a reservoir for storing a therapeutic fluid;
a pump for delivering one or more bolus doses of the therapeutic fluid from the reservoir to the body of the patient through the cannula, wherein the pump is configured for non-electrical operation; and
an actuator for transferring manual power provided by the patient for operating the pump; wherein displacement of the pump is limited for delivery, of a bolus dose corresponding to a pre-determined amount.
2. The device of claim 1, wherein the therapeutic fluid includes one or more of: insulin, pramlintide acetate and exenatide.
3. The device of claims 1 wherein the at least one housing includes:
a disposable part housing including at least a part of the reservoir and an outlet port for enabling passage of the fluid to the body of the patient; and
a reusable part housing removably attachable to the disposable part, the reusable part housing including at least a portion of the pump and the actuator; wherein the device is operable upon attachment of the reusable part housing and the disposable part housing.
4. The device of claim 1, wherein the actuator comprises a user-actuated rotatable wheel and one or more gears for transferring power between the wheel and the pump for causing delivery of a bolus dose in response to rotation of the user-actuated wheel.
5. The device of claim 4, wherein the one or more gears comprise at least one cog wheel in mechanical communication with at least one worm gear and a screw-nut coupled to the worm gear and further coupled to a piston of the pump such that rotation of the worm gear causes displacement of the piston.
6. The device of claim 1, wherein the pump comprises:
a piston coupled to the reservoir, the piston being further coupled to the actuator; wherein movement of the piston by the actuator results in displacement of the piston for delivery of a bolus dose.
7. The device of claim 6, wherein the pump further comprises a handle coupled to the piston to enable manual displacement of the piston.
8. The device of claim 1, further comprising a limiter for limiting displacement of the pump, wherein the limiter prevents displacement of the pump or the actuator beyond a pre-set spatial position defined by the limiter corresponding to a bolus dose.
9. The device of claim 8, wherein the predetermined amount of a bolus dose is configurable by user adjustment of the limiter.
wherein the pump comprises a piston coupled to the reservoir and the actuator;
wherein movement of the piston by the actuator results in displacement of the piston for delivery of a bolus dose; and
wherein the limiter comprises a stationary block for engaging a projection extending from an end of the piston such that upon contact between the stationary block and the projection extending from the end of the piston, further displacement of the piston is prevented.
11. The device of claim 1, wherein the pump comprises a peristaltic pump, wherein the peristaltic pump comprises a rotor coupled to a delivery tube for delivering one or more bolus doses, the rotor further coupled to the actuator such that manual power transferred by the actuator causes rotation of the rotor resulting in displacement, of therapeutic fluid contained within the delivery tube.
12. The device of claim 1, wherein the actuator includes a spiral spring configured to operate the pump upon activation of the spring by the patient, and wherein the actuator further comprises: at least one gear coupled to the spiral spring, wherein the spiral spring is biased in a first rotational direction; and a string coupled to the spiral spring for causing rotation of the spiral spring in a second rotational direction for increasing in the tension of the spiral spring, wherein upon release of the string, the spiral spring rotates in the first rotational direction resulting in movement of the actuator resulting in pump operation.
13. The device of claim 12, further comprising a limiter for limiting displacement of the pump, wherein the limiter prevents the string from moving beyond a predetermined position such that upon release of the string, the spiral spring rotates a pre-determined radial distance causing delivery of a bolus dose by the pump corresponding with the predetermined amount.
14. The device of claim 1, wherein the pump comprises an inflatable air container configured for driving fluid from the reservoir, and wherein the actuator comprises at least one air injection device for delivering air to the inflatable air container.
15. The device of claim 14, wherein the at least one air injection device comprises: an air tube in communication with the inflatable air container; and an air compression chamber in communication with the air tube, the air compression chamber including a displaceable plunger, wherein upon movement of the plunger by the patient, air is displaced from the air compression chamber into the inflatable air container through the air tube.
16. The device of claim 1, further comprising an indicator for indicating operation of the pump.
17. The device of claim 16, wherein the indicator includes one or more of an audible indicator for producing a sound and a visual indicator for producing a visual signal.
18. The device of claim 1, wherein operation of the counter is based on operation of the actuator.
19. The device of claim 1, further comprising a measurement unit for determining an extent of fluid delivered.
20. The device of claim 19, wherein the measurement unit comprises an optical unit for detecting one or more markings disposed on the actuator, wherein detection of the one or more markings corresponds to a pre-determined amount of fluid delivered.
