US20060282290A1 - Components and Methods For Patient Infusion Device - Google Patents
Components and Methods For Patient Infusion Device Download PDFInfo
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- US20060282290A1 US20060282290A1 US11/467,205 US46720506A US2006282290A1 US 20060282290 A1 US20060282290 A1 US 20060282290A1 US 46720506 A US46720506 A US 46720506A US 2006282290 A1 US2006282290 A1 US 2006282290A1
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- cannula
- housing
- port
- reservoir
- deployment
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
- A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
- A61M5/1454—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons spring-actuated, e.g. by a clockwork
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/14244—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body
- A61M5/14248—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body of the skin patch type
-
- G—PHYSICS
- G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
- G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
- G16H20/00—ICT specially adapted for therapies or health-improving plans, e.g. for handling prescriptions, for steering therapy or for monitoring patient compliance
- G16H20/10—ICT specially adapted for therapies or health-improving plans, e.g. for handling prescriptions, for steering therapy or for monitoring patient compliance relating to drugs or medications, e.g. for ensuring correct administration to patients
- G16H20/17—ICT specially adapted for therapies or health-improving plans, e.g. for handling prescriptions, for steering therapy or for monitoring patient compliance relating to drugs or medications, e.g. for ensuring correct administration to patients delivered via infusion or injection
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/14244—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body
- A61M5/14248—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body of the skin patch type
- A61M2005/14252—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body of the skin patch type with needle insertion means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/158—Needles for infusions; Accessories therefor, e.g. for inserting infusion needles, or for holding them on the body
- A61M2005/1583—Needle extractors
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/158—Needles for infusions; Accessories therefor, e.g. for inserting infusion needles, or for holding them on the body
- A61M2005/1585—Needle inserters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/02—General characteristics of the apparatus characterised by a particular materials
- A61M2205/0266—Shape memory materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/158—Needles for infusions; Accessories therefor, e.g. for inserting infusion needles, or for holding them on the body
Definitions
- the present invention relates generally to medical devices, systems and methods, and more particularly to small, low cost, portable infusion devices and methods that are useable to achieve precise, sophisticated, and programmable flow patterns for the delivery of therapeutic liquids such as insulin to a mammalian patient. Even more particularly, the present invention is directed to various new and improved components and methods for an infusion device.
- a medicine may only be available in a liquid form, or the liquid version may have desirable characteristics that cannot be achieved with solid or pill form. Delivery of liquid medicines may best be accomplished by infusing directly into the cardiovascular system via veins or arteries, into the subcutaneous tissue or directly into organs, tumors, cavities, bones or other site specific locations within the body.
- Ambulatory infusion pumps have been developed for delivering liquid medicaments to a patient. These infusion devices have the ability to offer sophisticated fluid delivery profiles accomplishing bolus requirements, continuous infusion and variable flow rate delivery. These infusion capabilities usually result in better efficacy of the drug and therapy and less toxicity to the patient's system.
- An example of a use of an ambulatory infusion pump is for the delivery of insulin for the treatment of diabetes mellitus. These pumps can deliver insulin on a continuous basal basis as well as a bolus basis as is disclosed in U.S. Pat. No. 4,498,843 to Schneider et al.
- the ambulatory pumps often work with a reservoir to contain the liquid medicine, such as a cartridge, a syringe or an IV bag, and use electromechanical pumping or metering technology to deliver the medication to the patient via tubing from the infusion device to a needle that is inserted transcutaneously, or through the skin of the patient.
- the devices allow control and programming via electromechanical buttons or switches located on the housing of the device, and accessed by the patient or clinician.
- the devices include visual feedback via text or graphic screens, such as liquid crystal displays known as LCD's, and may include alert or warning lights and audio or vibration signals and alarms.
- the device can be worn in a harness or pocket or strapped to the body of the patient.
- the applicant of the present application provided a small, low cost, light-weight, easy-to-use device for delivering liquid medicines to a patient.
- the device which is described in detail in co-pending U.S. application Ser. No. 09/943,992, filed on Aug. 31, 2001, includes an exit port, a dispenser for causing fluid from a reservoir to flow to the exit port, a local processor programmed to cause a flow of fluid to the exit port based on flow instructions from a separate, remote control device, and a wireless receiver connected to the local processor for receiving the flow instructions.
- the device is provided with a housing that is free of user input components, such as a keypad, for providing flow instructions to the local processor. What is still desired, however, are additional new and improved components and methods for devices for delivering fluid to a patient.
- the present invention provides a transcutaneous access tool for use as part of device for delivering fluid, such as insulin for example, to a patient.
- the transcutaneous access tool includes a first cannula moveable along an axis of the transcutaneous access tool, a fixed member including an elongated prong extending parallel with the axis, and a deployment member secured to the first cannula.
- the deployment member is movable along the axis away from the fixed member and includes spaced-apart, resiliently flexible fingers extending parallel with the axis and slidingly received on the prong of the fixed member. The fingers having distal ends that are laterally enlarged with respect to the axis.
- the transcutaneous access tool also includes a second cannula disposed within the lumen of the first cannula, and a retraction member secured to the second cannula and movable along the axis between the fixed member and the deployment member.
- the retraction member includes at least one catch extending laterally inwardly with respect to the axis. The catch catches on the laterally enlarged distal ends of the fingers of the deployment element, and prevents the retraction member from being moved away from the deployment member, when the fingers are laterally held apart by the prong of the fixed member.
- the transcutaneous access tool further includes a deployment spring biasing the deployment member away from the fixed member, and a retraction spring biasing the retraction member away from the deployment member and towards the fixed member.
- the first cannula is flexible and the second cannula is rigid.
- the present invention also provides a fluid delivery device including a housing, a reservoir positioned within the housing, and a transcutaneous access tool positioned within the housing.
- the transcutaneous access tool includes a cannula in fluid communication with the reservoir and linearly moveable along an axis of the transcutaneous access tool through a port in a wall of the housing, a deployment member secured to the cannula and movable along the axis of the transcutaneous access tool against the wall of the housing defining the port, and an annular seal coaxially positioned about the cannula and positioned between the deployment member and the wall of the housing defining the port, so that the seal provides a substantially fluid-tight seal between the deployment member and the wall of the housing when the deployment member is moved against the wall of the housing.
- the seal allows a fluid or gas, such as a sterilization medium, to enter the exit port from outside the housing prior to deployment of the cannula, but seals the housing in a fluid-tight manner upon deployment of the cannula.
- the device also includes an outlet plug removably connected to a distal end of the cannula extending out of the housing, and the port in the wall of the housing comprises an internal exit port and the housing further includes an external exit port for the flexible cannula and a sterilization access port adjacent the external exit port.
- the present invention additionally provides a fluid delivery device including a housing having a port providing communication with an interior of the device, an adhesive layer provided on an exterior surface of the housing surrounding the port of the housing and including resilient flaps normally sealing the port in a substantially fluid-tight manner, and a protective layer removably covering the adhesive layer and including a sterilization access tube extending through the flaps of the adhesive layer and into the housing.
- the sterilization access tube allows a fluid or gas, such as a sterilization medium, to enter the port from outside the housing prior to removal of the protective layer, and the flaps seal the port in a fluid-tight manner after removal of the protective layer.
- the present invention also provides a flow path assembly including a base layer having opposing first and second surfaces.
- the base layer defines a fill chamber outlet port extending through the base layer and between the opposing first and second surfaces, an auxiliary chamber inlet port extending through the base layer and between the opposing first and second surfaces, and a first groove on the second surface of the base layer connecting the fill chamber outlet port to the auxiliary chamber inlet port.
- the base layer also defines an auxiliary chamber outlet port extending through the base layer and between the opposing first and second surfaces, a reservoir inlet port extending through the base layer and between the opposing first and second surfaces, and a second groove on the second surface of the base layer connecting the auxiliary chamber outlet port to the reservoir inlet port.
- the base layer further defines a reservoir outlet port extending through the base layer and between the opposing first and second surfaces, a cannula inlet port extending through the base layer and between the opposing first and second surfaces, and a third groove on the second surface of the base layer connecting the reservoir outlet port to the cannula inlet port.
- the flow path assembly also includes a cover layer substantially covering the second surface of the base layer in a substantially fluid-tight manner.
- the base layer is relatively rigid and the cover layer is relatively flexible.
- the flow path assembly includes a cannula connector member secured to the first surface of the base layer in a substantially fluid-tight manner and defining a cannula connector chamber in fluid communication with the cannula inlet port of the base layer.
- the flow path assembly includes a fill port member secured to the first surface of the base layer in a substantially fluid-tight manner and defining a fill port chamber in fluid communication with the fill chamber outlet port of the base layer.
- the first surface of the base layer defines an auxiliary recess connecting the auxiliary chamber inlet port and the auxiliary chamber outlet port.
- the assembly includes a sensor assembly secured to the auxiliary chamber recess of the first surface of the base layer in a substantially fluid-tight manner, and the sensor assembly has a sensor chamber in fluid communication with the auxiliary chamber inlet port and the auxiliary chamber outlet port of the base layer.
- the first surface of the base layer defines a reservoir shelf connecting the reservoir inlet port and the reservoir outlet port.
- the assembly further includes a reservoir secured to the reservoir shelf of the first surface of the base layer in a substantially fluid-tight manner and the reservoir has a reservoir chamber in fluid communication with the reservoir inlet port and the reservoir outlet port.
- the reservoir includes an end cap closing the open first end of cylindrical side wall in a substantially fluid-tight manner and defining a reservoir port providing fluid communication between the reservoir chamber and the reservoir inlet port and the reservoir outlet port.
- the present invention provides another flow path assembly including a cylindrical side wall having opposing first and second open ends and defining a reservoir chamber, an end cap closing the second open end of the side wall and defining a port providing fluid communication with the reservoir chamber, a plunger received in the reservoir chamber and slidingly moveable along the side wall and between the opposing first and second open ends, and a lead screw extending into the first open end of the side wall and having a distal end secured to the plunger.
- the flow path assembly further includes a base layer having opposing first and second surfaces, a fill chamber outlet port extending through the base layer and between the opposing first and second surfaces, a reservoir inlet port extending through the base layer and between the opposing first and second surfaces, a reservoir outlet port extending through the base layer and between the opposing first and second surfaces, and a cannula inlet port extending through the base layer and between the opposing first and second surfaces.
- the second surface of the base layer defines a first groove connecting the fill chamber outlet port to the reservoir inlet port, and a second groove connecting the reservoir outlet port to the cannula inlet port.
- the first surface of the base layer defines a reservoir recess connecting the reservoir inlet port and the reservoir outlet port and receiving the end cap of the reservoir in a substantially fluid-tight manner.
- the port of the end cap provides fluid communication between the reservoir chamber and the reservoir inlet port and the reservoir outlet port.
- the present invention provides an additional flow path assembly including a first portion and a second portion of a housing of a fluid delivery device assembled together to form an end wall of the housing.
- the end wall includes a fill port, a reservoir connection port, a cannula connection port, and at least one flow path connecting the fill port, the reservoir connection port and the cannula connection port.
- the first portion of the housing includes a first portion of the end wall and the second portion of the housing includes a second portion of the end wall.
- the first and the second portions of the end wall have mating surfaces defining corresponding grooves which together define the flow path of the end wall when the first and the second portions of the housing are assembled together.
- FIG. 1 is a perspective view of a first exemplary embodiment of a fluid delivery device constructed in accordance with the present invention shown secured on a patient, and a remote control device for use with the fluid delivery device (the remote control device being enlarged with respect to the patient and the fluid delivery device for purposes of illustration);
- FIGS. 2 a and 2 b are enlarged top and bottom perspective views, respectively, of the fluid delivery device of FIG. 1 ;
- FIG. 3 is a further enlarged top perspective view of the fluid delivery device of FIG. 1 , shown with a top housing portion removed to reveal interior portions of the fluid delivery device, including an exemplary embodiment of a transcutaneous access tool constructed in accordance with the present invention and an exemplary embodiment of a laminated flow path constructed in accordance with the present invention;
- FIGS. 4 a - 4 c are simplified schematic views of the transcutaneous access tool of the fluid delivery device of FIG. 3 illustrating deployment of a needle of the tool;
- FIG. 5 is a further enlarged end perspective view of the transcutaneous access tool of FIG. 3 showing an exemplary embodiment of an exit port seal constructed in accordance with the present invention for sealing the exit port of the device housing upon deployment of the needle of the deployment of a needle of the tool;
- FIG. 6 is a sectional view of a fluid delivery device including an exemplary embodiment of a exit port seal assembly constructed in accordance with the present invention
- FIG. 7 is an enlarged sectional view of a portion of the exemplary embodiment of the exit port seal assembly contained in circle 7 of FIG. 6 , illustrating how the assembly allows an interior of the device to be sterilized prior to use of the device;
- FIG. 8 is a sectional view of the fluid delivery device of FIG. 6 showing a protective bottom layer of the exit port seal assembly removed;
- FIG. 9 is an enlarged sectional view of a portion of the exemplary embodiment of the exit port seal assembly contained in circle 9 of FIG. 8 , illustrating how the assembly seals the interior of the device upon removal of the protective bottom layer and prior to use of the device;
- FIG. 10 is an enlarged sectional view of an exemplary embodiment of an outlet plug constructed in accordance with the present invention shown positioned within an outlet port of a housing a fluid delivery device, and wherein the housing includes a sterilization access port adjacent the outlet port;
- FIG. 11 is an enlarged end perspective view of a portion of the laminated flow path assembly of the fluid delivery device of FIG. 3 ;
- FIG. 12 is an enlarged sectional view of an exemplary embodiment of a fluid reservoir and a reservoir end wall constructed in accordance with the present invention, and an exemplary embodiment of a plunger and a lead screw constructed in accordance with the present invention and received in the reservoir for forcing fluid towards the end wall;
- FIG. 13 is a first end view of the plunger of FIG. 12 ;
- FIG. 14 is a second end view of a portion of an exemplary embodiment of a laminated flow path constructed in accordance with the present invention for attachment to the end wall of the reservoir of FIG. 12 ;
- FIG. 15 is a sectional view of an exemplary embodiment of a fluid reservoir constructed in accordance with the present invention, and an exemplary embodiment of a device housing including a laminated flow path constructed in accordance with the present invention.
- FIG. 16 is a sectional view taken along line 16 - 16 of FIG. 15 of the device housing showing the laminated flow path connected to the reservoir.
- the fluid delivery device 10 includes exemplary embodiments of a reservoir 12 for receiving and holding fluid to be delivered by the device 10 , a transcutaneous access tool 14 for providing fluid communication between the reservoir 12 and a patient, and a laminated flow path assembly 16 connecting a fill port 18 to the reservoir 12 and the reservoir to the transcutaneous access tool 14 , all constructed in accordance with the present inventions.
- the fluid delivery device 10 can be used for the delivery of fluids to a person or animal.
- the types of liquids that can be delivered by the fluid delivery device 10 include, but are not limited to, insulin, antibiotics, nutritional fluids, total parenteral nutrition or TPN, analgesics, morphine, hormones or hormonal drugs, gene therapy drugs, anticoagulants, analgesics, cardiovascular medications, AZT or chemotherapeutics.
- the types of medical conditions that the fluid delivery device 10 might be used to treat include, but are not limited to, diabetes, cardiovascular disease, pain, chronic pain, cancer, AIDS, neurological diseases, Alzheimer's Disease, ALS, Hepatitis, Parkinson's Disease or spasticity.
- the volume of the reservoir 12 is chosen to best suit the therapeutic application of the fluid delivery device 10 impacted by such factors as available concentrations of medicinal fluids to be delivered, acceptable times between refills or disposal of the fluid delivery device 10 , size constraints and other factors.
- the fluid delivery device 10 also includes a dispenser 20 for causing fluid from the reservoir 12 to flow to the transcutaneous access tool 14 .
- a processor or electronic microcontroller (hereinafter referred to as the “local” processor) 22 is connected to the dispenser 20 , and is programmed to cause a flow of fluid to the transcutaneous access tool 14 based on flow instructions from a separate, remote control device 1000 , an example of which is shown in FIG. 1 .
- a wireless receiver 24 is connected to the local processor 22 for receiving flow instructions from the remote control device 1000 and delivering the flow instructions to the local processor 22 .
- the device 10 also includes a housing 26 containing the flow path assembly 16 , the transcutaneous access tool 14 , the reservoir 12 , the dispenser 20 , the local processor 22 , and the wireless receiver 24 .
- the housing 26 of the fluid delivery device 10 is free of user input components for providing flow instructions to the local processor, such as electromechanical switches or buttons on an outer surface of the housing 26 , or interfaces otherwise accessible to a user to adjust the programmed flow rate through the local processor.
- the lack of user input components allows the size, complexity and costs of the device 10 to be substantially reduced so that the device 10 lends itself to being small and disposable in nature. Examples of such devices are disclosed in co-pending U.S. patent application Ser. No. 09/943,992, filed on Aug. 31, 2001 (Atty. Docket No. INSL-110), and entitled DEVICES, SYSTEMS AND METHODS FOR PATIENT INFUSION, which is assigned to the assignee of the present application and has previously been incorporated herein by reference.
- the fluid delivery device 10 includes the wireless communication element, or receiver 24 , as shown in FIG. 3 , for receiving the user inputs from the separate, remote control device 1000 of FIG. 1 .
- Signals can be sent via a communication element (not shown) of the remote control device 1000 , which can include or be connected to an antenna 1300 , shown in FIG. 1 as being external to the device 1000 .
- the remote control device 1000 has user input components, including an array of electromechanical switches, such as the membrane keypad 1200 shown.
- the remote control device 1000 also includes user output components, including a visual display, such as a liquid crystal display (LCD) 1100 .
- the control device 1000 can be provided with a touch screen for both user input and output.
- the remote control device 1000 has its own processor (hereinafter referred to as the “remote” processor) connected to the membrane keypad 1200 and the LCD 1100 .
- the remote processor receives the user inputs from the membrane keypad 1200 and provides “flow” instructions for transmission to the fluid delivery device 10 , and provides information to the LCD 1100 . Since the remote control device 1000 also includes a visual display 1100 , the fluid delivery device 10 can be void of an information screen, further reducing the size, complexity and costs of the device 10 .
- the communication element 24 of the device 10 preferably receives electronic communication from the remote control device 1000 using radio frequency or other wireless communication standards and protocols.
- the communication element 24 is a two-way communication element, including a receiver and a transmitter, for allowing the fluid delivery device 10 to send information back to the remote control device 1000 .
- the remote control device 1000 also includes an integral communication element comprising a receiver and a transmitter, for allowing the remote control device 1000 to receive the information sent by the fluid delivery device 10 .
- the local processor 22 of the device 10 contains all the computer programs and electronic circuitry needed to allow a user to program the desired flow patterns and adjust the program as necessary.
- Such circuitry can include one or more microprocessors, digital and analog integrated circuits, resistors, capacitors, transistors and other semiconductors and other electronic components known to those skilled in the art.
- the local processor 22 also includes programming, electronic circuitry and memory to properly activate the dispenser 20 at the needed time intervals.
- the device 10 also includes a power supply 28 , such as a battery or capacitor, for supplying power to the local processor 22 .
- the power supply is preferably integrated into the fluid delivery device 10 , but can be provided as replaceable, e.g., a replaceable battery.
- the device 10 can also include sensors or transducers such as a flow condition sensor assembly 30 or dispenser position monitors 32 , for transmitting information to the local processor 22 to indicate how and when to activate the dispenser 20 , or to indicate other parameters determining fluid flow, as well as conditions such as the reservoir being empty or leaking, or the dispensing of too much or too little fluid from the reservoir 12 , etc.
- the device 10 can also be provided with an adhesive layer 34 on the outer surface of the housing 26 for securing the device 10 directly to the skin of a patient, as illustrated in FIG. 1 .
- the adhesive layer 34 is provided on an external “bottom” surface of the housing 26 .
- the adhesive layer 34 is also preferably provided in a continuous ring encircling an external exit port 36 of the housing 26 in order to provide a protective seal around the penetrated patient's skin to prevent the penetrated skin from becoming contaminated when a cannula 38 of the transcutaneous access tool 14 extends through the skin.
- the fill port 18 extend through the bottom surface of the housing 26 to discourage and prevent filling and re-filling of the fluid delivery device 10 when the device 10 is attached to a patient's skin.
- the housing 26 can be made from flexible material, or can be provided with flexible hinged sections that allow the fluid delivery device 10 to flex during patient movement to prevent detachment and aid in patient comfort.
- an outlet plug 40 is secured to the distal end of the cannula 38 of the transcutaneous access tool 14 prior to use of the device 10 .
- the outlet plug 40 has an air removal filter that allows air but not fluid to exit the cannula 38 , and acts as a flow restriction system that operates to substantially prime (i.e., purge of air) the flow path of the fluid delivery device 10 prior to operation of the device 10 , to ensure that a desired volume of fluid is accurately delivered by the device 10 during operation.
- the reservoir 12 is not pressurized, and the dispenser 20 is adapted to control flow from the reservoir 12 by driving or pumping the fluid from the reservoir to the transcutaneous access tool 14 .
- Examples of such “driving or pumping” dispensers are shown in co-pending U.S. patent application Ser. No. 09/955,623, filed on Sep. 19, 2001 (Atty. Docket No. INSL-117), and entitled PLUNGER FOR PATIENT INFUSION DEVICE, which is assigned to the assignee of the present application and incorporated herein by reference.
- Other examples of dispensers are shown in co-pending U.S. patent application Ser. No. 10/128,205, filed on Apr. 23, 2002 (Atty. Docket No.
- the reservoir 12 includes a cylindrical side wall 42 extending towards an outlet 44 connected to the transcutaneous access tool 14 .
- a threaded lead screw 46 is received in the reservoir 12 and extends towards the outlet 44 of the reservoir 12 generally parallel with the side wall 42 of the reservoir 12 , and a plunger 48 is secured to an end of the lead screw 46 .
- the lead screw 46 , the plunger 48 and the reservoir 12 are adapted (e.g., provided with o-rings) such that a fluid-tight seal is formed between the plunger 48 and the lead screw 46 and a fluid-tight seal is formed between the plunger 48 and the side wall of the reservoir 12 , so that movement of the plunger 48 towards the outlet 44 of the reservoir 12 forces fluid through the outlet 44 to the transcutaneous access tool 14 .
- the dispenser 20 causes fluid flow by causing linear movement of the lead screw 46 and the plunger 48 towards the outlet 44 of the reservoir 12 .
- the dispenser 20 includes an elongated shape memory element connected to the local processor 22 and having a changeable length decreasing from an uncharged length to a charged length when at least one charge is applied to the shape memory element.
- the shape memory element is operatively connected to the plunger 48 such that the changeable length of the shape memory element causes the plunger 48 to move along the side wall 42 of the reservoir 12 .
- the dispenser 20 includes a rotatable gear 50 linearly fixed with respect to the reservoir 12 .
- the gear 50 is coaxially fixed to an exterior surface of a slotted tube 52 such that rotation of the gear 50 causes rotation of the slotted tube 52 about a common longitudinal axis “A”.
- the lead screw 46 is coaxially positioned within the slotted tube 52 and includes a radially extending pin 54 slidingly received in longitudinal slots of the slotted tube 52 such that rotation of the slotted tube 52 causes rotation of the lead screw 46 .
- the lead screw 46 is also threadedly engaged with a fixed nut assembly 56 , such that rotation of the gear 50 causes linear movement of the lead screw 46 through the fixed nut assembly 56 and linear movement of the plunger 48 towards the outlet 44 of the reservoir 12 .
- the fixed nut assembly 56 is configured to be disengaged from the lead screw 46 prior to use of the device to allow the lead screw 46 and the plunger 48 to be linearly moved away from an inlet 58 of the reservoir 12 during filling of the reservoir 12 through the fill port 18 .
- the dispenser 20 further includes a ratchet member 60 for engaging radially extending teeth of the gear 50 , wherein the ratchet member 60 and the gear 50 are adapted such that linear movement of the ratchet member 60 in a first direction adjacent the gear 50 causes rotation of the gear 50 , while linear movement of the ratchet member 60 in a second direction adjacent the gear 50 causes no rotation of the gear 50 .
- the elongated shape memory element (not viewable) is connected to the ratchet member 60 such that the changeable length of the shape memory element decreasing from an uncharged length to a charged length causes linear movement of the ratchet member 60 in one of the first and the second directions.
- the dispenser 20 can also include a return element, such as a hinge spring (not viewable), connected to the ratchet member 60 for causing linear movement of the ratchet member 60 in the first direction.
- the reservoir 12 can be pressurized and a dispenser that does not create a driving or pumping force, but rather acts as a metering device, allowing pulses of fluid to pass from the pressurized reservoir 12 , through the dispenser, to the transcutaneous access tool 14 .
- metering Examples of such “metering” dispensers are shown in co-pending U.S. patent application Ser. No. 09/977,434, filed Oct. 12, 2001 (Atty. Docket No.
- the dispenser is controlled by the local processor 22 , which includes electronic programming, controls, and circuitry to allow sophisticated fluid delivery programming and control of the dispenser.
- the exemplary embodiment of the transcutaneous access tool 14 constructed in accordance with the present invention includes the first cannula 38 , which is preferably flexible, and a rigid second cannula 62 disposed within the lumen of the flexible first cannula 38 .
- the transcutaneous access tool 14 also includes a movable deployment member 64 secured to the first cannula 38 , a movable retraction member 66 secured to the second cannula 62 , and a stationary fixed member 68 secured to the housing 26 .
- the transcutaneous access tool 14 further includes a latch 72 that normally maintains the deployment member 64 and the first cannula 38 in a pre-deployment position against the bias force of a compressed helical deployment spring 70 .
- a shape memory element 74 activated upon the application of an electrical charge removes the latch 72 from the travel path of the deployment member 64 , thereby allowing the deployment spring 70 to drive the deployment member 64 and the retraction member 66 away from the fixed member 68 and toward an internal exit port 76 of a wall 78 of the housing 26 , and force the distal tips of both the first cannula 38 and the second cannula 62 through the external exit port 36 and into the skin of the patient.
- FIG. 4 a shows the transcutaneous access tool 14 prior to deployment
- FIG. 4 b shows the transcutaneous access tool 14 after deployment with the deployment member 64 and the retraction member 66 moved fully away from the fixed member 68 by the deployment spring 70 .
- the transcutaneous access tool 14 is in fluid communication with the reservoir 12 of the device 10 at all times before and after injection of the first cannula 38 into the skin of the patient.
- the housing 26 includes a cannula guide portion 80 which deflects the cannula (e.g., by approximately 40°) as the cannula 38 passes between the internal exit port 76 and the external exit port 36 .
- the cannula 38 does not have a bent distal end (e.g., bent approximately 90°).
- a compressed helical retraction spring 82 biases the retraction member 66 away from the deployment member 64 .
- the retraction spring 82 is allowed to force the retraction member 66 away from the deployment member 64 and towards the fixed member 68 , and withdraw the second cannula 62 from the skin of the patient, as shown in FIG. 4 c .
- the deployment member 64 maintains the first cannula 38 in the skin of the patient such that a relatively comfortable flow path is created between the reservoir 12 and the patient.
- the transcutaneous access tool 14 includes an elongated prong 84 extending from the fixed member 68 parallel with an axis “B” of the transcutaneous access tool 14 , spaced-apart, resiliently flexible fingers 86 extending from the deployment member 64 parallel with the axis “B” and slidingly received on the prong 84 of the fixed member 68 , and a catch 88 of the retraction member 66 extending laterally inwardly with respect to the axis “B”.
- the catch 88 catches on laterally enlarged distal ends 90 of the fingers 86 of the deployment member 64 , and prevents the retraction member 66 from being moved away from the deployment member 64 when the fingers 86 are laterally held apart by the prong 84 of the fixed member 68 , as shown in FIGS. 4 a and 4 b.
- the prong 84 and the fingers 86 are sized so that the fingers 86 slide off a distal end of the prong 84 when the deployment member 64 is fully deployed by the deployment spring 70 , as shown in FIG. 4 c .
- the force of the retraction spring 82 causes the catch 88 of the retraction member 66 to force the laterally enlarged distal ends 90 of the fingers 86 laterally together (i.e., squeeze the fingers 86 together) and be released from the laterally enlarged distal ends 90 .
- the retraction spring 82 then forces the retraction member 66 away from the deployment member 64 and towards the fixed member 68 , and withdraws the second cannula 62 from the skin of the patient, as shown in FIG. 4 c.
- the trancutaneous access tool 14 also includes an seal 92 that is moved between the deployment member 64 and the wall 78 of the housing 26 defining the internal exit port 76 upon deployment of the cannula 38 .
- the seal 92 provides a substantially fluid-tight seal between the deployment member 64 and the wall 78 of the housing 26 when the deployment member 64 is moved against the wall 78 , as shown in FIG. 4 c .
- the seal 92 allows a fluid or gas, such as a sterilization medium (e.g., ethylene oxide), to enter the internal exit port 76 from outside the housing 26 prior to deployment of the cannula 38 , but seals the housing 26 in a fluid-tight manner upon deployment of the cannula 38 .
- a sterilization medium e.g., ethylene oxide
- the seal 92 is annular in shape, is coaxially positioned about the first cannula 38 , and is secured to the deployment member 64 .
- the seal 92 is made from a resiliently flexible material such as an elastomer or rubber.
- the seal 92 can also be bonded to an outer surface of the first cannula 38 .
- the housing 26 can further be provided with a sterilization access port 98 adjacent the external exit port 36 .
- the sterilization access port 98 allows a sterilization medium to enter the housing 26 when the outlet plug 40 is blocking the external exit port 36 .
- the outlet plug 40 can be provided with its own sterilization access port, which would be formed in the side collar portion 94 of the outlet plug.
- the exemplary embodiment of the flow path assembly 16 includes a base layer 100 having opposing first and second surfaces 102 , 104 .
- the base layer 100 defines a fill chamber outlet port 106 extending through the base layer 100 and between the opposing first and second surfaces 102 , 104 , an auxiliary chamber inlet port 108 extending through the base layer 100 and between the opposing first and second surfaces 102 , 104 , and a first groove 110 on the second surface 104 of the base layer 100 connecting the fill chamber outlet port 106 to the auxiliary chamber inlet port 108 .
- the base layer 100 also defines an auxiliary chamber outlet port 112 extending through the base layer 100 and between the opposing first and second surfaces, the reservoir inlet port 58 extending through the base layer 100 and between the opposing first and second surfaces, and a second groove 114 on the second surface 104 of the base layer 100 connecting the auxiliary chamber outlet port 112 to the reservoir inlet port 58 .
- the base layer 100 further defines the reservoir outlet port 44 extending through the base layer 100 and between the opposing first and second surfaces, a cannula inlet port 116 extending through the base layer 100 and between the opposing first and second surfaces, and a third groove 118 on the second surface 104 of the base layer 100 connecting the reservoir outlet port 44 to the cannula inlet port 116 .
- the flow path assembly 16 also includes a cover layer 118 substantially covering the second surface 104 of the base layer 100 in a substantially fluid-tight manner, such that the grooves 110 , 114 , 118 in the second surface 104 of the base layer 100 are formed into fluid passageways.
- the base layer 100 is relatively rigid and the cover layer 118 is relatively flexible.
- the base layer 100 is preferably comprised of a relatively rigid plastic that is formed through injection molding, for example, while the cover layer 118 is made from a relatively flexible fluid-tight plastic, such as an elastomer, rubber or thermoplastic.
- the base layer 100 and the cover layer 118 are secured together in a suitable manner through bonding or by using an adhesive, for example, in order to seal the grooves 110 , 114 , 118 of the base layer 100 in a fluid-tight manner.
- an adhesive for example, in order to seal the grooves 110 , 114 , 118 of the base layer 100 in a fluid-tight manner.
- the laminated construction of the flow path assembly 16 simplifies manufacturing (and thus the cost) of the resulting fluid delivery device 10 .
- the flow path assembly 16 also includes a cannula connector member 120 secured to the first surface 102 of the base layer 100 in a substantially fluid-tight manner and defining a cannula connector chamber (not viewable) in fluid communication with the cannula inlet port 116 of the base layer 100 .
- the connector member 120 includes a needle septum 122 fitted in an opening of the connector chamber.
- the second cannula 62 of the transcutaneous access tool 14 extends through the needle septum 122 to provide fluid communication between the reservoir 12 and the first cannula 38 .
- the connector member 120 is unitarily formed as a single piece with the base layer 100 , by injection molding for example.
- the flow path assembly 16 also includes the fill port 18 secured to the first surface 102 of the base layer 100 in a substantially fluid-tight manner and defining a fill port chamber (not viewable) in fluid communication with the fill chamber outlet port 106 of the base layer 100 .
- the fill port 18 includes a needle septum 124 (as shown in FIG. 2 b ) fitted in an opening of the fill port chamber.
- the fill port 18 is unitarily formed as a single piece with the base layer 100 , by injection molding for example.
- the first surface 102 of the base layer 100 defines an auxiliary recess connecting the auxiliary chamber inlet port 108 and the auxiliary chamber outlet port 112 .
- the flow sensor assembly 30 is secured to the auxiliary recess of the first surface 102 of the base layer 100 in a substantially fluid-tight manner, and the flow sensor assembly 30 has a flow sensor chamber (not viewable) in fluid communication with the auxiliary chamber inlet port 108 and the auxiliary chamber outlet port 112 of the base layer 100 .
- the flow sensor assembly provides an indication of fluid pressure within the flow path assembly 16 , so that conditions within the flow path assembly can be determined. Examples of flow sensor assemblies are shown in co-pending U.S. patent application Ser. No. 10/087,507, filed on Mar.
- auxiliary chamber inlet port 108 and the auxiliary chamber outlet port 112 can be used to attach other types of “auxiliary” sensors or devices to the flow path assembly 16 .
- an auxiliary sensor connected to the auxiliary chamber inlet port 108 and the auxiliary chamber outlet port 112 can be provided to not only detect flow conditions but other parameters such as detection of air, temperature monitoring, drug parameter monitoring (concentration, pH, etc.) and other parameters important to infusion of liquid therapeutics, in addition to flow rate.
- An auxiliary device can include an air removal filter, a fluid sterilization filter, a pressure release valve, and other types of devices as desired.
- the first surface 102 of the base layer 100 defines a reservoir shelf 126 connecting the reservoir 58 inlet port and the reservoir outlet port 44 .
- the reservoir 12 includes the cylindrical side wall 42 having opposing open ends, and one of the open ends is received in a fluid-tight manner on the shelf 126 of the base layer 100 so that a interior chamber of the reservoir 12 is in fluid communication with the reservoir inlet port 58 and the reservoir outlet port 44 of the base layer 100 .
- the side wall 42 of the reservoir 12 can be made of any suitably strong and rigid material that is compatible with the fluid to be held by the reservoir 12 and that can be sterilized.
- the side wall 42 is comprised of stainless steel (in FIG. 3 the side wall 42 is shown as being transparent only for purposes of illustration). It is also contemplated that the side wall 42 can be formed unitarily as a single piece with the base layer 100 , if desired.
- the fluid delivery device 130 includes a housing 132 having a port 134 , an adhesive layer 136 provided on an exterior surface of the housing 132 surrounding the port 134 and including resiliently flexible flaps 138 normally sealing the port 134 in a substantially fluid-tight manner.
- the adhesive layer 136 is for securing the device 130 to a patient during use.
- a protective layer 140 removably covers the adhesive layer 136 and includes a sterilization access tube 142 extending through the flaps 138 of the adhesive layer 136 and into the housing 132 .
- the sterilization access tube 142 allows a fluid or gas, such as a sterilization medium (e.g., ethylene oxide), to enter the port 134 from outside the housing 132 prior to removal of the protective layer 140 .
- the flaps 138 then seal the port 134 in a fluid-tight manner after removal of the protective layer 140 , to reduce the risks of contamination of the fluid delivery device 130 during use.
- FIGS. 6 and 7 shown the device 130 prior to removal of the protective layer 140
- FIGS. 8 and 9 show the device 130 after removal of the protective layer 140 .
- the port 134 may also be used for passage of a deployable cannula or other transcutaneous access tool (not shown), or may be provided just to allow access of a sterilization medium through the sterilization access tube 142 prior to use.
- the reservoir 150 includes a cylindrical side wall 152 having opposing first and second open ends 154 , 156 and defining a reservoir chamber, an end cap 158 closing the second open end 156 of the side wall 152 and defining a port 160 providing fluid communication with the reservoir chamber, a plunger 162 received in the reservoir chamber and slidingly moveable along the side wall 152 and between the opposing first and second open ends 154 , 156 , and a lead screw 164 extending into the first open end 154 of the side wall 152 and having a distal end secured to the plunger 162 .
- a resiliently flexible o-ring 166 is provided in a circumferential groove of the plunger 162 to maintain a fluid-tight seal between the plunger 162 and the side wall 152 of the reservoir 150 .
- the distal end of the lead screw 164 is preferably rotatably secured within a socket 168 of the plunger 162 so that the lead screw 164 can be rotated independently of the plunger 162 .
- the distal end of the lead screw 164 is preferably snap-fit into the socket 168 for ease of assembly.
- the end cap 158 is made of a suitably rigid and strong material that is compliant with the fluid to be held in the reservoir 150 and that can be easily sterilized, such as stainless steel. The end cap 158 can be secured to the side wall 152 by welding for example.
- An exemplary embodiment of a flow path assembly constructed in accordance with the present invention includes the reservoir 150 of FIGS. 12 and 13 assembled to a base layer 170 of FIG. 14 .
- the base layer 170 has opposing first and second surfaces 172 (only the second surface is viewable in FIG. 14 ), a fill chamber outlet port 174 extending through the base layer 170 and between the opposing first and second surfaces, a reservoir inlet port 176 extending through the base layer 170 and between the opposing first and second surfaces, a reservoir outlet port 178 extending through the base layer 170 and between the opposing first and second surfaces, and a cannula inlet port 180 extending through the base layer 170 and between the opposing first and second surfaces.
- the second surface 172 of the base layer 170 defines a first groove 182 connecting the fill chamber outlet port 174 to the reservoir inlet port 176 , and a second groove 184 connecting the reservoir outlet port 178 to the cannula inlet port 180 .
- the first surface of the base layer 170 defines a reservoir recess 186 connecting the reservoir inlet port 176 and the reservoir outlet port 178 and for receiving the end cap 158 of the reservoir 150 of FIG. 12 in a substantially fluid-tight manner.
- the port 160 of the end cap 158 provides fluid communication between the reservoir 150 and the reservoir inlet port 176 and the reservoir outlet port 178 .
- the end cap 158 of the reservoir 150 is snap-fit into the reservoir recess 186 of the base layer 170 .
- the first surface of the base layer 170 also defines a fill port recess 188 over the fill chamber outlet port 174 and a cannula connector recess 190 over the cannula inlet port 180 .
- the base layer 170 is made of a suitable strong and rigid material, such as injection molded plastic or stainless steel.
- the flow path assembly further includes a cover layer secure over the second surface 172 of the base layer 170 in a fluid-tight manner such that the grooves 182 , 184 are formed into fluid passageways.
- the mating construction of the reservoir 150 and the base layer 170 of FIGS. 12 through 14 simplifies assembly (and thus the cost) of the resulting fluid delivery device.
- FIGS. 15 and 16 an additional flow path assembly 200 constructed in accordance with the present invention is shown.
- the flow path assembly 200 of FIGS. 15 and 16 is unitarily formed as part of an end wall 202 of a housing 204 of a fluid delivery device.
- the flow path assembly 200 of FIGS. 15 and 16 simplifies assembly (and thus the cost) of the fluid delivery device by incorporating the flow path into the end wall 202 of the housing 204 , which can be two injection molded pieces 206 , 208 assembly together.
- the flow path assembly 200 includes a first portion 206 and a second portion 208 of the housing 204 assembled together to form the end wall 202 of the housing.
- the end wall 202 includes a fill port 210 , a reservoir connection port 212 , a cannula connection port 214 , and at least one flow path 216 connecting the fill port, the reservoir connection port and the cannula connection port.
- the first portion 206 of the housing 204 includes a first portion of the end wall 202 and the second portion 208 of the housing 204 includes a second portion of the end wall 202 .
- the first and the second portions of the end wall 202 have mating surfaces defining corresponding grooves which together define the flow path 216 of the end wall when the first and the second portions 206 , 208 of the housing 204 are assembled together.
- the end wall 202 of the housing 204 further includes an interior surface defining a reservoir recess 218 in fluid communication with the reservoir connection port 212 , and a reservoir side wall 220 is received in the recess 218 .
- a circumferential o-ring groove is provided in the reservoir recess 218 , and a resiliently flexible o-ring 222 is positioned in the groove to provide a fluid-tight seal between the side wall 220 of the reservoir and the end wall 202 of the housing 204 .
- the fill port 210 extends between the mating surface of the second portion of the end wall 202 and an exterior surface of the second portion 208 of the housing 204 , and contains a needle septum 224 .
- the present invention generally provides new and improved components for a device for delivering fluid, such as insulin for example, to a patient.
- fluid such as insulin for example
- the embodiments described herein are merely exemplary and that a person skilled in the art may make variations and modifications to the embodiments described without departing from the spirit and scope of the present invention. All such equivalent variations and modifications are intended to be included within the scope of this invention as defined by the appended claims.
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Abstract
Description
- The present application is a divisional of U.S. patent application Ser. No. 10/260,192, which is related to U.S. Pat. No. 6,740,059 entitled DEVICES, SYSTEMS AND METHODS FOR PATIENT INFUSION, which is assigned to the assignee of the present application and incorporated herein by reference.
- The present invention relates generally to medical devices, systems and methods, and more particularly to small, low cost, portable infusion devices and methods that are useable to achieve precise, sophisticated, and programmable flow patterns for the delivery of therapeutic liquids such as insulin to a mammalian patient. Even more particularly, the present invention is directed to various new and improved components and methods for an infusion device.
- Today, there are numerous diseases and other physical ailments that are treated by various medicines including pharmaceuticals, nutritional formulas, biologically derived or active agents, hormonal and gene based material and other substances in both solid or liquid form. In the delivery of these medicines, it is often desirable to bypass the digestive system of a mammalian patient to avoid degradation of the active ingredients caused by the catalytic enzymes in the digestive tract and liver. Delivery of a medicine other than by way of the intestines is known as parenteral delivery. Parenteral delivery of various drugs in liquid form is often desired to enhance the effect of the substance being delivered, insuring that the unaltered medicine reaches its intended site at a significant concentration. Also, undesired side effects associated with other routes of delivery, such as systemic toxicity, can potentially be avoided.
- Often, a medicine may only be available in a liquid form, or the liquid version may have desirable characteristics that cannot be achieved with solid or pill form. Delivery of liquid medicines may best be accomplished by infusing directly into the cardiovascular system via veins or arteries, into the subcutaneous tissue or directly into organs, tumors, cavities, bones or other site specific locations within the body.
- Parenteral delivery of liquid medicines into the body is often accomplished by administering bolus injections using a needle and reservoir, or continuously by gravity driven dispensers or transdermal patch technologies. Bolus injections often imperfectly match the clinical needs of the patient, and usually require larger individual doses than are desired at the specific time they are given. Continuous delivery of medicine through gravity feed systems compromise the patient's mobility and lifestyle, and limit the therapy to simplistic flow rates and profiles. Transdermal patches have special requirements of the medicine being delivered, particularly as it relates to the molecular structure, and similar to gravity feed systems, the control of the drug administration is severely limited.
- Ambulatory infusion pumps have been developed for delivering liquid medicaments to a patient. These infusion devices have the ability to offer sophisticated fluid delivery profiles accomplishing bolus requirements, continuous infusion and variable flow rate delivery. These infusion capabilities usually result in better efficacy of the drug and therapy and less toxicity to the patient's system. An example of a use of an ambulatory infusion pump is for the delivery of insulin for the treatment of diabetes mellitus. These pumps can deliver insulin on a continuous basal basis as well as a bolus basis as is disclosed in U.S. Pat. No. 4,498,843 to Schneider et al.