21. The device of claim 20, wherein the actuator comprises a gear having one or more openings extending from one surface of the gear to the other surface, and wherein the optical unit comprises: a light source for producing a light beam to illuminate one surface of the gear; and a light sensor for detecting light passing through the one or more openings.
22. The device of claim 1, wherein the at least one housing is configured for receiving different size reservoirs.
23. A portable ambulatory therapeutic fluid delivery device for delivering a therapeutic fluid as bolus doses into a body of a patient, the device comprising:
a cradle securable to the patient's skin, wherein the cradle is configured for releasably receiving the at least one housing for connection and disconnection of the at least one housing therefrom;
a pump for delivering one or more bolus doses of therapeutic fluid from the reservoir to the body of the patient through the cannula, the pump configured for non-electric operation; and
a user-actuated rotatable wheel; and one or more gears for transferring force between the rotatable wheel and the pump, wherein the one or more gears are configured for operating the pump resulting in delivery of one or more bolus doses in response to rotation of the user-actuated wheel, wherein displacement of the pump is limited for delivery of a bolus dose corresponding to a pre-determined amount.
24. A portable ambulatory therapeutic fluid delivery device for delivering a therapeutic fluid in bolus doses into a body of a patient, the device comprising:
a pump for delivery of one or more bolus doses of therapeutic fluid from the reservoir to the body of the patient through the cannula, the pump being configured for non-electrical operation; and
an actuator for transferring manual power provided by the patient for operating the pump, wherein the actuator includes a spiral spring configured for moving the actuator upon release of the spiral spring by the patient, wherein the actuator further comprises: at least one gear coupled to the spiral spring, wherein the spiral spring is biased in a first rotational direction; and a string coupled to the spiral spring for causing rotation of the spiral spring in a second rotational direction for increasing tension of the spiral spring, wherein upon release of the string, the spiral spring rotates in the first rotational direction for causing rotation of the at least one gear coupled to the spiral spring, wherein displacement of the pump is limited for delivery of a bolus dose corresponding to a pre-determined amount.
25. A portable ambulatory therapeutic fluid delivery device for delivering a therapeutic fluid in bolus doses into a body of a patient, the device comprising:
a counter for displaying a value representative of an amount of therapeutic fluid delivered aeration of the device, the counter comprising a mechanically detachable counter housing configured for attaching and detaching from the at least one housing; and
a cradle securable to the patient's skin, the cradle is configured for releasably receiving the at least one housing enabling connection and disconnection of the at least one housing therefrom;
the at east one housing including:
a pump for delivering one or more bolus doses of the therapeutic fluid from the reservoir to the body of the patient through the cannula, wherein the pump is configured for non-electric operation;
an actuator for transferring manual power provided by the patient for operating the pump; an inflatable air container for causing displacement of the therapeutic fluid from the reservoir; and at least one manually-actuated air injection device for delivering air to the inflatable air container, wherein displacement of the pump is limited for delivery of a bolus dose corresponding to a pre-determined amount.
US12/733,009 2007-08-01 2008-07-31 Device for drug delivery Active 2029-06-19 US8465460B2 (en)
US12/733,009 US8465460B2 (en) 2007-08-01 2008-07-31 Device for drug delivery
US13/919,616 US9408967B2 (en) 2007-08-01 2013-06-17 Device for drug delivery
PCT/IL2008/001058 A-371-Of-International WO2009016637A2 (en) 2007-08-01 2008-07-31 A device for drug delivery
US13/919,616 Continuation US9408967B2 (en) 2007-08-01 2013-06-17 Device for drug delivery
US20100292651A1 US20100292651A1 (en) 2010-11-18
US8465460B2 true US8465460B2 (en) 2013-06-18
US12/733,009 Active 2029-06-19 US8465460B2 (en) 2007-08-01 2008-07-31 Device for drug delivery
US13/919,616 Active 2029-07-28 US9408967B2 (en) 2007-08-01 2013-06-17 Device for drug delivery
US15/198,169 Active 2028-11-21 US10238795B2 (en) 2007-08-01 2016-06-30 Device for drug delivery
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Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:YODFAT, OFER;IDDAN, GAVRIEL J.;GESHEIT, ILLAI;SIGNING DATES FROM 20101007 TO 20101018;REEL/FRAME:025156/0266