- The ambulatory pumps often work with a reservoir to contain the liquid medicine, such as a cartridge, a syringe or an IV bag, and use electromechanical pumping or metering technology to deliver the medication to the patient via tubing from the infusion device to a needle that is inserted transcutaneously, or through the skin of the patient. The devices allow control and programming via electromechanical buttons or switches located on the housing of the device, and accessed by the patient or clinician. The devices include visual feedback via text or graphic screens, such as liquid crystal displays known as LCD's, and may include alert or warning lights and audio or vibration signals and alarms. The device can be worn in a harness or pocket or strapped to the body of the patient.
- Currently available ambulatory infusion devices are expensive, difficult to program and prepare for infusion, and tend to be bulky, heavy and very fragile. Filling these devices can be difficult and require the patient to carry both the intended medication as well as filling accessories. The devices require specialized care, maintenance, and cleaning to assure proper functionality and safety for their intended long term use. Due to the high cost of existing devices, healthcare providers limit the patient populations approved to use the devices and therapies for which the devices can be used.
- Clearly, therefore, there was a need for a programmable and adjustable infusion system that is precise and reliable and can offer clinicians and patients a small, low cost, light-weight, easy-to-use alternative for parenteral delivery of liquid medicines.
- In response, the applicant of the present application provided a small, low cost, light-weight, easy-to-use device for delivering liquid medicines to a patient. The device, which is described in detail in co-pending U.S. application Ser. No. 09/943,992, filed on Aug. 31, 2001, includes an exit port, a dispenser for causing fluid from a reservoir to flow to the exit port, a local processor programmed to cause a flow of fluid to the exit port based on flow instructions from a separate, remote control device, and a wireless receiver connected to the local processor for receiving the flow instructions. To reduce the size, complexity and costs of the device, the device is provided with a housing that is free of user input components, such as a keypad, for providing flow instructions to the local processor. What is still desired, however, are additional new and improved components and methods for devices for delivering fluid to a patient.
- The present invention provides a transcutaneous access tool for use as part of device for delivering fluid, such as insulin for example, to a patient. The transcutaneous access tool includes a first cannula moveable along an axis of the transcutaneous access tool, a fixed member including an elongated prong extending parallel with the axis, and a deployment member secured to the first cannula. The deployment member is movable along the axis away from the fixed member and includes spaced-apart, resiliently flexible fingers extending parallel with the axis and slidingly received on the prong of the fixed member. The fingers having distal ends that are laterally enlarged with respect to the axis.
- The transcutaneous access tool also includes a second cannula disposed within the lumen of the first cannula, and a retraction member secured to the second cannula and movable along the axis between the fixed member and the deployment member. The retraction member includes at least one catch extending laterally inwardly with respect to the axis. The catch catches on the laterally enlarged distal ends of the fingers of the deployment element, and prevents the retraction member from being moved away from the deployment member, when the fingers are laterally held apart by the prong of the fixed member.
- According to one aspect of the present invention, the transcutaneous access tool further includes a deployment spring biasing the deployment member away from the fixed member, and a retraction spring biasing the retraction member away from the deployment member and towards the fixed member. According to another aspect, the first cannula is flexible and the second cannula is rigid.
- The present invention also provides a fluid delivery device including a housing, a reservoir positioned within the housing, and a transcutaneous access tool positioned within the housing. The transcutaneous access tool includes a cannula in fluid communication with the reservoir and linearly moveable along an axis of the transcutaneous access tool through a port in a wall of the housing, a deployment member secured to the cannula and movable along the axis of the transcutaneous access tool against the wall of the housing defining the port, and an annular seal coaxially positioned about the cannula and positioned between the deployment member and the wall of the housing defining the port, so that the seal provides a substantially fluid-tight seal between the deployment member and the wall of the housing when the deployment member is moved against the wall of the housing. The seal allows a fluid or gas, such as a sterilization medium, to enter the exit port from outside the housing prior to deployment of the cannula, but seals the housing in a fluid-tight manner upon deployment of the cannula.
- According to one aspect of the present invention, the device also includes an outlet plug removably connected to a distal end of the cannula extending out of the housing, and the port in the wall of the housing comprises an internal exit port and the housing further includes an external exit port for the flexible cannula and a sterilization access port adjacent the external exit port.
- The present invention additionally provides a fluid delivery device including a housing having a port providing communication with an interior of the device, an adhesive layer provided on an exterior surface of the housing surrounding the port of the housing and including resilient flaps normally sealing the port in a substantially fluid-tight manner, and a protective layer removably covering the adhesive layer and including a sterilization access tube extending through the flaps of the adhesive layer and into the housing. The sterilization access tube allows a fluid or gas, such as a sterilization medium, to enter the port from outside the housing prior to removal of the protective layer, and the flaps seal the port in a fluid-tight manner after removal of the protective layer.
- The present invention also provides a flow path assembly including a base layer having opposing first and second surfaces. The base layer defines a fill chamber outlet port extending through the base layer and between the opposing first and second surfaces, an auxiliary chamber inlet port extending through the base layer and between the opposing first and second surfaces, and a first groove on the second surface of the base layer connecting the fill chamber outlet port to the auxiliary chamber inlet port. The base layer also defines an auxiliary chamber outlet port extending through the base layer and between the opposing first and second surfaces, a reservoir inlet port extending through the base layer and between the opposing first and second surfaces, and a second groove on the second surface of the base layer connecting the auxiliary chamber outlet port to the reservoir inlet port. The base layer further defines a reservoir outlet port extending through the base layer and between the opposing first and second surfaces, a cannula inlet port extending through the base layer and between the opposing first and second surfaces, and a third groove on the second surface of the base layer connecting the reservoir outlet port to the cannula inlet port. The flow path assembly also includes a cover layer substantially covering the second surface of the base layer in a substantially fluid-tight manner.
- According to one aspect of the present invention, the base layer is relatively rigid and the cover layer is relatively flexible. According to another aspect, the flow path assembly includes a cannula connector member secured to the first surface of the base layer in a substantially fluid-tight manner and defining a cannula connector chamber in fluid communication with the cannula inlet port of the base layer. According to an additional aspect, the flow path assembly includes a fill port member secured to the first surface of the base layer in a substantially fluid-tight manner and defining a fill port chamber in fluid communication with the fill chamber outlet port of the base layer.
- According to another aspect of the present invention, the first surface of the base layer defines an auxiliary recess connecting the auxiliary chamber inlet port and the auxiliary chamber outlet port. According to a further aspect, the assembly includes a sensor assembly secured to the auxiliary chamber recess of the first surface of the base layer in a substantially fluid-tight manner, and the sensor assembly has a sensor chamber in fluid communication with the auxiliary chamber inlet port and the auxiliary chamber outlet port of the base layer.
- According to an additional aspect, the first surface of the base layer defines a reservoir shelf connecting the reservoir inlet port and the reservoir outlet port. According to another aspect, the assembly further includes a reservoir secured to the reservoir shelf of the first surface of the base layer in a substantially fluid-tight manner and the reservoir has a reservoir chamber in fluid communication with the reservoir inlet port and the reservoir outlet port. According to yet another aspect, the reservoir includes an end cap closing the open first end of cylindrical side wall in a substantially fluid-tight manner and defining a reservoir port providing fluid communication between the reservoir chamber and the reservoir inlet port and the reservoir outlet port.
- The present invention provides another flow path assembly including a cylindrical side wall having opposing first and second open ends and defining a reservoir chamber, an end cap closing the second open end of the side wall and defining a port providing fluid communication with the reservoir chamber, a plunger received in the reservoir chamber and slidingly moveable along the side wall and between the opposing first and second open ends, and a lead screw extending into the first open end of the side wall and having a distal end secured to the plunger.
- According to one aspect of the present invention, the flow path assembly further includes a base layer having opposing first and second surfaces, a fill chamber outlet port extending through the base layer and between the opposing first and second surfaces, a reservoir inlet port extending through the base layer and between the opposing first and second surfaces, a reservoir outlet port extending through the base layer and between the opposing first and second surfaces, and a cannula inlet port extending through the base layer and between the opposing first and second surfaces. The second surface of the base layer defines a first groove connecting the fill chamber outlet port to the reservoir inlet port, and a second groove connecting the reservoir outlet port to the cannula inlet port. The first surface of the base layer defines a reservoir recess connecting the reservoir inlet port and the reservoir outlet port and receiving the end cap of the reservoir in a substantially fluid-tight manner. The port of the end cap provides fluid communication between the reservoir chamber and the reservoir inlet port and the reservoir outlet port.
- The present invention provides an additional flow path assembly including a first portion and a second portion of a housing of a fluid delivery device assembled together to form an end wall of the housing. The end wall includes a fill port, a reservoir connection port, a cannula connection port, and at least one flow path connecting the fill port, the reservoir connection port and the cannula connection port.
- According to one aspect of the present invention, the first portion of the housing includes a first portion of the end wall and the second portion of the housing includes a second portion of the end wall. The first and the second portions of the end wall have mating surfaces defining corresponding grooves which together define the flow path of the end wall when the first and the second portions of the housing are assembled together.
- These aspects of the invention together with additional features and advantages thereof may best be understood by reference to the following detailed descriptions and examples taken in connection with the accompanying illustrated drawings.
-
FIG. 1 is a perspective view of a first exemplary embodiment of a fluid delivery device constructed in accordance with the present invention shown secured on a patient, and a remote control device for use with the fluid delivery device (the remote control device being enlarged with respect to the patient and the fluid delivery device for purposes of illustration); -
FIGS. 2 a and 2 b are enlarged top and bottom perspective views, respectively, of the fluid delivery device ofFIG. 1 ; -
FIG. 3 is a further enlarged top perspective view of the fluid delivery device ofFIG. 1 , shown with a top housing portion removed to reveal interior portions of the fluid delivery device, including an exemplary embodiment of a transcutaneous access tool constructed in accordance with the present invention and an exemplary embodiment of a laminated flow path constructed in accordance with the present invention; -
FIGS. 4 a-4 c are simplified schematic views of the transcutaneous access tool of the fluid delivery device ofFIG. 3 illustrating deployment of a needle of the tool; -
FIG. 5 is a further enlarged end perspective view of the transcutaneous access tool ofFIG. 3 showing an exemplary embodiment of an exit port seal constructed in accordance with the present invention for sealing the exit port of the device housing upon deployment of the needle of the deployment of a needle of the tool; -
FIG. 6 is a sectional view of a fluid delivery device including an exemplary embodiment of a exit port seal assembly constructed in accordance with the present invention; -
FIG. 7 is an enlarged sectional view of a portion of the exemplary embodiment of the exit port seal assembly contained incircle 7 ofFIG. 6 , illustrating how the assembly allows an interior of the device to be sterilized prior to use of the device; -
FIG. 8 is a sectional view of the fluid delivery device ofFIG. 6 showing a protective bottom layer of the exit port seal assembly removed; -
FIG. 9 is an enlarged sectional view of a portion of the exemplary embodiment of the exit port seal assembly contained incircle 9 ofFIG. 8 , illustrating how the assembly seals the interior of the device upon removal of the protective bottom layer and prior to use of the device; -
FIG. 10 is an enlarged sectional view of an exemplary embodiment of an outlet plug constructed in accordance with the present invention shown positioned within an outlet port of a housing a fluid delivery device, and wherein the housing includes a sterilization access port adjacent the outlet port; -
FIG. 11 is an enlarged end perspective view of a portion of the laminated flow path assembly of the fluid delivery device ofFIG. 3 ; -
FIG. 12 is an enlarged sectional view of an exemplary embodiment of a fluid reservoir and a reservoir end wall constructed in accordance with the present invention, and an exemplary embodiment of a plunger and a lead screw constructed in accordance with the present invention and received in the reservoir for forcing fluid towards the end wall; -
FIG. 13 is a first end view of the plunger ofFIG. 12 ; -
FIG. 14 is a second end view of a portion of an exemplary embodiment of a laminated flow path constructed in accordance with the present invention for attachment to the end wall of the reservoir ofFIG. 12 ; -
FIG. 15 is a sectional view of an exemplary embodiment of a fluid reservoir constructed in accordance with the present invention, and an exemplary embodiment of a device housing including a laminated flow path constructed in accordance with the present invention; and -
FIG. 16 is a sectional view taken along line 16-16 ofFIG. 15 of the device housing showing the laminated flow path connected to the reservoir. - Like reference characters designate identical or corresponding components and units throughout the several views.
- Referring to
FIGS. 1 through 3 , there is illustrated an exemplary embodiment of afluid delivery device 10 constructed in accordance with the present inventions. Referring toFIG. 3 , thefluid delivery device 10 includes exemplary embodiments of areservoir 12 for receiving and holding fluid to be delivered by thedevice 10, atranscutaneous access tool 14 for providing fluid communication between thereservoir 12 and a patient, and a laminatedflow path assembly 16 connecting afill port 18 to thereservoir 12 and the reservoir to thetranscutaneous access tool 14, all constructed in accordance with the present inventions. - The
fluid delivery device 10 can be used for the delivery of fluids to a person or animal. The types of liquids that can be delivered by thefluid delivery device 10 include, but are not limited to, insulin, antibiotics, nutritional fluids, total parenteral nutrition or TPN, analgesics, morphine, hormones or hormonal drugs, gene therapy drugs, anticoagulants, analgesics, cardiovascular medications, AZT or chemotherapeutics. The types of medical conditions that thefluid delivery device 10 might be used to treat include, but are not limited to, diabetes, cardiovascular disease, pain, chronic pain, cancer, AIDS, neurological diseases, Alzheimer's Disease, ALS, Hepatitis, Parkinson's Disease or spasticity. The volume of thereservoir 12 is chosen to best suit the therapeutic application of thefluid delivery device 10 impacted by such factors as available concentrations of medicinal fluids to be delivered, acceptable times between refills or disposal of thefluid delivery device 10, size constraints and other factors. - The
fluid delivery device 10 also includes adispenser 20 for causing fluid from thereservoir 12 to flow to thetranscutaneous access tool 14. A processor or electronic microcontroller (hereinafter referred to as the “local” processor) 22 is connected to thedispenser 20, and is programmed to cause a flow of fluid to thetranscutaneous access tool 14 based on flow instructions from a separate,remote control device 1000, an example of which is shown inFIG. 1 . Awireless receiver 24 is connected to thelocal processor 22 for receiving flow instructions from theremote control device 1000 and delivering the flow instructions to thelocal processor 22. Thedevice 10 also includes ahousing 26 containing theflow path assembly 16, thetranscutaneous access tool 14, thereservoir 12, thedispenser 20, thelocal processor 22, and thewireless receiver 24. - As shown best in
FIGS. 2 a and 2 b, thehousing 26 of thefluid delivery device 10 is free of user input components for providing flow instructions to the local processor, such as electromechanical switches or buttons on an outer surface of thehousing 26, or interfaces otherwise accessible to a user to adjust the programmed flow rate through the local processor. The lack of user input components allows the size, complexity and costs of thedevice 10 to be substantially reduced so that thedevice 10 lends itself to being small and disposable in nature. Examples of such devices are disclosed in co-pending U.S. patent application Ser. No. 09/943,992, filed on Aug. 31, 2001 (Atty. Docket No. INSL-110), and entitled DEVICES, SYSTEMS AND METHODS FOR PATIENT INFUSION, which is assigned to the assignee of the present application and has previously been incorporated herein by reference. - In order to program, adjust the programming of, or otherwise communicate user inputs to the local processor, the
fluid delivery device 10 includes the wireless communication element, orreceiver 24, as shown inFIG. 3 , for receiving the user inputs from the separate,remote control device 1000 ofFIG. 1 . Signals can be sent via a communication element (not shown) of theremote control device 1000, which can include or be connected to anantenna 1300, shown inFIG. 1 as being external to thedevice 1000. - The
remote control device 1000 has user input components, including an array of electromechanical switches, such as themembrane keypad 1200 shown. Theremote control device 1000 also includes user output components, including a visual display, such as a liquid crystal display (LCD) 1100. Alternatively, thecontrol device 1000 can be provided with a touch screen for both user input and output. Although not shown inFIG. 1 , theremote control device 1000 has its own processor (hereinafter referred to as the “remote” processor) connected to themembrane keypad 1200 and theLCD 1100. The remote processor receives the user inputs from themembrane keypad 1200 and provides “flow” instructions for transmission to thefluid delivery device 10, and provides information to theLCD 1100. Since theremote control device 1000 also includes avisual display 1100, thefluid delivery device 10 can be void of an information screen, further reducing the size, complexity and costs of thedevice 10. - The
communication element 24 of thedevice 10 preferably receives electronic communication from theremote control device 1000 using radio frequency or other wireless communication standards and protocols. In a preferred embodiment, thecommunication element 24 is a two-way communication element, including a receiver and a transmitter, for allowing thefluid delivery device 10 to send information back to theremote control device 1000. In such an embodiment, theremote control device 1000 also includes an integral communication element comprising a receiver and a transmitter, for allowing theremote control device 1000 to receive the information sent by thefluid delivery device 10. - The
local processor 22 of thedevice 10 contains all the computer programs and electronic circuitry needed to allow a user to program the desired flow patterns and adjust the program as necessary. Such circuitry can include one or more microprocessors, digital and analog integrated circuits, resistors, capacitors, transistors and other semiconductors and other electronic components known to those skilled in the art. Thelocal processor 22 also includes programming, electronic circuitry and memory to properly activate thedispenser 20 at the needed time intervals. - In the exemplary embodiment of
FIG. 3 , thedevice 10 also includes apower supply 28, such as a battery or capacitor, for supplying power to thelocal processor 22. The power supply is preferably integrated into thefluid delivery device 10, but can be provided as replaceable, e.g., a replaceable battery. Thedevice 10 can also include sensors or transducers such as a flowcondition sensor assembly 30 or dispenser position monitors 32, for transmitting information to thelocal processor 22 to indicate how and when to activate thedispenser 20, or to indicate other parameters determining fluid flow, as well as conditions such as the reservoir being empty or leaking, or the dispensing of too much or too little fluid from thereservoir 12, etc. - As shown in
FIG. 2 b, thedevice 10 can also be provided with anadhesive layer 34 on the outer surface of thehousing 26 for securing thedevice 10 directly to the skin of a patient, as illustrated inFIG. 1 . Theadhesive layer 34 is provided on an external “bottom” surface of thehousing 26. Theadhesive layer 34 is also preferably provided in a continuous ring encircling anexternal exit port 36 of thehousing 26 in order to provide a protective seal around the penetrated patient's skin to prevent the penetrated skin from becoming contaminated when acannula 38 of thetranscutaneous access tool 14 extends through the skin. It is preferable that thefill port 18 extend through the bottom surface of thehousing 26 to discourage and prevent filling and re-filling of thefluid delivery device 10 when thedevice 10 is attached to a patient's skin. Thehousing 26 can be made from flexible material, or can be provided with flexible hinged sections that allow thefluid delivery device 10 to flex during patient movement to prevent detachment and aid in patient comfort. - As shown in
FIGS. 2 b and 3, anoutlet plug 40 is secured to the distal end of thecannula 38 of thetranscutaneous access tool 14 prior to use of thedevice 10. Theoutlet plug 40 has an air removal filter that allows air but not fluid to exit thecannula 38, and acts as a flow restriction system that operates to substantially prime (i.e., purge of air) the flow path of thefluid delivery device 10 prior to operation of thedevice 10, to ensure that a desired volume of fluid is accurately delivered by thedevice 10 during operation. - In the exemplary embodiment of
FIG. 3 , thereservoir 12 is not pressurized, and thedispenser 20 is adapted to control flow from thereservoir 12 by driving or pumping the fluid from the reservoir to thetranscutaneous access tool 14. Examples of such “driving or pumping” dispensers are shown in co-pending U.S. patent application Ser. No. 09/955,623, filed on Sep. 19, 2001 (Atty. Docket No. INSL-117), and entitled PLUNGER FOR PATIENT INFUSION DEVICE, which is assigned to the assignee of the present application and incorporated herein by reference. Other examples of dispensers are shown in co-pending U.S. patent application Ser. No. 10/128,205, filed on Apr. 23, 2002 (Atty. Docket No. INSL-122), and entitled DISPENSER FOR PATIENT INFUSION DEVICE, which is assigned to the assignee of the present application and incorporated herein by reference, and co-pending U.S. patent application Ser. No. 10/128,203, filed on Apr. 23, 2002 (Atty. Docket No. INSL-123), and entitled DISPENSER FOR PATIENT INFUSION DEVICE, which is assigned to the assignee of the present application and incorporated herein by reference. Further examples of dispensers are shown in co-pending U.S. patent application Ser. No. 10/163,688, filed on Jun. 9, 2002 (Atty. Docket No. INSL-124), and entitled PLUNGER FOR PATIENT INFUSION DEVICE, which is assigned to the assignee of the present application and incorporated herein by reference, and in co-pending U.S. patent application Ser. No. 10/163,690, filed on Jun. 9, 2002 (Atty. Docket No. INSL-125), and entitled PLUNGER FOR PATIENT INFUSION DEVICE, which is also assigned to the assignee of the present application and incorporated herein by reference. - In the embodiment shown in
FIGS. 4 and 5 , thereservoir 12 includes acylindrical side wall 42 extending towards anoutlet 44 connected to thetranscutaneous access tool 14. A threadedlead screw 46 is received in thereservoir 12 and extends towards theoutlet 44 of thereservoir 12 generally parallel with theside wall 42 of thereservoir 12, and aplunger 48 is secured to an end of thelead screw 46. Thelead screw 46, theplunger 48 and thereservoir 12 are adapted (e.g., provided with o-rings) such that a fluid-tight seal is formed between theplunger 48 and thelead screw 46 and a fluid-tight seal is formed between theplunger 48 and the side wall of thereservoir 12, so that movement of theplunger 48 towards theoutlet 44 of thereservoir 12 forces fluid through theoutlet 44 to thetranscutaneous access tool 14. - The
dispenser 20 causes fluid flow by causing linear movement of thelead screw 46 and theplunger 48 towards theoutlet 44 of thereservoir 12. Although not shown inFIG. 3 , thedispenser 20 includes an elongated shape memory element connected to thelocal processor 22 and having a changeable length decreasing from an uncharged length to a charged length when at least one charge is applied to the shape memory element. The shape memory element is operatively connected to theplunger 48 such that the changeable length of the shape memory element causes theplunger 48 to move along theside wall 42 of thereservoir 12. - In the exemplary embodiment shown in
FIG. 3 , thedispenser 20 includes arotatable gear 50 linearly fixed with respect to thereservoir 12. Thegear 50 is coaxially fixed to an exterior surface of a slottedtube 52 such that rotation of thegear 50 causes rotation of the slottedtube 52 about a common longitudinal axis “A”. Thelead screw 46 is coaxially positioned within the slottedtube 52 and includes aradially extending pin 54 slidingly received in longitudinal slots of the slottedtube 52 such that rotation of the slottedtube 52 causes rotation of thelead screw 46. Thelead screw 46 is also threadedly engaged with a fixednut assembly 56, such that rotation of thegear 50 causes linear movement of thelead screw 46 through the fixednut assembly 56 and linear movement of theplunger 48 towards theoutlet 44 of thereservoir 12. In one exemplary embodiment, the fixednut assembly 56 is configured to be disengaged from thelead screw 46 prior to use of the device to allow thelead screw 46 and theplunger 48 to be linearly moved away from aninlet 58 of thereservoir 12 during filling of thereservoir 12 through thefill port 18. - The
dispenser 20 further includes aratchet member 60 for engaging radially extending teeth of thegear 50, wherein theratchet member 60 and thegear 50 are adapted such that linear movement of theratchet member 60 in a first direction adjacent thegear 50 causes rotation of thegear 50, while linear movement of theratchet member 60 in a second direction adjacent thegear 50 causes no rotation of thegear 50. The elongated shape memory element (not viewable) is connected to theratchet member 60 such that the changeable length of the shape memory element decreasing from an uncharged length to a charged length causes linear movement of theratchet member 60 in one of the first and the second directions. Thedispenser 20 can also include a return element, such as a hinge spring (not viewable), connected to theratchet member 60 for causing linear movement of theratchet member 60 in the first direction. - It should be understood, however, that other types of dispensers can also be used with a device incorporating the
reservoir 12, thetranscutaneous access tool 14, or the laminatedflow path assembly 16 of the present inventions. For example, thereservoir 12 can be pressurized and a dispenser that does not create a driving or pumping force, but rather acts as a metering device, allowing pulses of fluid to pass from thepressurized reservoir 12, through the dispenser, to thetranscutaneous access tool 14. Examples of such “metering” dispensers are shown in co-pending U.S. patent application Ser. No. 09/977,434, filed Oct. 12, 2001 (Atty. Docket No. INSL-116), and entitled LAMINATED PATIENT INFUSION DEVICE, which is assigned to the assignee of the present application and incorporated herein by reference. In any event, in the exemplary embodiment shown the dispenser is controlled by thelocal processor 22, which includes electronic programming, controls, and circuitry to allow sophisticated fluid delivery programming and control of the dispenser. - Referring now to
FIGS. 3 through 5 , the exemplary embodiment of thetranscutaneous access tool 14 constructed in accordance with the present invention includes thefirst cannula 38, which is preferably flexible, and a rigidsecond cannula 62 disposed within the lumen of the flexiblefirst cannula 38. Thetranscutaneous access tool 14 also includes amovable deployment member 64 secured to thefirst cannula 38, amovable retraction member 66 secured to thesecond cannula 62, and a stationary fixedmember 68 secured to thehousing 26. - The
transcutaneous access tool 14 further includes alatch 72 that normally maintains thedeployment member 64 and thefirst cannula 38 in a pre-deployment position against the bias force of a compressedhelical deployment spring 70. Ashape memory element 74 activated upon the application of an electrical charge removes thelatch 72 from the travel path of thedeployment member 64, thereby allowing thedeployment spring 70 to drive thedeployment member 64 and theretraction member 66 away from the fixedmember 68 and toward aninternal exit port 76 of awall 78 of thehousing 26, and force the distal tips of both thefirst cannula 38 and thesecond cannula 62 through theexternal exit port 36 and into the skin of the patient.FIG. 4 a shows thetranscutaneous access tool 14 prior to deployment, whileFIG. 4 b shows thetranscutaneous access tool 14 after deployment with thedeployment member 64 and theretraction member 66 moved fully away from the fixedmember 68 by thedeployment spring 70. - The
transcutaneous access tool 14 is in fluid communication with thereservoir 12 of thedevice 10 at all times before and after injection of thefirst cannula 38 into the skin of the patient. Thehousing 26 includes acannula guide portion 80 which deflects the cannula (e.g., by approximately 40°) as thecannula 38 passes between theinternal exit port 76 and theexternal exit port 36. However, thecannula 38 does not have a bent distal end (e.g., bent approximately 90°). - A compressed
helical retraction spring 82 biases theretraction member 66 away from thedeployment member 64. After thesecond cannula 62 has injected the distal tip of thefirst cannula 38 into the skin of the patient, theretraction spring 82 is allowed to force theretraction member 66 away from thedeployment member 64 and towards the fixedmember 68, and withdraw thesecond cannula 62 from the skin of the patient, as shown inFIG. 4 c. Thedeployment member 64, however, maintains thefirst cannula 38 in the skin of the patient such that a relatively comfortable flow path is created between thereservoir 12 and the patient. - In the exemplary embodiment of
FIGS. 3 through 5 , thetranscutaneous access tool 14 includes anelongated prong 84 extending from the fixedmember 68 parallel with an axis “B” of thetranscutaneous access tool 14, spaced-apart, resilientlyflexible fingers 86 extending from thedeployment member 64 parallel with the axis “B” and slidingly received on theprong 84 of the fixedmember 68, and acatch 88 of theretraction member 66 extending laterally inwardly with respect to the axis “B”. Thecatch 88 catches on laterally enlarged distal ends 90 of thefingers 86 of thedeployment member 64, and prevents theretraction member 66 from being moved away from thedeployment member 64 when thefingers 86 are laterally held apart by theprong 84 of the fixedmember 68, as shown inFIGS. 4 a and 4 b. - The
prong 84 and thefingers 86, however, are sized so that thefingers 86 slide off a distal end of theprong 84 when thedeployment member 64 is fully deployed by thedeployment spring 70, as shown inFIG. 4 c. The force of theretraction spring 82 causes thecatch 88 of theretraction member 66 to force the laterally enlarged distal ends 90 of thefingers 86 laterally together (i.e., squeeze thefingers 86 together) and be released from the laterally enlarged distal ends 90. Theretraction spring 82 then forces theretraction member 66 away from thedeployment member 64 and towards the fixedmember 68, and withdraws thesecond cannula 62 from the skin of the patient, as shown inFIG. 4 c. - Referring to
FIGS. 3 through 5 , thetrancutaneous access tool 14 also includes anseal 92 that is moved between thedeployment member 64 and thewall 78 of thehousing 26 defining theinternal exit port 76 upon deployment of thecannula 38. Theseal 92 provides a substantially fluid-tight seal between thedeployment member 64 and thewall 78 of thehousing 26 when thedeployment member 64 is moved against thewall 78, as shown inFIG. 4 c. Theseal 92 allows a fluid or gas, such as a sterilization medium (e.g., ethylene oxide), to enter theinternal exit port 76 from outside thehousing 26 prior to deployment of thecannula 38, but seals thehousing 26 in a fluid-tight manner upon deployment of thecannula 38. - In the exemplary embodiment shown, the
seal 92 is annular in shape, is coaxially positioned about thefirst cannula 38, and is secured to thedeployment member 64. Theseal 92 is made from a resiliently flexible material such as an elastomer or rubber. Theseal 92 can also be bonded to an outer surface of thefirst cannula 38. - Referring to
FIG. 10 , if theoutlet plug 40, which includes aside collar portion 94 and a centralair filter portion 96, is connected to the distal end of thecannula 38 prior to use of thefluid delivery device 10, thehousing 26 can further be provided with asterilization access port 98 adjacent theexternal exit port 36. As its name implies, thesterilization access port 98 allows a sterilization medium to enter thehousing 26 when theoutlet plug 40 is blocking theexternal exit port 36. Alternatively, theoutlet plug 40 can be provided with its own sterilization access port, which would be formed in theside collar portion 94 of the outlet plug. - Referring now to
FIGS. 3 and 11 , the exemplary embodiment of theflow path assembly 16 includes abase layer 100 having opposing first andsecond surfaces base layer 100 defines a fillchamber outlet port 106 extending through thebase layer 100 and between the opposing first andsecond surfaces chamber inlet port 108 extending through thebase layer 100 and between the opposing first andsecond surfaces first groove 110 on thesecond surface 104 of thebase layer 100 connecting the fillchamber outlet port 106 to the auxiliarychamber inlet port 108. Thebase layer 100 also defines an auxiliarychamber outlet port 112 extending through thebase layer 100 and between the opposing first and second surfaces, thereservoir inlet port 58 extending through thebase layer 100 and between the opposing first and second surfaces, and asecond groove 114 on thesecond surface 104 of thebase layer 100 connecting the auxiliarychamber outlet port 112 to thereservoir inlet port 58. Thebase layer 100 further defines thereservoir outlet port 44 extending through thebase layer 100 and between the opposing first and second surfaces, acannula inlet port 116 extending through thebase layer 100 and between the opposing first and second surfaces, and athird groove 118 on thesecond surface 104 of thebase layer 100 connecting thereservoir outlet port 44 to thecannula inlet port 116. - As shown in
FIG. 3 , theflow path assembly 16 also includes acover layer 118 substantially covering thesecond surface 104 of thebase layer 100 in a substantially fluid-tight manner, such that thegrooves second surface 104 of thebase layer 100 are formed into fluid passageways. Preferably, thebase layer 100 is relatively rigid and thecover layer 118 is relatively flexible. Thebase layer 100 is preferably comprised of a relatively rigid plastic that is formed through injection molding, for example, while thecover layer 118 is made from a relatively flexible fluid-tight plastic, such as an elastomer, rubber or thermoplastic. Thebase layer 100 and thecover layer 118 are secured together in a suitable manner through bonding or by using an adhesive, for example, in order to seal thegrooves base layer 100 in a fluid-tight manner. Among other benefits and features, the laminated construction of theflow path assembly 16 simplifies manufacturing (and thus the cost) of the resultingfluid delivery device 10. - Referring to
FIGS. 3 and 11 , theflow path assembly 16 also includes acannula connector member 120 secured to thefirst surface 102 of thebase layer 100 in a substantially fluid-tight manner and defining a cannula connector chamber (not viewable) in fluid communication with thecannula inlet port 116 of thebase layer 100. Theconnector member 120 includes aneedle septum 122 fitted in an opening of the connector chamber. Thesecond cannula 62 of thetranscutaneous access tool 14 extends through theneedle septum 122 to provide fluid communication between thereservoir 12 and thefirst cannula 38. Preferably, theconnector member 120 is unitarily formed as a single piece with thebase layer 100, by injection molding for example. - Still referring to
FIGS. 3 and 11 , theflow path assembly 16 also includes thefill port 18 secured to thefirst surface 102 of thebase layer 100 in a substantially fluid-tight manner and defining a fill port chamber (not viewable) in fluid communication with the fillchamber outlet port 106 of thebase layer 100. Thefill port 18 includes a needle septum 124 (as shown inFIG. 2 b) fitted in an opening of the fill port chamber. Preferably, thefill port 18 is unitarily formed as a single piece with thebase layer 100, by injection molding for example. - Although not viewable, the
first surface 102 of thebase layer 100 defines an auxiliary recess connecting the auxiliarychamber inlet port 108 and the auxiliarychamber outlet port 112. Theflow sensor assembly 30 is secured to the auxiliary recess of thefirst surface 102 of thebase layer 100 in a substantially fluid-tight manner, and theflow sensor assembly 30 has a flow sensor chamber (not viewable) in fluid communication with the auxiliarychamber inlet port 108 and the auxiliarychamber outlet port 112 of thebase layer 100. The flow sensor assembly provides an indication of fluid pressure within theflow path assembly 16, so that conditions within the flow path assembly can be determined. Examples of flow sensor assemblies are shown in co-pending U.S. patent application Ser. No. 10/087,507, filed on Mar. 1, 2002 (Atty. Docket No. INSL-118), and entitled FLOW CONDITION SENSOR ASSEMBLY FOR PATIENT INFUSION DEVICE, which is assigned to the assignee of the present application and incorporated herein by reference. - While the exemplary embodiment of the
flow path assembly 16 ofFIGS. 3 and 11 includes theflow sensor assembly 30 in fluid communication with the auxiliarychamber inlet port 108 and the auxiliarychamber outlet port 112 of thebase layer 100, the auxiliarychamber inlet port 108 and the auxiliarychamber outlet port 112 can be used to attach other types of “auxiliary” sensors or devices to theflow path assembly 16. For example, an auxiliary sensor connected to the auxiliarychamber inlet port 108 and the auxiliarychamber outlet port 112 can be provided to not only detect flow conditions but other parameters such as detection of air, temperature monitoring, drug parameter monitoring (concentration, pH, etc.) and other parameters important to infusion of liquid therapeutics, in addition to flow rate. An auxiliary device can include an air removal filter, a fluid sterilization filter, a pressure release valve, and other types of devices as desired. - Referring to
FIG. 3 , thefirst surface 102 of thebase layer 100 defines areservoir shelf 126 connecting thereservoir 58 inlet port and thereservoir outlet port 44. Thereservoir 12 includes thecylindrical side wall 42 having opposing open ends, and one of the open ends is received in a fluid-tight manner on theshelf 126 of thebase layer 100 so that a interior chamber of thereservoir 12 is in fluid communication with thereservoir inlet port 58 and thereservoir outlet port 44 of thebase layer 100. Theside wall 42 of thereservoir 12 can be made of any suitably strong and rigid material that is compatible with the fluid to be held by thereservoir 12 and that can be sterilized. In one exemplary embodiment, theside wall 42 is comprised of stainless steel (inFIG. 3 theside wall 42 is shown as being transparent only for purposes of illustration). It is also contemplated that theside wall 42 can be formed unitarily as a single piece with thebase layer 100, if desired. - Referring now to
FIGS. 6 through 9 , anotherfluid delivery device 130 constructed in accordance with the present invention is shown. Thefluid delivery device 130 includes ahousing 132 having aport 134, anadhesive layer 136 provided on an exterior surface of thehousing 132 surrounding theport 134 and including resilientlyflexible flaps 138 normally sealing theport 134 in a substantially fluid-tight manner. Theadhesive layer 136 is for securing thedevice 130 to a patient during use. - A
protective layer 140 removably covers theadhesive layer 136 and includes asterilization access tube 142 extending through theflaps 138 of theadhesive layer 136 and into thehousing 132. Among other benefits and features, thesterilization access tube 142 allows a fluid or gas, such as a sterilization medium (e.g., ethylene oxide), to enter theport 134 from outside thehousing 132 prior to removal of theprotective layer 140. Theflaps 138 then seal theport 134 in a fluid-tight manner after removal of theprotective layer 140, to reduce the risks of contamination of thefluid delivery device 130 during use.FIGS. 6 and 7 shown thedevice 130 prior to removal of theprotective layer 140, whileFIGS. 8 and 9 show thedevice 130 after removal of theprotective layer 140. Theport 134 may also be used for passage of a deployable cannula or other transcutaneous access tool (not shown), or may be provided just to allow access of a sterilization medium through thesterilization access tube 142 prior to use. - Referring to
FIG. 12 , another exemplary embodiment of areservoir 150 constructed in accordance with the present invention is shown. Thereservoir 150 includes acylindrical side wall 152 having opposing first and second open ends 154, 156 and defining a reservoir chamber, anend cap 158 closing the secondopen end 156 of theside wall 152 and defining aport 160 providing fluid communication with the reservoir chamber, aplunger 162 received in the reservoir chamber and slidingly moveable along theside wall 152 and between the opposing first and second open ends 154, 156, and alead screw 164 extending into the firstopen end 154 of theside wall 152 and having a distal end secured to theplunger 162. - In the exemplary embodiment of
FIGS. 12 and 13 , a resiliently flexible o-ring 166 is provided in a circumferential groove of theplunger 162 to maintain a fluid-tight seal between theplunger 162 and theside wall 152 of thereservoir 150. The distal end of thelead screw 164 is preferably rotatably secured within asocket 168 of theplunger 162 so that thelead screw 164 can be rotated independently of theplunger 162. In addition, the distal end of thelead screw 164 is preferably snap-fit into thesocket 168 for ease of assembly. Theend cap 158 is made of a suitably rigid and strong material that is compliant with the fluid to be held in thereservoir 150 and that can be easily sterilized, such as stainless steel. Theend cap 158 can be secured to theside wall 152 by welding for example. - An exemplary embodiment of a flow path assembly constructed in accordance with the present invention includes the
reservoir 150 ofFIGS. 12 and 13 assembled to abase layer 170 ofFIG. 14 . Thebase layer 170 has opposing first and second surfaces 172 (only the second surface is viewable inFIG. 14 ), a fillchamber outlet port 174 extending through thebase layer 170 and between the opposing first and second surfaces, areservoir inlet port 176 extending through thebase layer 170 and between the opposing first and second surfaces, areservoir outlet port 178 extending through thebase layer 170 and between the opposing first and second surfaces, and acannula inlet port 180 extending through thebase layer 170 and between the opposing first and second surfaces. Thesecond surface 172 of thebase layer 170 defines afirst groove 182 connecting the fillchamber outlet port 174 to thereservoir inlet port 176, and asecond groove 184 connecting thereservoir outlet port 178 to thecannula inlet port 180. - The first surface of the
base layer 170 defines areservoir recess 186 connecting thereservoir inlet port 176 and thereservoir outlet port 178 and for receiving theend cap 158 of thereservoir 150 ofFIG. 12 in a substantially fluid-tight manner. Theport 160 of theend cap 158 provides fluid communication between thereservoir 150 and thereservoir inlet port 176 and thereservoir outlet port 178. During assembly, theend cap 158 of thereservoir 150 is snap-fit into thereservoir recess 186 of thebase layer 170. - Referring to
FIG. 14 , the first surface of thebase layer 170 also defines afill port recess 188 over the fillchamber outlet port 174 and acannula connector recess 190 over thecannula inlet port 180. Thebase layer 170 is made of a suitable strong and rigid material, such as injection molded plastic or stainless steel. Although not shown, the flow path assembly further includes a cover layer secure over thesecond surface 172 of thebase layer 170 in a fluid-tight manner such that thegrooves reservoir 150 and thebase layer 170 ofFIGS. 12 through 14 simplifies assembly (and thus the cost) of the resulting fluid delivery device. - Referring to
FIGS. 15 and 16 , an additionalflow path assembly 200 constructed in accordance with the present invention is shown. In general, theflow path assembly 200 ofFIGS. 15 and 16 is unitarily formed as part of anend wall 202 of ahousing 204 of a fluid delivery device. Among other benefits and features, theflow path assembly 200 ofFIGS. 15 and 16 simplifies assembly (and thus the cost) of the fluid delivery device by incorporating the flow path into theend wall 202 of thehousing 204, which can be two injection moldedpieces - In the exemplary embodiment shown, the
flow path assembly 200 includes afirst portion 206 and asecond portion 208 of thehousing 204 assembled together to form theend wall 202 of the housing. Theend wall 202 includes afill port 210, areservoir connection port 212, acannula connection port 214, and at least oneflow path 216 connecting the fill port, the reservoir connection port and the cannula connection port. - In the exemplary embodiment shown, the
first portion 206 of thehousing 204 includes a first portion of theend wall 202 and thesecond portion 208 of thehousing 204 includes a second portion of theend wall 202. The first and the second portions of theend wall 202 have mating surfaces defining corresponding grooves which together define theflow path 216 of the end wall when the first and thesecond portions housing 204 are assembled together. - The
end wall 202 of thehousing 204 further includes an interior surface defining areservoir recess 218 in fluid communication with thereservoir connection port 212, and areservoir side wall 220 is received in therecess 218. A circumferential o-ring groove is provided in thereservoir recess 218, and a resiliently flexible o-ring 222 is positioned in the groove to provide a fluid-tight seal between theside wall 220 of the reservoir and theend wall 202 of thehousing 204. Thefill port 210 extends between the mating surface of the second portion of theend wall 202 and an exterior surface of thesecond portion 208 of thehousing 204, and contains aneedle septum 224. - As illustrated by the above described exemplary embodiments, the present invention generally provides new and improved components for a device for delivering fluid, such as insulin for example, to a patient. It should be understood that the embodiments described herein are merely exemplary and that a person skilled in the art may make variations and modifications to the embodiments described without departing from the spirit and scope of the present invention. All such equivalent variations and modifications are intended to be included within the scope of this invention as defined by the appended claims.
Claims (13)
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US11/467,205 US20060282290A1 (en) | 2002-09-30 | 2006-08-25 | Components and Methods For Patient Infusion Device |
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US11/467,205 US20060282290A1 (en) | 2002-09-30 | 2006-08-25 | Components and Methods For Patient Infusion Device |
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US11/467,205 Abandoned US20060282290A1 (en) | 2002-09-30 | 2006-08-25 | Components and Methods For Patient Infusion Device |
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---|---|---|---|---|
US20060253086A1 (en) * | 2005-05-06 | 2006-11-09 | Medtronic Minimed, Inc. | Medical needles for damping motion |
US20090143732A1 (en) * | 2007-11-29 | 2009-06-04 | Insulet Corporation | Interfacing a prefilled syringe with an infusion pump to fill the infusion pump |
US20100008794A1 (en) * | 2002-10-09 | 2010-01-14 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US7722536B2 (en) | 2003-07-15 | 2010-05-25 | Abbott Diabetes Care Inc. | Glucose measuring device integrated into a holster for a personal area network device |
US7727181B2 (en) | 2002-10-09 | 2010-06-01 | Abbott Diabetes Care Inc. | Fluid delivery device with autocalibration |
US7768408B2 (en) | 2005-05-17 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US20110046558A1 (en) * | 2009-08-18 | 2011-02-24 | Peter Gravesen | Medicine delivery device having detachable pressure sensing unit |
US7922458B2 (en) | 2002-10-09 | 2011-04-12 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
US7981034B2 (en) | 2006-02-28 | 2011-07-19 | Abbott Diabetes Care Inc. | Smart messages and alerts for an infusion delivery and management system |
US8016789B2 (en) | 2008-10-10 | 2011-09-13 | Deka Products Limited Partnership | Pump assembly with a removable cover assembly |
US8029460B2 (en) | 2005-03-21 | 2011-10-04 | Abbott Diabetes Care Inc. | Method and system for providing integrated medication infusion and analyte monitoring system |
US8034026B2 (en) | 2001-05-18 | 2011-10-11 | Deka Products Limited Partnership | Infusion pump assembly |
US8047811B2 (en) | 2002-10-09 | 2011-11-01 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
US8066672B2 (en) | 2008-10-10 | 2011-11-29 | Deka Products Limited Partnership | Infusion pump assembly with a backup power supply |
US8085151B2 (en) | 2007-06-28 | 2011-12-27 | Abbott Diabetes Care Inc. | Signal converting cradle for medical condition monitoring and management system |
US8112138B2 (en) | 2005-06-03 | 2012-02-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing rechargeable power in data monitoring and management systems |
US8115635B2 (en) | 2005-02-08 | 2012-02-14 | Abbott Diabetes Care Inc. | RF tag on test strips, test strip vials and boxes |
US8113244B2 (en) | 2006-02-09 | 2012-02-14 | Deka Products Limited Partnership | Adhesive and peripheral systems and methods for medical devices |
US8202267B2 (en) | 2006-10-10 | 2012-06-19 | Medsolve Technologies, Inc. | Method and apparatus for infusing liquid to a body |
US8206296B2 (en) | 2006-08-07 | 2012-06-26 | Abbott Diabetes Care Inc. | Method and system for providing integrated analyte monitoring and infusion system therapy management |
US8223028B2 (en) | 2008-10-10 | 2012-07-17 | Deka Products Limited Partnership | Occlusion detection system and method |
US8262616B2 (en) | 2008-10-10 | 2012-09-11 | Deka Products Limited Partnership | Infusion pump assembly |
US8267892B2 (en) | 2008-10-10 | 2012-09-18 | Deka Products Limited Partnership | Multi-language / multi-processor infusion pump assembly |
US8287495B2 (en) | 2009-07-30 | 2012-10-16 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8344966B2 (en) | 2006-01-31 | 2013-01-01 | Abbott Diabetes Care Inc. | Method and system for providing a fault tolerant display unit in an electronic device |
US8408421B2 (en) | 2008-09-16 | 2013-04-02 | Tandem Diabetes Care, Inc. | Flow regulating stopcocks and related methods |
US8414563B2 (en) | 2007-12-31 | 2013-04-09 | Deka Products Limited Partnership | Pump assembly with switch |
US8430849B2 (en) | 2010-09-24 | 2013-04-30 | Perqflo, Llc | Infusion pumps and plunger pusher position-responsive cartridge lock for infusion pumps |
US8460243B2 (en) | 2003-06-10 | 2013-06-11 | Abbott Diabetes Care Inc. | Glucose measuring module and insulin pump combination |
US8467972B2 (en) | 2009-04-28 | 2013-06-18 | Abbott Diabetes Care Inc. | Closed loop blood glucose control algorithm analysis |
US8496646B2 (en) | 2007-02-09 | 2013-07-30 | Deka Products Limited Partnership | Infusion pump assembly |
US8512246B2 (en) | 2003-04-28 | 2013-08-20 | Abbott Diabetes Care Inc. | Method and apparatus for providing peak detection circuitry for data communication systems |
US8512244B2 (en) | 2006-06-30 | 2013-08-20 | Abbott Diabetes Care Inc. | Integrated analyte sensor and infusion device and methods therefor |
US8547239B2 (en) | 2009-08-18 | 2013-10-01 | Cequr Sa | Methods for detecting failure states in a medicine delivery device |
WO2013149186A1 (en) | 2012-03-30 | 2013-10-03 | Insulet Corporation | Fluid delivery device with transcutaneous access tool, insertion mechansim and blood glucose monitoring for use therewith |
US8560082B2 (en) | 2009-01-30 | 2013-10-15 | Abbott Diabetes Care Inc. | Computerized determination of insulin pump therapy parameters using real time and retrospective data processing |
US8573027B2 (en) | 2009-02-27 | 2013-11-05 | Tandem Diabetes Care, Inc. | Methods and devices for determination of flow reservoir volume |
US8579853B2 (en) | 2006-10-31 | 2013-11-12 | Abbott Diabetes Care Inc. | Infusion devices and methods |
US8638220B2 (en) | 2005-10-31 | 2014-01-28 | Abbott Diabetes Care Inc. | Method and apparatus for providing data communication in data monitoring and management systems |
US8641618B2 (en) | 2007-06-27 | 2014-02-04 | Abbott Diabetes Care Inc. | Method and structure for securing a monitoring device element |
US8650937B2 (en) | 2008-09-19 | 2014-02-18 | Tandem Diabetes Care, Inc. | Solute concentration measurement device and related methods |
US20140088508A1 (en) * | 2012-09-24 | 2014-03-27 | Patrick Ryan | Drug-delivery devices with integrated needle-insertion mechanism |
US8708961B2 (en) | 2008-01-28 | 2014-04-29 | Medsolve Technologies, Inc. | Apparatus for infusing liquid to a body |
US8708376B2 (en) | 2008-10-10 | 2014-04-29 | Deka Products Limited Partnership | Medium connector |
US8795230B2 (en) | 2010-11-30 | 2014-08-05 | Becton, Dickinson And Company | Adjustable height needle infusion device |
US8798934B2 (en) | 2009-07-23 | 2014-08-05 | Abbott Diabetes Care Inc. | Real time management of data relating to physiological control of glucose levels |
US8814831B2 (en) | 2010-11-30 | 2014-08-26 | Becton, Dickinson And Company | Ballistic microneedle infusion device |
US8905972B2 (en) | 2010-11-20 | 2014-12-09 | Perqflo, Llc | Infusion pumps |
US8915879B2 (en) | 2010-09-24 | 2014-12-23 | Perqflo, Llc | Infusion pumps |
US8932216B2 (en) | 2006-08-07 | 2015-01-13 | Abbott Diabetes Care Inc. | Method and system for providing data management in integrated analyte monitoring and infusion system |
US8939928B2 (en) | 2009-07-23 | 2015-01-27 | Becton, Dickinson And Company | Medical device having capacitive coupling communication and energy harvesting |
US8986253B2 (en) | 2008-01-25 | 2015-03-24 | Tandem Diabetes Care, Inc. | Two chamber pumps and related methods |
US9005169B2 (en) | 2007-10-16 | 2015-04-14 | Cequr Sa | Cannula insertion device and related methods |
US9173996B2 (en) | 2001-05-18 | 2015-11-03 | Deka Products Limited Partnership | Infusion set for a fluid pump |
US9180245B2 (en) | 2008-10-10 | 2015-11-10 | Deka Products Limited Partnership | System and method for administering an infusible fluid |
US9211378B2 (en) | 2010-10-22 | 2015-12-15 | Cequr Sa | Methods and systems for dosing a medicament |
US9216249B2 (en) | 2010-09-24 | 2015-12-22 | Perqflo, Llc | Infusion pumps |
US9250106B2 (en) | 2009-02-27 | 2016-02-02 | Tandem Diabetes Care, Inc. | Methods and devices for determination of flow reservoir volume |
US9375529B2 (en) | 2009-09-02 | 2016-06-28 | Becton, Dickinson And Company | Extended use medical device |
US9416775B2 (en) | 2014-07-02 | 2016-08-16 | Becton, Dickinson And Company | Internal cam metering pump |
WO2016134137A1 (en) | 2015-02-18 | 2016-08-25 | Insulet Corporation | Fluid delivery and infusion devices, and methods of use thereof |
US9433757B2 (en) | 2011-03-03 | 2016-09-06 | Becton, Dickinson And Company | Compact spring inserter for drug delivery infusion set |
US9498573B2 (en) | 2010-09-24 | 2016-11-22 | Perqflo, Llc | Infusion pumps |
US9623173B2 (en) | 2012-03-05 | 2017-04-18 | Becton, Dickinson And Company | Wireless communication for on-body medical devices |
US9750444B2 (en) | 2009-09-30 | 2017-09-05 | Abbott Diabetes Care Inc. | Interconnect for on-body analyte monitoring device |
US9782536B2 (en) | 2009-01-12 | 2017-10-10 | Becton, Dickinson And Company | Infusion set and/or patch pump having at least one of an in-dwelling rigid catheter with flexible features and/or a flexible catheter attachment |
US9950109B2 (en) | 2010-11-30 | 2018-04-24 | Becton, Dickinson And Company | Slide-activated angled inserter and cantilevered ballistic insertion for intradermal drug infusion |
US9962486B2 (en) | 2013-03-14 | 2018-05-08 | Tandem Diabetes Care, Inc. | System and method for detecting occlusions in an infusion pump |
US10004845B2 (en) | 2014-04-18 | 2018-06-26 | Becton, Dickinson And Company | Split piston metering pump |
US10080841B2 (en) | 2015-11-18 | 2018-09-25 | President And Fellows Of Harvard College | Systems and methods for monitoring, managing, and treating asthma and anaphylaxis |
US10092691B2 (en) | 2009-09-02 | 2018-10-09 | Becton, Dickinson And Company | Flexible and conformal patch pump |
US10159786B2 (en) | 2014-09-30 | 2018-12-25 | Perqflo, Llc | Hybrid ambulatory infusion pumps |
US10258736B2 (en) | 2012-05-17 | 2019-04-16 | Tandem Diabetes Care, Inc. | Systems including vial adapter for fluid transfer |
US10434285B2 (en) | 2011-02-09 | 2019-10-08 | Becton, Dickinson And Company | Self-contained inserter for drug delivery infusion set |
US10441717B2 (en) | 2014-04-15 | 2019-10-15 | Insulet Corporation | Monitoring a physiological parameter associated with tissue of a host to confirm delivery of medication |
US10448885B2 (en) | 2015-06-12 | 2019-10-22 | Insulet Corporation | Confirmation of delivery of medication to a host |
WO2020097552A1 (en) * | 2018-11-08 | 2020-05-14 | Capillary Biomedical, Inc | Linear insertion device with rotational drive |
US10716896B2 (en) | 2015-11-24 | 2020-07-21 | Insulet Corporation | Wearable automated medication delivery system |
US10751478B2 (en) | 2016-10-07 | 2020-08-25 | Insulet Corporation | Multi-stage delivery system |
US10777319B2 (en) | 2014-01-30 | 2020-09-15 | Insulet Netherlands B.V. | Therapeutic product delivery system and method of pairing |
US10780217B2 (en) | 2016-11-10 | 2020-09-22 | Insulet Corporation | Ratchet drive for on body delivery system |
US10874803B2 (en) | 2018-05-31 | 2020-12-29 | Insulet Corporation | Drug cartridge with drive system |
US10898656B2 (en) | 2017-09-26 | 2021-01-26 | Insulet Corporation | Needle mechanism module for drug delivery device |
US10963417B2 (en) | 2004-06-04 | 2021-03-30 | Abbott Diabetes Care Inc. | Systems and methods for managing diabetes care data |
US10973978B2 (en) | 2017-08-03 | 2021-04-13 | Insulet Corporation | Fluid flow regulation arrangements for drug delivery devices |
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US11534089B2 (en) | 2011-02-28 | 2022-12-27 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
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US11642283B2 (en) | 2007-12-31 | 2023-05-09 | Deka Products Limited Partnership | Method for fluid delivery |
US11672909B2 (en) | 2016-02-12 | 2023-06-13 | Medtronic Minimed, Inc. | Ambulatory infusion pumps and assemblies for use with same |
US11676694B2 (en) | 2012-06-07 | 2023-06-13 | Tandem Diabetes Care, Inc. | Device and method for training users of ambulatory medical devices |
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US11684716B2 (en) | 2020-07-31 | 2023-06-27 | Insulet Corporation | Techniques to reduce risk of occlusions in drug delivery systems |
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US11911590B2 (en) | 2013-12-26 | 2024-02-27 | Tandem Diabetes Care, Inc. | Integration of infusion pump with remote electronic device |
US11929158B2 (en) | 2016-01-13 | 2024-03-12 | Insulet Corporation | User interface for diabetes management system |
US11935637B2 (en) | 2019-09-27 | 2024-03-19 | Insulet Corporation | Onboarding and total daily insulin adaptivity |
USD1020794S1 (en) | 2018-04-02 | 2024-04-02 | Bigfoot Biomedical, Inc. | Medication delivery device with icons |
US11957875B2 (en) | 2019-12-06 | 2024-04-16 | Insulet Corporation | Techniques and devices providing adaptivity and personalization in diabetes treatment |
US11964126B2 (en) | 2006-02-09 | 2024-04-23 | Deka Products Limited Partnership | Infusion pump assembly |
USD1024090S1 (en) | 2019-01-09 | 2024-04-23 | Bigfoot Biomedical, Inc. | Display screen or portion thereof with graphical user interface associated with insulin delivery |
US11969579B2 (en) | 2017-01-13 | 2024-04-30 | Insulet Corporation | Insulin delivery methods, systems and devices |
US11986630B2 (en) | 2020-02-12 | 2024-05-21 | Insulet Corporation | Dual hormone delivery system for reducing impending hypoglycemia and/or hyperglycemia risk |
US11992653B2 (en) | 2018-07-18 | 2024-05-28 | Insulet Corporation | Drug delivery insertion apparatuses and system |
US12036389B2 (en) | 2020-01-06 | 2024-07-16 | Insulet Corporation | Prediction of meal and/or exercise events based on persistent residuals |
US12042630B2 (en) | 2017-01-13 | 2024-07-23 | Insulet Corporation | System and method for adjusting insulin delivery |
US12064591B2 (en) | 2013-07-19 | 2024-08-20 | Insulet Corporation | Infusion pump system and method |
US12064590B2 (en) | 2006-02-09 | 2024-08-20 | Deka Products Limited Partnership | Patch-sized fluid delivery systems and methods |
US12070574B2 (en) | 2006-02-09 | 2024-08-27 | Deka Products Limited Partnership | Apparatus, systems and methods for an infusion pump assembly |
US12076160B2 (en) | 2016-12-12 | 2024-09-03 | Insulet Corporation | Alarms and alerts for medication delivery devices and systems |
US12090498B2 (en) | 2021-08-19 | 2024-09-17 | Insulet Corporation | Low-friction rolling plunger for a wearable drug delivery device |
US12097353B2 (en) | 2021-02-25 | 2024-09-24 | Medtronic Minimed, Inc. | Infusion pumps |
Families Citing this family (255)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6595956B1 (en) | 1998-03-23 | 2003-07-22 | Joseph Gross | Drug delivery device |
US20050160858A1 (en) * | 2002-07-24 | 2005-07-28 | M 2 Medical A/S | Shape memory alloy actuator |
JP2005533545A (en) | 2002-07-24 | 2005-11-10 | エム2・メディカル・アクティーゼルスカブ | Infusion pump system, infusion pump unit, infusion pump |
US7128727B2 (en) * | 2002-09-30 | 2006-10-31 | Flaherty J Christopher | Components and methods for patient infusion device |
WO2004041330A2 (en) | 2002-11-05 | 2004-05-21 | M 2 Medical A/S | A disposable wearable insulin dispensing device, a combination of such a device and a programming controller and a method of controlling the operation of such a device |
AU2003287926A1 (en) | 2002-12-23 | 2004-07-14 | M2 Medical A/S | A disposable, wearable insulin dispensing device, a combination of such a device and a programming controller and a method of controlling the operation of such a device |
EP1583573B1 (en) | 2002-12-23 | 2011-02-16 | Asante Solutions, Inc. | Flexible piston rod |
CA2523267C (en) * | 2003-04-23 | 2013-09-03 | Biovalve Technologies, Inc. | Hydraulically actuated pump for long duration medicament administration |
US7753879B2 (en) | 2004-01-29 | 2010-07-13 | M2 Group Holdings, Inc. | Disposable medicine dispensing device |
DE102004019053A1 (en) * | 2004-04-20 | 2005-11-24 | Disetronic Licensing Ag | Apparatus and method for occlusion detection in infusion pumps |
WO2006014425A1 (en) | 2004-07-02 | 2006-02-09 | Biovalve Technologies, Inc. | Methods and devices for delivering glp-1 and uses thereof |
US9636450B2 (en) * | 2007-02-19 | 2017-05-02 | Udo Hoss | Pump system modular components for delivering medication and analyte sensing at seperate insertion sites |
US20060217771A1 (en) | 2005-02-07 | 2006-09-28 | Medtronic, Inc. | Potassium monitoring |
WO2006105793A1 (en) | 2005-04-06 | 2006-10-12 | M 2 Medical A/S | Method and device for dispensing liquid medicine by means of a twistable element |
US8840586B2 (en) | 2006-08-23 | 2014-09-23 | Medtronic Minimed, Inc. | Systems and methods allowing for reservoir filling and infusion medium delivery |
US20080097291A1 (en) | 2006-08-23 | 2008-04-24 | Hanson Ian B | Infusion pumps and methods and delivery devices and methods with same |
US8277415B2 (en) | 2006-08-23 | 2012-10-02 | Medtronic Minimed, Inc. | Infusion medium delivery device and method with drive device for driving plunger in reservoir |
US8512288B2 (en) | 2006-08-23 | 2013-08-20 | Medtronic Minimed, Inc. | Infusion medium delivery device and method with drive device for driving plunger in reservoir |
US7905868B2 (en) | 2006-08-23 | 2011-03-15 | Medtronic Minimed, Inc. | Infusion medium delivery device and method with drive device for driving plunger in reservoir |
US8137314B2 (en) | 2006-08-23 | 2012-03-20 | Medtronic Minimed, Inc. | Infusion medium delivery device and method with compressible or curved reservoir or conduit |
US20110077605A1 (en) * | 2005-07-14 | 2011-03-31 | Boehringer Technologies, L.P. | Pump system for negative pressure wound therapy |
US7857806B2 (en) * | 2005-07-14 | 2010-12-28 | Boehringer Technologies, L.P. | Pump system for negative pressure wound therapy |
PL1762259T3 (en) * | 2005-09-12 | 2011-03-31 | Unomedical As | Inserter for an infusion set with a first and second spring units |
US8057436B2 (en) * | 2005-09-26 | 2011-11-15 | Asante Solutions, Inc. | Dispensing fluid from an infusion pump system |
US8409142B2 (en) | 2005-09-26 | 2013-04-02 | Asante Solutions, Inc. | Operating an infusion pump system |
US8105279B2 (en) | 2005-09-26 | 2012-01-31 | M2 Group Holdings, Inc. | Dispensing fluid from an infusion pump system |
US7534226B2 (en) | 2005-09-26 | 2009-05-19 | M2 Group Holdings, Inc. | Dispensing fluid from an infusion pump system |
US8551046B2 (en) | 2006-09-18 | 2013-10-08 | Asante Solutions, Inc. | Dispensing fluid from an infusion pump system |
EP2162168B1 (en) | 2005-09-26 | 2018-11-07 | Bigfoot Biomedical, Inc. | Modular infusion pump having two different energy sources |
US8880138B2 (en) | 2005-09-30 | 2014-11-04 | Abbott Diabetes Care Inc. | Device for channeling fluid and methods of use |
WO2007056504A1 (en) | 2005-11-08 | 2007-05-18 | M2 Medical A/S | Infusion pump system |
EP1955240B8 (en) | 2005-11-08 | 2016-03-30 | Bigfoot Biomedical, Inc. | Method for manual and autonomous control of an infusion pump |
FR2894993A1 (en) * | 2005-12-19 | 2007-06-22 | Rhodia Recherches & Tech | NEW METHOD FOR IMPREGNATING A TEXTILE SURFACE |
US8579884B2 (en) * | 2006-02-09 | 2013-11-12 | Deka Products Limited Partnership | Infusion pump assembly |
WO2007115039A2 (en) | 2006-03-30 | 2007-10-11 | Valeritas, Llc | Multi-cartridge fluid delivery device |
US8478557B2 (en) | 2009-07-31 | 2013-07-02 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte monitoring system calibration accuracy |
US8140312B2 (en) | 2007-05-14 | 2012-03-20 | Abbott Diabetes Care Inc. | Method and system for determining analyte levels |
US9392969B2 (en) | 2008-08-31 | 2016-07-19 | Abbott Diabetes Care Inc. | Closed loop control and signal attenuation detection |
US20070270750A1 (en) * | 2006-05-17 | 2007-11-22 | Alcon, Inc. | Drug delivery device |
US20090171269A1 (en) * | 2006-06-29 | 2009-07-02 | Abbott Diabetes Care, Inc. | Infusion Device and Methods Therefor |
US7811262B2 (en) | 2006-08-23 | 2010-10-12 | Medtronic Minimed, Inc. | Systems and methods allowing for reservoir filling and infusion medium delivery |
US20080051765A1 (en) * | 2006-08-23 | 2008-02-28 | Medtronic Minimed, Inc. | Systems and methods allowing for reservoir filling and infusion medium delivery |
US7828764B2 (en) | 2006-08-23 | 2010-11-09 | Medtronic Minimed, Inc. | Systems and methods allowing for reservoir filling and infusion medium delivery |
US7794434B2 (en) * | 2006-08-23 | 2010-09-14 | Medtronic Minimed, Inc. | Systems and methods allowing for reservoir filling and infusion medium delivery |
US7736338B2 (en) | 2006-08-23 | 2010-06-15 | Medtronic Minimed, Inc. | Infusion medium delivery system, device and method with needle inserter and needle inserter device and method |
US8597243B2 (en) | 2007-04-30 | 2013-12-03 | Medtronic Minimed, Inc. | Systems and methods allowing for reservoir air bubble management |
US8434528B2 (en) | 2007-04-30 | 2013-05-07 | Medtronic Minimed, Inc. | Systems and methods for reservoir filling |
US7963954B2 (en) | 2007-04-30 | 2011-06-21 | Medtronic Minimed, Inc. | Automated filling systems and methods |
US8323250B2 (en) | 2007-04-30 | 2012-12-04 | Medtronic Minimed, Inc. | Adhesive patch systems and methods |
DK2146760T3 (en) | 2007-04-30 | 2019-01-28 | Medtronic Minimed Inc | FILLING OF RESERVOIR, BUBBLE MANAGEMENT AND DELIVERY SYSTEMS FOR INFUSION MEDIA AND PROCEDURES |
US8613725B2 (en) | 2007-04-30 | 2013-12-24 | Medtronic Minimed, Inc. | Reservoir systems and methods |
US7959715B2 (en) | 2007-04-30 | 2011-06-14 | Medtronic Minimed, Inc. | Systems and methods allowing for reservoir air bubble management |
US8239166B2 (en) | 2007-05-14 | 2012-08-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US7892199B2 (en) | 2007-05-21 | 2011-02-22 | Asante Solutions, Inc. | Occlusion sensing for an infusion pump |
US7794426B2 (en) | 2007-05-21 | 2010-09-14 | Asante Solutions, Inc. | Infusion pump system with contamination-resistant features |
US7833196B2 (en) | 2007-05-21 | 2010-11-16 | Asante Solutions, Inc. | Illumination instrument for an infusion pump |
US7981102B2 (en) | 2007-05-21 | 2011-07-19 | Asante Solutions, Inc. | Removable controller for an infusion pump |
US20090063402A1 (en) * | 2007-08-31 | 2009-03-05 | Abbott Diabetes Care, Inc. | Method and System for Providing Medication Level Determination |
US7717903B2 (en) | 2007-09-06 | 2010-05-18 | M2 Group Holdings, Inc. | Operating an infusion pump system |
US7828528B2 (en) | 2007-09-06 | 2010-11-09 | Asante Solutions, Inc. | Occlusion sensing system for infusion pumps |
US8287514B2 (en) | 2007-09-07 | 2012-10-16 | Asante Solutions, Inc. | Power management techniques for an infusion pump system |
US7935076B2 (en) | 2007-09-07 | 2011-05-03 | Asante Solutions, Inc. | Activity sensing techniques for an infusion pump system |
US7935105B2 (en) | 2007-09-07 | 2011-05-03 | Asante Solutions, Inc. | Data storage for an infusion pump system |
US7879026B2 (en) | 2007-09-07 | 2011-02-01 | Asante Solutions, Inc. | Controlled adjustment of medicine dispensation from an infusion pump device |
US7771391B2 (en) * | 2007-09-28 | 2010-08-10 | Calibra Medical, Inc. | Disposable infusion device with snap action actuation |
US8128596B2 (en) * | 2007-09-28 | 2012-03-06 | Calibra Medial, Inc. | Disposable infusion device layered structure |
US7967795B1 (en) | 2010-01-19 | 2011-06-28 | Lamodel Ltd. | Cartridge interface assembly with driving plunger |
US10420880B2 (en) | 2007-10-02 | 2019-09-24 | West Pharma. Services IL, Ltd. | Key for securing components of a drug delivery system during assembly and/or transport and methods of using same |
US9345836B2 (en) | 2007-10-02 | 2016-05-24 | Medimop Medical Projects Ltd. | Disengagement resistant telescoping assembly and unidirectional method of assembly for such |
US9173997B2 (en) | 2007-10-02 | 2015-11-03 | Medimop Medical Projects Ltd. | External drug pump |
US9656019B2 (en) | 2007-10-02 | 2017-05-23 | Medimop Medical Projects Ltd. | Apparatuses for securing components of a drug delivery system during transport and methods of using same |
US8377031B2 (en) | 2007-10-23 | 2013-02-19 | Abbott Diabetes Care Inc. | Closed loop control system with safety parameters and methods |
US20090112149A1 (en) * | 2007-10-31 | 2009-04-30 | Kriesel Marshall S | Variable rate fluid dispenser |
EP2224980B1 (en) * | 2007-11-12 | 2018-07-25 | Medicom Innovation Partner a/s | Auto injector with changing anchor locations for a mechanical driver |
US7771392B2 (en) * | 2007-11-29 | 2010-08-10 | Roche Diagnostics Operations, Inc. | Lead screw delivery device using reusable shape memory actuator drive |
US7875022B2 (en) | 2007-12-12 | 2011-01-25 | Asante Solutions, Inc. | Portable infusion pump and media player |
US20090164239A1 (en) | 2007-12-19 | 2009-06-25 | Abbott Diabetes Care, Inc. | Dynamic Display Of Glucose Information |
US8313467B2 (en) | 2007-12-27 | 2012-11-20 | Medtronic Minimed, Inc. | Reservoir pressure equalization systems and methods |
EP2259816B1 (en) | 2008-02-20 | 2015-10-21 | Unomedical A/S | Insertion device with horizontally moving part |
US9295776B2 (en) | 2008-04-11 | 2016-03-29 | Medtronic Minimed, Inc. | Reservoir plunger head systems and methods |
US8597269B2 (en) | 2008-04-11 | 2013-12-03 | Medtronic Minimed, Inc. | Reservoir seal retainer systems and methods |
US8206353B2 (en) | 2008-04-11 | 2012-06-26 | Medtronic Minimed, Inc. | Reservoir barrier layer systems and methods |
US8858501B2 (en) | 2008-04-11 | 2014-10-14 | Medtronic Minimed, Inc. | Reservoir barrier layer systems and methods |
US8172811B2 (en) | 2008-05-15 | 2012-05-08 | Roche Diagnostics Operations, Inc. | Drug delivery pump drive using a shaped memory alloy wire |
WO2010009172A1 (en) | 2008-07-14 | 2010-01-21 | Abbott Diabetes Care Inc. | Closed loop control system interface and methods |
US20100057040A1 (en) | 2008-08-31 | 2010-03-04 | Abbott Diabetes Care, Inc. | Robust Closed Loop Control And Methods |
US8734422B2 (en) | 2008-08-31 | 2014-05-27 | Abbott Diabetes Care Inc. | Closed loop control with improved alarm functions |
US8622988B2 (en) * | 2008-08-31 | 2014-01-07 | Abbott Diabetes Care Inc. | Variable rate closed loop control and methods |
US9943644B2 (en) | 2008-08-31 | 2018-04-17 | Abbott Diabetes Care Inc. | Closed loop control with reference measurement and methods thereof |
US9393369B2 (en) | 2008-09-15 | 2016-07-19 | Medimop Medical Projects Ltd. | Stabilized pen injector |
WO2010041261A1 (en) * | 2008-10-09 | 2010-04-15 | Medingo Ltd. | Skin securable drug delivery device with a shock absorbing protective shield |
US20100145305A1 (en) * | 2008-11-10 | 2010-06-10 | Ruth Alon | Low volume accurate injector |
US9370621B2 (en) | 2008-12-16 | 2016-06-21 | Medtronic Minimed, Inc. | Needle insertion systems and methods |
US8152779B2 (en) * | 2008-12-30 | 2012-04-10 | Medimop Medical Projects Ltd. | Needle assembly for drug pump |
US8052656B2 (en) * | 2009-02-10 | 2011-11-08 | Tyco Healthcare Group Lp | Enteral feeding system |
US8393357B2 (en) | 2009-07-08 | 2013-03-12 | Medtronic Minimed, Inc. | Reservoir filling systems and methods |
US8356644B2 (en) | 2009-08-07 | 2013-01-22 | Medtronic Minimed, Inc. | Transfer guard systems and methods |
US8900190B2 (en) | 2009-09-02 | 2014-12-02 | Medtronic Minimed, Inc. | Insertion device systems and methods |
US8308679B2 (en) | 2009-12-30 | 2012-11-13 | Medtronic Minimed, Inc. | Alignment systems and methods |
US8932256B2 (en) | 2009-09-02 | 2015-01-13 | Medtronic Minimed, Inc. | Insertion device systems and methods |
US10071198B2 (en) | 2012-11-02 | 2018-09-11 | West Pharma. Servicees IL, Ltd. | Adhesive structure for medical device |
US10071196B2 (en) | 2012-05-15 | 2018-09-11 | West Pharma. Services IL, Ltd. | Method for selectively powering a battery-operated drug-delivery device and device therefor |
US8157769B2 (en) | 2009-09-15 | 2012-04-17 | Medimop Medical Projects Ltd. | Cartridge insertion assembly for drug delivery system |
US9399091B2 (en) | 2009-09-30 | 2016-07-26 | Medtronic, Inc. | System and method to regulate ultrafiltration |
WO2011087804A2 (en) | 2009-12-21 | 2011-07-21 | Medtronic, Inc. | Peptide-polynucleotide compositions, and methods for transfecting a cell with dna and treatment of neurodegenerative disease |
US8998840B2 (en) | 2009-12-30 | 2015-04-07 | Medtronic Minimed, Inc. | Connection and alignment systems and methods |
US9039653B2 (en) | 2009-12-29 | 2015-05-26 | Medtronic Minimed, Inc. | Retention systems and methods |
US8998858B2 (en) | 2009-12-29 | 2015-04-07 | Medtronic Minimed, Inc. | Alignment and connection systems and methods |
US8858500B2 (en) | 2009-12-30 | 2014-10-14 | Medtronic Minimed, Inc. | Engagement and sensing systems and methods |
US8435209B2 (en) | 2009-12-30 | 2013-05-07 | Medtronic Minimed, Inc. | Connection and alignment detection systems and methods |
US20120215163A1 (en) | 2009-12-30 | 2012-08-23 | Medtronic Minimed, Inc. | Sensing systems and methods |
US8348898B2 (en) | 2010-01-19 | 2013-01-08 | Medimop Medical Projects Ltd. | Automatic needle for drug pump |
JP5569014B2 (en) * | 2010-02-03 | 2014-08-13 | セイコーエプソン株式会社 | Fluid transport device |
US9326708B2 (en) | 2010-03-26 | 2016-05-03 | Medtronic Minimed, Inc. | Ambient temperature sensor systems and methods |
EP2569031B1 (en) | 2010-05-10 | 2017-10-11 | Medimop Medical Projects Ltd. | Low volume accurate injector |
USD669165S1 (en) | 2010-05-27 | 2012-10-16 | Asante Solutions, Inc. | Infusion pump |
WO2011153526A2 (en) * | 2010-06-04 | 2011-12-08 | Parker-Hannifin Corporation | Miniaturized syringe pump system and modules |
AU2011265005B2 (en) | 2010-06-07 | 2015-04-09 | Amgen Inc. | Drug delivery device |
US8814829B2 (en) | 2010-08-12 | 2014-08-26 | Baxter International Inc. | Drug delivery device for fluid restricted patients |
WO2012048168A2 (en) | 2010-10-07 | 2012-04-12 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods |
US8919452B2 (en) | 2010-11-08 | 2014-12-30 | Baker Hughes Incorporated | Casing spears and related systems and methods |
WO2012103428A2 (en) | 2011-01-27 | 2012-08-02 | Medtronic Minimed, Inc. | Insertion device systems and methods |
US10342918B2 (en) | 2011-02-09 | 2019-07-09 | Becton, Dickinson And Company | Subcutaneous infusion device |
US8852152B2 (en) | 2011-02-09 | 2014-10-07 | Asante Solutions, Inc. | Infusion pump systems and methods |
US8998851B2 (en) | 2011-02-09 | 2015-04-07 | Becton, Dickinson And Company | Compact spring inserter for drug deliver infusion set |
WO2012115772A2 (en) | 2011-02-25 | 2012-08-30 | Medtronic, Inc. | Therapy for kidney disease and/or heart failure |
US20120220528A1 (en) | 2011-02-25 | 2012-08-30 | Medtronic, Inc. | Systems and methods for therapy of kidney disease and/or heart failure using chimeric natriuretic peptides |
US8454581B2 (en) | 2011-03-16 | 2013-06-04 | Asante Solutions, Inc. | Infusion pump systems and methods |
USD702834S1 (en) | 2011-03-22 | 2014-04-15 | Medimop Medical Projects Ltd. | Cartridge for use in injection device |
WO2012131044A1 (en) | 2011-03-30 | 2012-10-04 | Unomedical A/S | Subcutaneous inserter device |
US8926542B2 (en) | 2011-04-29 | 2015-01-06 | Medtronic, Inc. | Monitoring fluid volume for patients with renal disease |
US9848778B2 (en) | 2011-04-29 | 2017-12-26 | Medtronic, Inc. | Method and device to monitor patients with kidney disease |
US9456755B2 (en) | 2011-04-29 | 2016-10-04 | Medtronic, Inc. | Method and device to monitor patients with kidney disease |
US8585657B2 (en) | 2011-06-21 | 2013-11-19 | Asante Solutions, Inc. | Dispensing fluid from an infusion pump system |
CN103889481B (en) | 2011-08-02 | 2016-03-09 | 美敦力公司 | With the hemodialysis system of flow path with controlled compliance volume |
US10857277B2 (en) | 2011-08-16 | 2020-12-08 | Medtronic, Inc. | Modular hemodialysis system |
EP2750697A4 (en) | 2011-09-02 | 2015-03-25 | Medtronic Inc | Chimeric natriuretic peptide compositions and methods of preparation |
US8808230B2 (en) | 2011-09-07 | 2014-08-19 | Asante Solutions, Inc. | Occlusion detection for an infusion pump system |
WO2013053076A1 (en) | 2011-10-10 | 2013-04-18 | Zensun (Shanghai)Science & Technology Limited | Compositions and methods for treating heart failure |
US9713668B2 (en) | 2012-01-04 | 2017-07-25 | Medtronic, Inc. | Multi-staged filtration system for blood fluid removal |
EP2809375B1 (en) | 2012-01-31 | 2021-08-11 | Medimop Medical Projects Ltd. | Time dependent drug delivery apparatus |
US10668213B2 (en) | 2012-03-26 | 2020-06-02 | West Pharma. Services IL, Ltd. | Motion activated mechanisms for a drug delivery device |
US9463280B2 (en) | 2012-03-26 | 2016-10-11 | Medimop Medical Projects Ltd. | Motion activated septum puncturing drug delivery device |
US9072827B2 (en) | 2012-03-26 | 2015-07-07 | Medimop Medical Projects Ltd. | Fail safe point protector for needle safety flap |
US9555186B2 (en) | 2012-06-05 | 2017-01-31 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8454557B1 (en) | 2012-07-19 | 2013-06-04 | Asante Solutions, Inc. | Infusion pump system and method |
US8454562B1 (en) | 2012-07-20 | 2013-06-04 | Asante Solutions, Inc. | Infusion pump system and method |
US9867929B2 (en) | 2012-08-15 | 2018-01-16 | Becton, Dickinson And Company | Pump engine with metering system for dispensing liquid medication |
US9731069B2 (en) | 2012-09-27 | 2017-08-15 | Becton, Dickinson And Company | Perpendicular infusion set and disposable inserter |
US9427523B2 (en) | 2012-12-10 | 2016-08-30 | Bigfoot Biomedical, Inc. | Infusion pump system and method |
US10905816B2 (en) | 2012-12-10 | 2021-02-02 | Medtronic, Inc. | Sodium management system for hemodialysis |
US20140276536A1 (en) | 2013-03-14 | 2014-09-18 | Asante Solutions, Inc. | Infusion Pump System and Methods |
US9421323B2 (en) | 2013-01-03 | 2016-08-23 | Medimop Medical Projects Ltd. | Door and doorstop for portable one use drug delivery apparatus |
US11565029B2 (en) | 2013-01-09 | 2023-01-31 | Medtronic, Inc. | Sorbent cartridge with electrodes |
US9707328B2 (en) | 2013-01-09 | 2017-07-18 | Medtronic, Inc. | Sorbent cartridge to measure solute concentrations |
US9713666B2 (en) | 2013-01-09 | 2017-07-25 | Medtronic, Inc. | Recirculating dialysate fluid circuit for blood measurement |
US11154648B2 (en) | 2013-01-09 | 2021-10-26 | Medtronic, Inc. | Fluid circuits for sorbent cartridge with sensors |
US9623164B2 (en) | 2013-02-01 | 2017-04-18 | Medtronic, Inc. | Systems and methods for multifunctional volumetric fluid control |
US10850016B2 (en) | 2013-02-01 | 2020-12-01 | Medtronic, Inc. | Modular fluid therapy system having jumpered flow paths and systems and methods for cleaning and disinfection |
US10543052B2 (en) | 2013-02-01 | 2020-01-28 | Medtronic, Inc. | Portable dialysis cabinet |
US9526822B2 (en) | 2013-02-01 | 2016-12-27 | Medtronic, Inc. | Sodium and buffer source cartridges for use in a modular controlled compliant flow path |
US10010663B2 (en) | 2013-02-01 | 2018-07-03 | Medtronic, Inc. | Fluid circuit for delivery of renal replacement therapies |
US9827361B2 (en) | 2013-02-02 | 2017-11-28 | Medtronic, Inc. | pH buffer measurement system for hemodialysis systems |
US9144640B2 (en) | 2013-02-02 | 2015-09-29 | Medtronic, Inc. | Sorbent cartridge configurations for improved dialysate regeneration |
US9446186B2 (en) | 2013-03-01 | 2016-09-20 | Bigfoot Biomedical, Inc. | Operating an infusion pump system |
US20140296784A1 (en) * | 2013-03-27 | 2014-10-02 | Animas Corporation | Infusion device with layered structure having durable and disposable components |
US9011164B2 (en) | 2013-04-30 | 2015-04-21 | Medimop Medical Projects Ltd. | Clip contact for easy installation of printed circuit board PCB |
US9889256B2 (en) | 2013-05-03 | 2018-02-13 | Medimop Medical Projects Ltd. | Sensing a status of an infuser based on sensing motor control and power input |
KR102357275B1 (en) | 2013-05-22 | 2022-02-03 | 젠순 (상하이) 사이언스 앤드 테크놀로지 캄파니 리미티드 | Extended release of neuregulin for treating heart failure |
US9446187B2 (en) | 2013-06-03 | 2016-09-20 | Bigfoot Biomedical, Inc. | Infusion pump system and method |
US9457141B2 (en) | 2013-06-03 | 2016-10-04 | Bigfoot Biomedical, Inc. | Infusion pump system and method |
CN105555336B (en) | 2013-08-05 | 2019-04-30 | 康迈德医疗器械有限公司 | The patch pump of compliance |
MX2016005315A (en) | 2013-10-24 | 2016-08-11 | Amgen Inc | Drug delivery system with temperature-sensitive control. |
EP3102107A4 (en) | 2013-11-04 | 2018-02-07 | Medtronic, Inc. | Method and device to manage fluid volumes in the body |
US9884145B2 (en) | 2013-11-26 | 2018-02-06 | Medtronic, Inc. | Parallel modules for in-line recharging of sorbents using alternate duty cycles |
US10537875B2 (en) | 2013-11-26 | 2020-01-21 | Medtronic, Inc. | Precision recharging of sorbent materials using patient and session data |
CN105992552B (en) | 2013-11-27 | 2019-06-18 | 美敦力公司 | Accurate dialysis monitoring and synchronization system |
US10569015B2 (en) | 2013-12-02 | 2020-02-25 | Bigfoot Biomedical, Inc. | Infusion pump system and method |
JP6822843B2 (en) | 2014-06-03 | 2021-01-27 | アムジエン・インコーポレーテツド | Systems and methods for remotely processing data collected by drug delivery devices |
WO2015199768A1 (en) | 2014-06-24 | 2015-12-30 | Medtronic, Inc. | Stacked sorbent assembly |
WO2015199766A1 (en) | 2014-06-24 | 2015-12-30 | Medtronic, Inc. | Modular dialysate regeneration assembly |
US9629901B2 (en) | 2014-07-01 | 2017-04-25 | Bigfoot Biomedical, Inc. | Glucagon administration system and methods |
US10137246B2 (en) | 2014-08-06 | 2018-11-27 | Bigfoot Biomedical, Inc. | Infusion pump assembly and method |
US9919096B2 (en) | 2014-08-26 | 2018-03-20 | Bigfoot Biomedical, Inc. | Infusion pump system and method |
US9895479B2 (en) | 2014-12-10 | 2018-02-20 | Medtronic, Inc. | Water management system for use in dialysis |
US10874787B2 (en) | 2014-12-10 | 2020-12-29 | Medtronic, Inc. | Degassing system for dialysis |
US9713665B2 (en) | 2014-12-10 | 2017-07-25 | Medtronic, Inc. | Degassing system for dialysis |
US10098993B2 (en) | 2014-12-10 | 2018-10-16 | Medtronic, Inc. | Sensing and storage system for fluid balance |
SG10201907352UA (en) * | 2015-02-10 | 2019-09-27 | Amgen Inc | Rotationally biased insertion mechanism for a drug delivery pump |
US10251813B2 (en) | 2015-03-04 | 2019-04-09 | West Pharma. Services IL, Ltd. | Flexibly mounted cartridge alignment collar for drug delivery device |
US9795534B2 (en) | 2015-03-04 | 2017-10-24 | Medimop Medical Projects Ltd. | Compliant coupling assembly for cartridge coupling of a drug delivery device |
CN107430578B (en) | 2015-03-30 | 2020-11-17 | 索尼半导体解决方案公司 | Asynchronous interface |
US9744297B2 (en) | 2015-04-10 | 2017-08-29 | Medimop Medical Projects Ltd. | Needle cannula position as an input to operational control of an injection device |
US10293120B2 (en) | 2015-04-10 | 2019-05-21 | West Pharma. Services IL, Ltd. | Redundant injection device status indication |
US9878097B2 (en) | 2015-04-29 | 2018-01-30 | Bigfoot Biomedical, Inc. | Operating an infusion pump system |
US10149943B2 (en) | 2015-05-29 | 2018-12-11 | West Pharma. Services IL, Ltd. | Linear rotation stabilizer for a telescoping syringe stopper driverdriving assembly |
JP2018516678A (en) | 2015-06-04 | 2018-06-28 | メディモップ・メディカル・プロジェクツ・リミテッド | Drug delivery device cartridge insertion |
CN209137590U (en) * | 2015-09-21 | 2019-07-23 | 贝克顿·迪金森公司 | Noggin piece and drug delivery device in drug delivery device |
US10576207B2 (en) | 2015-10-09 | 2020-03-03 | West Pharma. Services IL, Ltd. | Angled syringe patch injector |
US9987432B2 (en) | 2015-09-22 | 2018-06-05 | West Pharma. Services IL, Ltd. | Rotation resistant friction adapter for plunger driver of drug delivery device |
US11318254B2 (en) | 2015-10-09 | 2022-05-03 | West Pharma. Services IL, Ltd. | Injector needle cap remover |
WO2017078965A1 (en) | 2015-11-06 | 2017-05-11 | Medtronic, Inc | Dialysis prescription optimization for decreased arrhythmias |
EP3374900A1 (en) | 2016-01-05 | 2018-09-19 | Bigfoot Biomedical, Inc. | Operating multi-modal medicine delivery systems |
US10449294B1 (en) | 2016-01-05 | 2019-10-22 | Bigfoot Biomedical, Inc. | Operating an infusion pump system |
CN113041432B (en) | 2016-01-21 | 2023-04-07 | 西医药服务以色列有限公司 | Medicament delivery device comprising a visual indicator |
JP6513297B2 (en) | 2016-01-21 | 2019-05-22 | ウェスト ファーマ サービシーズ イスラエル リミテッド | Automatic injector, receiving frame and method of connecting cartridge in automatic injector |
WO2017127215A1 (en) | 2016-01-21 | 2017-07-27 | Medimop Medical Projects Ltd. | Needle insertion and retraction mechanism |
US10363342B2 (en) | 2016-02-04 | 2019-07-30 | Insulet Corporation | Anti-inflammatory cannula |
USD809134S1 (en) | 2016-03-10 | 2018-01-30 | Bigfoot Biomedical, Inc. | Infusion pump assembly |
US11389597B2 (en) | 2016-03-16 | 2022-07-19 | West Pharma. Services IL, Ltd. | Staged telescopic screw assembly having different visual indicators |
US10874790B2 (en) | 2016-08-10 | 2020-12-29 | Medtronic, Inc. | Peritoneal dialysis intracycle osmotic agent adjustment |
US10994064B2 (en) | 2016-08-10 | 2021-05-04 | Medtronic, Inc. | Peritoneal dialysate flow path sensing |
WO2017189089A1 (en) | 2016-04-29 | 2017-11-02 | Amgen Inc. | Drug delivery device with messaging label |
US11103652B2 (en) | 2016-06-02 | 2021-08-31 | West Pharma. Services IL, Ltd. | Three position needle retraction |
JP7059251B2 (en) | 2016-08-01 | 2022-04-25 | ウェスト ファーマ サービシーズ イスラエル リミテッド | A spring that prevents the door from closing halfway |
WO2018026387A1 (en) | 2016-08-01 | 2018-02-08 | Medimop Medical Projects Ltd. | Anti-rotation cartridge pin |
WO2018034784A1 (en) | 2016-08-17 | 2018-02-22 | Amgen Inc. | Drug delivery device with placement detection |
US11013843B2 (en) | 2016-09-09 | 2021-05-25 | Medtronic, Inc. | Peritoneal dialysis fluid testing system |
EP3519011A4 (en) | 2016-09-27 | 2020-05-20 | Bigfoot Biomedical, Inc. | Medicine injection and disease management systems, devices, and methods |
US10981148B2 (en) | 2016-11-29 | 2021-04-20 | Medtronic, Inc. | Zirconium oxide module conditioning |
USD836769S1 (en) | 2016-12-12 | 2018-12-25 | Bigfoot Biomedical, Inc. | Insulin delivery controller |
CH713379A2 (en) | 2017-01-19 | 2018-07-31 | Tecpharma Licensing Ag | Cannula insertion mechanism for a patch device. |
WO2018134708A1 (en) | 2017-01-19 | 2018-07-26 | Tecpharma Licensing Ag | Cannula insertion mechanism for a patch device |
CH713377A2 (en) | 2017-01-19 | 2018-07-31 | Tecpharma Licensing Ag | Cannula insertion mechanism for a patch device. |
CH713378A2 (en) | 2017-01-19 | 2018-07-31 | Tecpharma Licensing Ag | Cannula insertion mechanism for a patch device. |
US10792425B2 (en) * | 2017-03-03 | 2020-10-06 | Jerry Joseph | Treatment system with automated cannula and sensor inserter, fluid delivery device, and drive mechanism for use therewith |
WO2018184012A1 (en) | 2017-03-31 | 2018-10-04 | Capillary Biomedical, Inc. | Helical insertion infusion device |
US11040137B2 (en) * | 2017-05-19 | 2021-06-22 | Min Wei | Wearable drug delivery device |
WO2018222521A1 (en) | 2017-05-30 | 2018-12-06 | West Pharma. Services IL, Ltd. | Modular drive train for wearable injector |
US10960381B2 (en) | 2017-06-15 | 2021-03-30 | Medtronic, Inc. | Zirconium phosphate disinfection recharging and conditioning |
USD839294S1 (en) | 2017-06-16 | 2019-01-29 | Bigfoot Biomedical, Inc. | Display screen with graphical user interface for closed-loop medication delivery |
US11389088B2 (en) | 2017-07-13 | 2022-07-19 | Bigfoot Biomedical, Inc. | Multi-scale display of blood glucose information |
AU2018358749B2 (en) | 2017-11-06 | 2024-02-29 | Amgen Inc. | Drug delivery device with placement and flow sensing |
US11278654B2 (en) | 2017-12-07 | 2022-03-22 | Medtronic, Inc. | Pneumatic manifold for a dialysis system |
EP3501577A1 (en) | 2017-12-21 | 2019-06-26 | TecPharma Licensing AG | Cannula insertion mechanism |
CN111683703B (en) | 2017-12-22 | 2022-11-18 | 西氏医药包装(以色列)有限公司 | Syringe adapted for cartridges of different sizes |
MA51617A (en) | 2018-01-17 | 2020-11-25 | Amgen Inc | DRUG DELIVERY MECHANISM |
US11033667B2 (en) | 2018-02-02 | 2021-06-15 | Medtronic, Inc. | Sorbent manifold for a dialysis system |
US11110215B2 (en) | 2018-02-23 | 2021-09-07 | Medtronic, Inc. | Degasser and vent manifolds for dialysis |
US11583633B2 (en) | 2018-04-03 | 2023-02-21 | Amgen Inc. | Systems and methods for delayed drug delivery |
US11213616B2 (en) | 2018-08-24 | 2022-01-04 | Medtronic, Inc. | Recharge solution for zirconium phosphate |
EP3636298A1 (en) | 2018-10-10 | 2020-04-15 | Tecpharma Licensing AG | Insertion device for a processing device |
US11806457B2 (en) | 2018-11-16 | 2023-11-07 | Mozarc Medical Us Llc | Peritoneal dialysis adequacy meaurements |
US11806456B2 (en) | 2018-12-10 | 2023-11-07 | Mozarc Medical Us Llc | Precision peritoneal dialysis therapy based on dialysis adequacy measurements |
CN111407881A (en) | 2019-01-07 | 2020-07-14 | 上海泽生科技开发股份有限公司 | Methods and compositions for neuregulin to prevent, treat or delay myocardial damage |
CH715757A2 (en) | 2019-01-17 | 2020-07-31 | Tecpharma Licensing Ag | Modular delivery device for fluid drug formulation. |
US11559624B2 (en) | 2019-11-21 | 2023-01-24 | Medtronic Minimed, Inc. | Systems for wearable infusion port and associated pump |
US11324881B2 (en) | 2019-11-21 | 2022-05-10 | Medtronic Minimed, Inc. | Systems for wearable infusion port and associated pump |
WO2021101696A1 (en) * | 2019-11-21 | 2021-05-27 | Medtronic Minimed, Inc. | Systems for wearable infusion port and associated pump |
EP3928814A1 (en) * | 2020-06-23 | 2021-12-29 | TecMed AG | Wearable drug delivery device |
CN113082397B (en) * | 2021-04-16 | 2022-10-11 | 重庆医药高等专科学校 | Medical transfusion fixing device |
US11850344B2 (en) | 2021-08-11 | 2023-12-26 | Mozarc Medical Us Llc | Gas bubble sensor |
WO2023028059A1 (en) * | 2021-08-24 | 2023-03-02 | Zyno Medical, Llc | Field-chargeable transcutaneous drug delivery system |
US11965763B2 (en) | 2021-11-12 | 2024-04-23 | Mozarc Medical Us Llc | Determining fluid flow across rotary pump |
US11944733B2 (en) | 2021-11-18 | 2024-04-02 | Mozarc Medical Us Llc | Sodium and bicarbonate control |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5569190A (en) * | 1987-06-08 | 1996-10-29 | D'antonio; Nicholas F. | Hypodermic fluid dispenser |
US6126637A (en) * | 1998-04-15 | 2000-10-03 | Science Incorporated | Fluid delivery device with collapsible needle cover |
US6478771B1 (en) * | 1998-11-13 | 2002-11-12 | Elan Pharma International Limited | Drug delivery systems and methods |
US7128727B2 (en) * | 2002-09-30 | 2006-10-31 | Flaherty J Christopher | Components and methods for patient infusion device |
Family Cites Families (148)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US405524A (en) * | 1889-06-18 | Whip-socket | ||
US315727A (en) * | 1885-04-14 | Odometer for vehicles | ||
US311735A (en) * | 1885-02-03 | Printing-press | ||
US5338157B1 (en) * | 1992-09-09 | 1999-11-02 | Sims Deltec Inc | Systems and methods for communicating with ambulat |
GB763369A (en) * | 1953-04-04 | 1956-12-12 | Metallgesellschaft Ag | Process for the catalytic conversion of gases and/or vapours |
US3631847A (en) | 1966-03-04 | 1972-01-04 | James C Hobbs | Method and apparatus for injecting fluid into the vascular system |
US3792703A (en) * | 1972-07-10 | 1974-02-19 | Deseret Pharma | Catheter placement unit |
US3812843A (en) | 1973-03-12 | 1974-05-28 | Lear Siegler Inc | Method and apparatus for injecting contrast media into the vascular system |
US3885662A (en) | 1973-12-26 | 1975-05-27 | Ibm | Steerable follower selection mechanism |
FR2348709A1 (en) | 1976-04-23 | 1977-11-18 | Pistor Michel | MESOTHERAPIC TREATMENT PROCESS AND INJECTION DEVICE, FORMING AUTOMATIC MICRO-INJECTOR, INCLUDING APPLICATION |
US4067000A (en) | 1976-05-28 | 1978-01-03 | Rca Corporation | Remote control transmitter with an audible battery life indicator |
US4273122A (en) | 1976-11-12 | 1981-06-16 | Whitney Douglass G | Self contained powered injection system |
DE2738155A1 (en) | 1977-08-24 | 1979-03-08 | Stierlen Maquet Ag | REMOTE CONTROL ARRANGEMENT FOR A MEDICAL DEVICE |
DE2738406A1 (en) | 1977-08-25 | 1979-03-08 | Stierlen Maquet Ag | PROCEDURE AND REMOTE CONTROL ARRANGEMENT FOR REMOTE CONTROL OF A MEDICAL DEVICE |
US4151845A (en) | 1977-11-25 | 1979-05-01 | Miles Laboratories, Inc. | Blood glucose control apparatus |
US4193397A (en) | 1977-12-01 | 1980-03-18 | Metal Bellows Corporation | Infusion apparatus and method |
US4559037A (en) | 1977-12-28 | 1985-12-17 | Siemens Aktiengesellschaft | Device for the pre-programmable infusion of liquids |
US4373527B1 (en) | 1979-04-27 | 1995-06-27 | Univ Johns Hopkins | Implantable programmable medication infusion system |
US4268150A (en) | 1980-01-28 | 1981-05-19 | Laurence Chen | Disposable camera with simplified film advance and indicator |
CA1169323A (en) | 1980-06-03 | 1984-06-19 | Anthony M. Albisser | Insulin infusion device |
AU546785B2 (en) | 1980-07-23 | 1985-09-19 | Commonwealth Of Australia, The | Open-loop controlled infusion of diabetics |
US4559033A (en) | 1980-10-27 | 1985-12-17 | University Of Utah Research Foundation | Apparatus and methods for minimizing peritoneal injection catheter obstruction |
US4424720A (en) | 1980-12-15 | 1984-01-10 | Ivac Corporation | Mechanism for screw drive and syringe plunger engagement/disengagement |
US4364385A (en) | 1981-03-13 | 1982-12-21 | Lossef Steven V | Insulin delivery device |
JPS57163309A (en) | 1981-04-01 | 1982-10-07 | Olympus Optical Co Ltd | Capsule apparatus for medical use |
JPS57211361A (en) | 1981-06-23 | 1982-12-25 | Terumo Corp | Liquid injecting apparatus |
US4529401A (en) | 1982-01-11 | 1985-07-16 | Cardiac Pacemakers, Inc. | Ambulatory infusion pump having programmable parameters |
US4435173A (en) | 1982-03-05 | 1984-03-06 | Delta Medical Industries | Variable rate syringe pump for insulin delivery |
US4498843A (en) | 1982-08-02 | 1985-02-12 | Schneider Philip H | Insulin infusion pump |
US4551134A (en) | 1982-08-06 | 1985-11-05 | Nuvatec, Inc. | Intravenous set |
US4514732A (en) | 1982-08-23 | 1985-04-30 | General Electric Company | Technique for increasing battery life in remote control transmitters |
US4624661A (en) | 1982-11-16 | 1986-11-25 | Surgidev Corp. | Drug dispensing system |
DE3314664C2 (en) | 1983-04-22 | 1985-02-21 | B. Braun Melsungen Ag, 3508 Melsungen | Procedure for triggering a pre-alarm in a pressure infusion apparatus |
US4781693A (en) | 1983-09-02 | 1988-11-01 | Minntech Corporation | Insulin dispenser for peritoneal cavity |
DE3468173D1 (en) | 1983-09-07 | 1988-02-04 | Disetronic Ag | Portable infusion apparatus |
US4562751A (en) | 1984-01-06 | 1986-01-07 | Nason Clyde K | Solenoid drive apparatus for an external infusion pump |
US4678408A (en) | 1984-01-06 | 1987-07-07 | Pacesetter Infusion, Ltd. | Solenoid drive apparatus for an external infusion pump |
US4685903A (en) | 1984-01-06 | 1987-08-11 | Pacesetter Infusion, Ltd. | External infusion pump apparatus |
US4684368A (en) | 1984-06-01 | 1987-08-04 | Parker Hannifin Corporation | Inverted pump |
US4855746A (en) | 1984-07-30 | 1989-08-08 | Zenith Electronics Corporation | Multiple device remote control transmitter |
US4634427A (en) | 1984-09-04 | 1987-01-06 | American Hospital Supply Company | Implantable demand medication delivery assembly |
CA1254091A (en) | 1984-09-28 | 1989-05-16 | Vladimir Feingold | Implantable medication infusion system |
US4595490A (en) * | 1985-04-01 | 1986-06-17 | Union Carbide Corporation | Processing of high normal paraffin concentration naphtha feedstocks |
US4755173A (en) | 1986-02-25 | 1988-07-05 | Pacesetter Infusion, Ltd. | Soft cannula subcutaneous injection set |
US5349852A (en) | 1986-03-04 | 1994-09-27 | Deka Products Limited Partnership | Pump controller using acoustic spectral analysis |
US4778451A (en) | 1986-03-04 | 1988-10-18 | Kamen Dean L | Flow control system using boyle's law |
AT384737B (en) | 1986-04-04 | 1987-12-28 | Thoma Dipl Ing Dr Techn Herwig | DEVICE FOR CONTINUOUSLY DELIVERING LIQUID MEDICINAL PRODUCTS |
USD306691S (en) | 1986-05-23 | 1990-03-20 | Fuji Photo Film Co., Ltd. | Disposable camera |
USD303013S (en) | 1986-06-19 | 1989-08-22 | Pacesetter Infusion, Ltd. | Female luer connector |
USD312782S (en) | 1986-06-30 | 1990-12-11 | Fuji Photo Film Co., Ltd. | Package for a disposable camera |
USD315305S (en) | 1986-06-30 | 1991-03-12 | Fuji Photo Film Co., Ltd. | Package for a disposable camera |
CA1283827C (en) | 1986-12-18 | 1991-05-07 | Giorgio Cirelli | Appliance for injection of liquid formulations |
GB8701731D0 (en) | 1987-01-27 | 1987-03-04 | Patcentre Benelux Nv Sa | Pumps |
US4734092A (en) | 1987-02-18 | 1988-03-29 | Ivac Corporation | Ambulatory drug delivery device |
ATE91239T1 (en) | 1987-05-18 | 1993-07-15 | Disetronic Ag | INFUSION DEVICE. |
US4898579A (en) | 1987-06-26 | 1990-02-06 | Pump Controller Corporation | Infusion pump |
US4748827A (en) * | 1987-06-29 | 1988-06-07 | Chang Dick Y K | Coil support structure |
US5189609A (en) | 1987-10-09 | 1993-02-23 | Hewlett-Packard Company | Medical monitoring system with softkey control |
US4836752A (en) | 1987-11-02 | 1989-06-06 | Fisher Scientific Company | Partial restriction detector |
US4896578A (en) * | 1987-12-14 | 1990-01-30 | Marx P J | Neck and body assembly for a stringed instrument |
US4898578A (en) | 1988-01-26 | 1990-02-06 | Baxter International Inc. | Drug infusion system with calculator |
US4801957A (en) | 1988-02-18 | 1989-01-31 | Eastman Kodak Company | Disposable single-use camera and accessory re-usable electronic flash unit |
US5062841A (en) | 1988-08-12 | 1991-11-05 | The Regents Of The University Of California | Implantable, self-regulating mechanochemical insulin pump |
US4882600A (en) | 1989-04-07 | 1989-11-21 | Eastman Kodak Company | Underwater disposable single-use camera |
US5205819A (en) | 1989-05-11 | 1993-04-27 | Bespak Plc | Pump apparatus for biomedical use |
US5129891A (en) | 1989-05-19 | 1992-07-14 | Strato Medical Corporation | Catheter attachment device |
US5411480A (en) | 1989-06-16 | 1995-05-02 | Science Incorporated | Fluid delivery apparatus |
US5045871A (en) | 1989-06-30 | 1991-09-03 | Reinholdson Mark R | Disposable camera |
US4973998A (en) | 1990-01-16 | 1990-11-27 | Eastman Kodak Company | Disposable single-use camera and accessory re-usable electronic flash unit |
US5109850A (en) | 1990-02-09 | 1992-05-05 | Massachusetts Institute Of Technology | Automatic blood monitoring for medication delivery method and apparatus |
US5492534A (en) | 1990-04-02 | 1996-02-20 | Pharmetrix Corporation | Controlled release portable pump |
US5318540A (en) | 1990-04-02 | 1994-06-07 | Pharmetrix Corporation | Controlled release infusion device |
US5007458A (en) | 1990-04-23 | 1991-04-16 | Parker Hannifin Corporation | Poppet diaphragm valve |
US5125415A (en) | 1990-06-19 | 1992-06-30 | Smiths Industries Medical Systems, Inc. | Syringe tip cap with self-sealing filter |
JPH0451966A (en) | 1990-06-19 | 1992-02-20 | Toichi Ishikawa | Medical fluid continuous injector |
US5176662A (en) | 1990-08-23 | 1993-01-05 | Minimed Technologies, Ltd. | Subcutaneous injection set with improved cannula mounting arrangement |
US5242406A (en) | 1990-10-19 | 1993-09-07 | Sil Medics Ltd. | Liquid delivery device particularly useful for delivering drugs |
US5245447A (en) | 1991-05-20 | 1993-09-14 | Xerox Corporation | Indexing mechanism for compact scanner |
US5213483A (en) | 1991-06-19 | 1993-05-25 | Strato Medical Corporation | Peristaltic infusion pump with removable cassette and mechanically keyed tube set |
US5207645A (en) | 1991-06-25 | 1993-05-04 | Medication Delivery Devices | Infusion pump, treatment fluid bag therefor, and method for the use thereof |
US5239326A (en) | 1991-08-07 | 1993-08-24 | Kabushiki Kaisha Senshukai | Film-loaded disposable camera |
US5179609A (en) * | 1991-08-30 | 1993-01-12 | At&T Bell Laboratories | Optical assembly including fiber attachment |
DE4129271C1 (en) | 1991-09-03 | 1992-09-17 | Fresenius Ag, 6380 Bad Homburg, De | |
US5244463A (en) | 1991-12-06 | 1993-09-14 | Block Medical, Inc. | Programmable infusion pump |
US5911716A (en) * | 1992-01-24 | 1999-06-15 | I-Flow Corporation | Platen pump |
US5267956A (en) | 1992-02-05 | 1993-12-07 | Alcon Surgical, Inc. | Surgical cassette |
US5346476A (en) | 1992-04-29 | 1994-09-13 | Edward E. Elson | Fluid delivery system |
IE930532A1 (en) * | 1993-07-19 | 1995-01-25 | Elan Med Tech | Liquid material dispenser and valve |
US5254096A (en) | 1992-09-23 | 1993-10-19 | Becton, Dickinson And Company | Syringe pump with graphical display or error conditions |
US5232439A (en) | 1992-11-02 | 1993-08-03 | Infusion Technologies Corporation | Method for pumping fluid from a flexible, variable geometry reservoir |
US5342313A (en) | 1992-11-02 | 1994-08-30 | Infusion Technologies Corporation | Fluid pump for a flexible, variable geometry reservoir |
US5433710A (en) | 1993-03-16 | 1995-07-18 | Minimed, Inc. | Medication infusion pump with fluoropolymer valve seat |
DE4310808C2 (en) * | 1993-04-02 | 1995-06-22 | Boehringer Mannheim Gmbh | Liquid dosing system |
US5257980A (en) | 1993-04-05 | 1993-11-02 | Minimed Technologies, Ltd. | Subcutaneous injection set with crimp-free soft cannula |
EP1129739B1 (en) | 1993-10-04 | 2008-08-13 | Research International, Inc. | Micromachined filters |
JP3259267B2 (en) | 1993-12-28 | 2002-02-25 | ニプロ株式会社 | Chemical injection device |
FR2716286A1 (en) * | 1994-02-16 | 1995-08-18 | Debiotech Sa | Installation of remote monitoring of controllable equipment. |
US5643213A (en) | 1994-03-09 | 1997-07-01 | I-Flow Corporation | Elastomeric syringe actuation device |
US5630710A (en) | 1994-03-09 | 1997-05-20 | Baxter International Inc. | Ambulatory infusion pump |
DE4415896A1 (en) | 1994-05-05 | 1995-11-09 | Boehringer Mannheim Gmbh | Analysis system for monitoring the concentration of an analyte in the blood of a patient |
US5576781A (en) | 1994-05-16 | 1996-11-19 | Deleeuw; Paul | Disposable camera |
US5452033A (en) | 1994-06-06 | 1995-09-19 | Eastman Kodak Company | Single use photographic film package and camera |
US5582593A (en) | 1994-07-21 | 1996-12-10 | Hultman; Barry W. | Ambulatory medication delivery system |
JPH0858897A (en) * | 1994-08-12 | 1996-03-05 | Japan Storage Battery Co Ltd | Fluid supply device |
US5505709A (en) | 1994-09-15 | 1996-04-09 | Minimed, Inc., A Delaware Corporation | Mated infusion pump and syringe |
US5545152A (en) | 1994-10-28 | 1996-08-13 | Minimed Inc. | Quick-connect coupling for a medication infusion system |
DE19500529C5 (en) | 1995-01-11 | 2007-11-22 | Dräger Medical AG & Co. KG | Control unit for a ventilator |
US5637095A (en) | 1995-01-13 | 1997-06-10 | Minimed Inc. | Medication infusion pump with flexible drive plunger |
US5665070A (en) | 1995-01-19 | 1997-09-09 | I-Flow Corporation | Infusion pump with magnetic bag compression |
US5741228A (en) * | 1995-02-17 | 1998-04-21 | Strato/Infusaid | Implantable access device |
US5647853A (en) | 1995-03-03 | 1997-07-15 | Minimed Inc. | Rapid response occlusion detector for a medication infusion pump |
US5575770A (en) | 1995-04-05 | 1996-11-19 | Therex Corporation | Implantable drug infusion system with safe bolus capability |
US5665065A (en) | 1995-05-26 | 1997-09-09 | Minimed Inc. | Medication infusion device with blood glucose data input |
US5584813A (en) | 1995-06-07 | 1996-12-17 | Minimed Inc. | Subcutaneous injection set |
US5573342A (en) | 1995-06-20 | 1996-11-12 | Patalano; Christine S. | Body lotion applicator system |
EP0763369B1 (en) * | 1995-09-18 | 2002-01-09 | Becton, Dickinson and Company | Needle shield with collapsible cover |
US5726751A (en) * | 1995-09-27 | 1998-03-10 | University Of Washington | Silicon microchannel optical flow cytometer |
US5776103A (en) * | 1995-10-11 | 1998-07-07 | Science Incorporated | Fluid delivery device with bolus injection site |
US5779676A (en) * | 1995-10-11 | 1998-07-14 | Science Incorporated | Fluid delivery device with bolus injection site |
ATE242020T1 (en) * | 1996-03-14 | 2003-06-15 | Oneil Christine | PATIENT-CONTROLLED FLOW REGULATION FOR A MEDICATION DELIVERY SYSTEM |
US5865806A (en) * | 1996-04-04 | 1999-02-02 | Becton Dickinson And Company | One step catheter advancement automatic needle retraction system |
GB9608505D0 (en) * | 1996-04-25 | 1996-07-03 | Zeneca Ltd | Compositions processes and uses |
US5976109A (en) * | 1996-04-30 | 1999-11-02 | Medtronic, Inc. | Apparatus for drug infusion implanted within a living body |
US5785688A (en) * | 1996-05-07 | 1998-07-28 | Ceramatec, Inc. | Fluid delivery apparatus and method |
US5726404A (en) * | 1996-05-31 | 1998-03-10 | University Of Washington | Valveless liquid microswitch |
US5886647A (en) * | 1996-12-20 | 1999-03-23 | Badger; Berkley C. | Apparatus and method for wireless, remote control of multiple devices |
US5858239A (en) * | 1997-02-14 | 1999-01-12 | Aksys, Ltd. | Methods and apparatus for adjustment of blood drip chamber of dialysis machines using touchscreen interface |
US5785681A (en) * | 1997-02-25 | 1998-07-28 | Minimed Inc. | Flow rate controller for a medication infusion pump |
US6061580A (en) * | 1997-02-28 | 2000-05-09 | Randice-Lisa Altschul | Disposable wireless telephone and method for call-out only |
US5875393A (en) * | 1997-02-28 | 1999-02-23 | Randice-Lisa Altschul | Disposable wireless telephone and method |
US5871470A (en) * | 1997-04-18 | 1999-02-16 | Becton Dickinson And Company | Combined spinal epidural needle set |
GB2325026B (en) * | 1997-05-07 | 1999-03-10 | Yu Lin Huang | A slurry supplying mechanism |
US5858005A (en) * | 1997-08-27 | 1999-01-12 | Science Incorporated | Subcutaneous infusion set with dynamic needle |
US5961492A (en) * | 1997-08-27 | 1999-10-05 | Science Incorporated | Fluid delivery device with temperature controlled energy source |
US6527744B1 (en) * | 1997-08-27 | 2003-03-04 | Science Incorporated | Fluid delivery device with light activated energy source |
US6019747A (en) * | 1997-10-21 | 2000-02-01 | I-Flow Corporation | Spring-actuated infusion syringe |
US5897530A (en) * | 1997-12-24 | 1999-04-27 | Baxter International Inc. | Enclosed ambulatory pump |
US6244776B1 (en) * | 1998-01-05 | 2001-06-12 | Lien J. Wiley | Applicators for health and beauty products |
US5919167A (en) * | 1998-04-08 | 1999-07-06 | Ferring Pharmaceuticals | Disposable micropump |
US5906597A (en) * | 1998-06-09 | 1999-05-25 | I-Flow Corporation | Patient-controlled drug administration device |
US6375638B2 (en) * | 1999-02-12 | 2002-04-23 | Medtronic Minimed, Inc. | Incremental motion pump mechanisms powered by shape memory alloy wire or the like |
CA2370623C (en) * | 1999-06-08 | 2004-07-20 | Medical Research Group, Inc. | Method and apparatus for infusing liquids using a chemical reaction in an implanted infusion device |
JP2004521667A (en) * | 2000-09-08 | 2004-07-22 | インシュレット コーポレイション | Device, system and method for patient infusion |
US6363609B1 (en) * | 2000-10-20 | 2002-04-02 | Short Block Technologies, Inc. | Method and apparatus for aligning crankshaft sections |
DK1341569T3 (en) * | 2000-11-09 | 2007-05-29 | Insulet Corp | Transcutaneous delivery agent |
KR100407467B1 (en) * | 2001-07-12 | 2003-11-28 | 최수봉 | Insulin pump operated by remote-controller |
US6960192B1 (en) * | 2002-04-23 | 2005-11-01 | Insulet Corporation | Transcutaneous fluid delivery system |
US20040068224A1 (en) * | 2002-10-02 | 2004-04-08 | Couvillon Lucien Alfred | Electroactive polymer actuated medication infusion pumps |
-
2002
- 2002-09-30 US US10/260,192 patent/US7128727B2/en not_active Expired - Fee Related
-
2003
- 2003-09-11 WO PCT/US2003/028769 patent/WO2004030716A2/en not_active Application Discontinuation
- 2003-09-11 EP EP03752335.4A patent/EP1549382B1/en not_active Expired - Lifetime
- 2003-09-11 AU AU2003270629A patent/AU2003270629A1/en not_active Abandoned
-
2006
- 2006-08-25 US US11/467,205 patent/US20060282290A1/en not_active Abandoned
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5569190A (en) * | 1987-06-08 | 1996-10-29 | D'antonio; Nicholas F. | Hypodermic fluid dispenser |
US6126637A (en) * | 1998-04-15 | 2000-10-03 | Science Incorporated | Fluid delivery device with collapsible needle cover |
US6478771B1 (en) * | 1998-11-13 | 2002-11-12 | Elan Pharma International Limited | Drug delivery systems and methods |
US7128727B2 (en) * | 2002-09-30 | 2006-10-31 | Flaherty J Christopher | Components and methods for patient infusion device |
Cited By (319)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8034026B2 (en) | 2001-05-18 | 2011-10-11 | Deka Products Limited Partnership | Infusion pump assembly |
US9173996B2 (en) | 2001-05-18 | 2015-11-03 | Deka Products Limited Partnership | Infusion set for a fluid pump |
US7993108B2 (en) | 2002-10-09 | 2011-08-09 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
US20100114029A1 (en) * | 2002-10-09 | 2010-05-06 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US20100049133A1 (en) * | 2002-10-09 | 2010-02-25 | Abbott Diabetes Care, Inc. | Device and method employing shape memory alloy |
US8343093B2 (en) | 2002-10-09 | 2013-01-01 | Abbott Diabetes Care Inc. | Fluid delivery device with autocalibration |
US20100008794A1 (en) * | 2002-10-09 | 2010-01-14 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US8029245B2 (en) | 2002-10-09 | 2011-10-04 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
US20100049132A1 (en) * | 2002-10-09 | 2010-02-25 | Abbott Diabetes Care, Inc. | Device and method employing shape memory alloy |
US20100049131A1 (en) * | 2002-10-09 | 2010-02-25 | Abbott Diabetes Care, Inc. | Device and method employing shape memory alloy |
US20100057038A1 (en) * | 2002-10-09 | 2010-03-04 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US20100057007A1 (en) * | 2002-10-09 | 2010-03-04 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US20100063446A1 (en) * | 2002-10-09 | 2010-03-11 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US20100068072A1 (en) * | 2002-10-09 | 2010-03-18 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US20100076371A1 (en) * | 2002-10-09 | 2010-03-25 | Abbott Diabetes Care, Inc. | Device and method employing shape memory alloy |
US8727745B2 (en) | 2002-10-09 | 2014-05-20 | Abbott Diabetes Care, Inc. | Device and method employing shape memory alloy |
US8172800B2 (en) | 2002-10-09 | 2012-05-08 | Abbott Diabetes Care, Inc. | Device and method employing shape memory alloy |
US20100100041A1 (en) * | 2002-10-09 | 2010-04-22 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US20100100042A1 (en) * | 2002-10-09 | 2010-04-22 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US20100114028A1 (en) * | 2002-10-09 | 2010-05-06 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US20100114073A1 (en) * | 2002-10-09 | 2010-05-06 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US8029250B2 (en) | 2002-10-09 | 2011-10-04 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
US7993109B2 (en) | 2002-10-09 | 2011-08-09 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
US7727181B2 (en) | 2002-10-09 | 2010-06-01 | Abbott Diabetes Care Inc. | Fluid delivery device with autocalibration |
US8083718B2 (en) | 2002-10-09 | 2011-12-27 | Abbott Diabetes Care Inc. | Device and method employing shape memory alloy |
US20100241076A1 (en) * | 2002-10-09 | 2010-09-23 | Abbott Diabetes Care, Inc. | Device and Method Employing Shape Memory Alloy |
US8079984B2 (en) | 2002-10-09 | 2011-12-20 | Abbott Diabetes Care Inc. | Device and method employing shape memory alloy |
US8079983B2 (en) | 2002-10-09 | 2011-12-20 | Abbott Diabetes Care Inc. | Device and method employing shape memory alloy |
US8075527B2 (en) | 2002-10-09 | 2011-12-13 | Abbott Diabetes Care Inc. | Device and method employing shape memory alloy |
US7922458B2 (en) | 2002-10-09 | 2011-04-12 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
US8066665B2 (en) | 2002-10-09 | 2011-11-29 | Abbott Diabetes Care Inc. | Device and method employing shape memory alloy |
US7951114B2 (en) | 2002-10-09 | 2011-05-31 | Abbott Diabetes Care Inc. | Device and method employing shape memory alloy |
US8047811B2 (en) | 2002-10-09 | 2011-11-01 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
US7959606B2 (en) | 2002-10-09 | 2011-06-14 | Abbott Diabetes Care Inc. | Device and method employing shape memory alloy |
US8047812B2 (en) | 2002-10-09 | 2011-11-01 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
US8512246B2 (en) | 2003-04-28 | 2013-08-20 | Abbott Diabetes Care Inc. | Method and apparatus for providing peak detection circuitry for data communication systems |
US8460243B2 (en) | 2003-06-10 | 2013-06-11 | Abbott Diabetes Care Inc. | Glucose measuring module and insulin pump combination |
US7722536B2 (en) | 2003-07-15 | 2010-05-25 | Abbott Diabetes Care Inc. | Glucose measuring device integrated into a holster for a personal area network device |
US8029443B2 (en) | 2003-07-15 | 2011-10-04 | Abbott Diabetes Care Inc. | Glucose measuring device integrated into a holster for a personal area network device |
US10963417B2 (en) | 2004-06-04 | 2021-03-30 | Abbott Diabetes Care Inc. | Systems and methods for managing diabetes care data |
US12056079B2 (en) | 2004-06-04 | 2024-08-06 | Abbott Diabetes Care Inc. | Systems and methods for managing diabetes care data |
US11507530B2 (en) | 2004-06-04 | 2022-11-22 | Abbott Diabetes Care Inc. | Systems and methods for managing diabetes care data |
US11182332B2 (en) | 2004-06-04 | 2021-11-23 | Abbott Diabetes Care Inc. | Systems and methods for managing diabetes care data |
US8542122B2 (en) | 2005-02-08 | 2013-09-24 | Abbott Diabetes Care Inc. | Glucose measurement device and methods using RFID |
US8223021B2 (en) | 2005-02-08 | 2012-07-17 | Abbott Diabetes Care Inc. | RF tag on test strips, test strip vials and boxes |
US8115635B2 (en) | 2005-02-08 | 2012-02-14 | Abbott Diabetes Care Inc. | RF tag on test strips, test strip vials and boxes |
US8358210B2 (en) | 2005-02-08 | 2013-01-22 | Abbott Diabetes Care Inc. | RF tag on test strips, test strip vials and boxes |
US8390455B2 (en) | 2005-02-08 | 2013-03-05 | Abbott Diabetes Care Inc. | RF tag on test strips, test strip vials and boxes |
US8029460B2 (en) | 2005-03-21 | 2011-10-04 | Abbott Diabetes Care Inc. | Method and system for providing integrated medication infusion and analyte monitoring system |
US8029459B2 (en) | 2005-03-21 | 2011-10-04 | Abbott Diabetes Care Inc. | Method and system for providing integrated medication infusion and analyte monitoring system |
US8343092B2 (en) | 2005-03-21 | 2013-01-01 | Abbott Diabetes Care Inc. | Method and system for providing integrated medication infusion and analyte monitoring system |
US10220143B2 (en) | 2005-05-06 | 2019-03-05 | Medtronic Minimed, Inc. | Infusion device with base portion and durable portion |
US7641649B2 (en) * | 2005-05-06 | 2010-01-05 | Medtronic Minimed, Inc. | Reservoir support and method for infusion device |
US7569050B2 (en) * | 2005-05-06 | 2009-08-04 | Medtronic Minimed, Inc. | Infusion device and method with drive device in infusion device and method with drive device in separable durable housing portion |
US9233203B2 (en) | 2005-05-06 | 2016-01-12 | Medtronic Minimed, Inc. | Medical needles for damping motion |
US9180248B2 (en) | 2005-05-06 | 2015-11-10 | Medtronic Minimed, Inc. | Infusion device with base portion and durable portion |
US20080009824A1 (en) * | 2005-05-06 | 2008-01-10 | Medtronic Minimed, Inc. | Pump assembly and method for infusion device |
US7699833B2 (en) | 2005-05-06 | 2010-04-20 | Moberg Sheldon B | Pump assembly and method for infusion device |
US11141530B2 (en) | 2005-05-06 | 2021-10-12 | Medtronic Minimed, Inc. | Infusion device with base portion and durable portion |
US7935085B2 (en) | 2005-05-06 | 2011-05-03 | Medtronic Minimed, Inc. | Infusion device and method with disposable portion |
US20060264889A1 (en) * | 2005-05-06 | 2006-11-23 | Medtronic Minimed, Inc. | Infusion device and method with drive device in infusion device and method with drive device in separable durable housing portion |
US7686787B2 (en) | 2005-05-06 | 2010-03-30 | Medtronic Minimed, Inc. | Infusion device and method with disposable portion |
US7955305B2 (en) | 2005-05-06 | 2011-06-07 | Medtronic Minimed, Inc. | Needle inserter and method for infusion device |
US20060253086A1 (en) * | 2005-05-06 | 2006-11-09 | Medtronic Minimed, Inc. | Medical needles for damping motion |
US9750440B2 (en) | 2005-05-17 | 2017-09-05 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US9332944B2 (en) | 2005-05-17 | 2016-05-10 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US8653977B2 (en) | 2005-05-17 | 2014-02-18 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US8089363B2 (en) | 2005-05-17 | 2012-01-03 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US7768408B2 (en) | 2005-05-17 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US7884729B2 (en) | 2005-05-17 | 2011-02-08 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US10206611B2 (en) | 2005-05-17 | 2019-02-19 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US8471714B2 (en) | 2005-05-17 | 2013-06-25 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US8112138B2 (en) | 2005-06-03 | 2012-02-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing rechargeable power in data monitoring and management systems |
US8638220B2 (en) | 2005-10-31 | 2014-01-28 | Abbott Diabetes Care Inc. | Method and apparatus for providing data communication in data monitoring and management systems |
US8344966B2 (en) | 2006-01-31 | 2013-01-01 | Abbott Diabetes Care Inc. | Method and system for providing a fault tolerant display unit in an electronic device |
US11890448B2 (en) | 2006-02-09 | 2024-02-06 | Deka Products Limited Partnership | Method and system for shape-memory alloy wire control |
US11413391B2 (en) | 2006-02-09 | 2022-08-16 | Deka Products Limited Partnership | Patch-sized fluid delivery systems and methods |
US11738139B2 (en) | 2006-02-09 | 2023-08-29 | Deka Products Limited Partnership | Patch-sized fluid delivery systems and methods |
US12070574B2 (en) | 2006-02-09 | 2024-08-27 | Deka Products Limited Partnership | Apparatus, systems and methods for an infusion pump assembly |
US11717609B2 (en) | 2006-02-09 | 2023-08-08 | Deka Products Limited Partnership | Adhesive and peripheral systems and methods for medical devices |
US8414522B2 (en) | 2006-02-09 | 2013-04-09 | Deka Products Limited Partnership | Fluid delivery systems and methods |
US11712513B2 (en) | 2006-02-09 | 2023-08-01 | Deka Products Limited Partnership | Adhesive and peripheral systems and methods for medical devices |
US12064590B2 (en) | 2006-02-09 | 2024-08-20 | Deka Products Limited Partnership | Patch-sized fluid delivery systems and methods |
US12036387B2 (en) | 2006-02-09 | 2024-07-16 | Deka Products Limited Partnership | Device to determine volume of fluid dispensed |
US11844926B2 (en) | 2006-02-09 | 2023-12-19 | Deka Products Limited Partnership | Adhesive and peripheral systems and methods for medical devices |
US11690952B2 (en) | 2006-02-09 | 2023-07-04 | Deka Products Limited Partnership | Pumping fluid delivery systems and methods using force application assembly |
US8545445B2 (en) | 2006-02-09 | 2013-10-01 | Deka Products Limited Partnership | Patch-sized fluid delivery systems and methods |
US11617826B2 (en) | 2006-02-09 | 2023-04-04 | Deka Products Limited Partnership | Patch-sized fluid delivery systems and methods |
US11559625B2 (en) | 2006-02-09 | 2023-01-24 | Deka Products Limited Partnership | Patch-sized fluid delivery systems and methods |
US11534543B2 (en) | 2006-02-09 | 2022-12-27 | Deka Products Limited Partnership | Method for making patch-sized fluid delivery systems |
US11992650B2 (en) | 2006-02-09 | 2024-05-28 | Deka Products Limited Partnership | Adhesive and peripheral systems and methods for medical devices |
US8585377B2 (en) | 2006-02-09 | 2013-11-19 | Deka Products Limited Partnership | Pumping fluid delivery systems and methods using force application assembly |
US11904134B2 (en) | 2006-02-09 | 2024-02-20 | Deka Products Limited Partnership | Patch-sized fluid delivery systems and methods |
US8113244B2 (en) | 2006-02-09 | 2012-02-14 | Deka Products Limited Partnership | Adhesive and peripheral systems and methods for medical devices |
US11339774B2 (en) | 2006-02-09 | 2022-05-24 | Deka Products Limited Partnership | Adhesive and peripheral systems and methods for medical devices |
US11364335B2 (en) | 2006-02-09 | 2022-06-21 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US11497846B2 (en) | 2006-02-09 | 2022-11-15 | Deka Products Limited Partnership | Patch-sized fluid delivery systems and methods |
US11491273B2 (en) | 2006-02-09 | 2022-11-08 | Deka Products Limited Partnership | Adhesive and peripheral systems and methods for medical devices |
US11478623B2 (en) | 2006-02-09 | 2022-10-25 | Deka Products Limited Partnership | Infusion pump assembly |
US11391273B2 (en) | 2006-02-09 | 2022-07-19 | Deka Products Limited Partnership | Adhesive and peripheral systems and methods for medical devices |
US11964126B2 (en) | 2006-02-09 | 2024-04-23 | Deka Products Limited Partnership | Infusion pump assembly |
US11395877B2 (en) | 2006-02-09 | 2022-07-26 | Deka Products Limited Partnership | Systems and methods for fluid delivery |
US11426512B2 (en) | 2006-02-09 | 2022-08-30 | Deka Products Limited Partnership | Apparatus, systems and methods for an infusion pump assembly |
US11786651B2 (en) | 2006-02-09 | 2023-10-17 | Deka Products Limited Partnership | Patch-sized fluid delivery system |
US11408414B2 (en) | 2006-02-09 | 2022-08-09 | Deka Products Limited Partnership | Adhesive and peripheral systems and methods for medical devices |
US11406753B2 (en) | 2006-02-09 | 2022-08-09 | Deka Products Limited Partnership | Adhesive and peripheral systems and methods for medical devices |
US10448834B2 (en) | 2006-02-28 | 2019-10-22 | Abbott Diabetes Care Inc. | Smart messages and alerts for an infusion delivery and management system |
US9782076B2 (en) | 2006-02-28 | 2017-10-10 | Abbott Diabetes Care Inc. | Smart messages and alerts for an infusion delivery and management system |
US7981034B2 (en) | 2006-02-28 | 2011-07-19 | Abbott Diabetes Care Inc. | Smart messages and alerts for an infusion delivery and management system |
US10220145B2 (en) | 2006-06-30 | 2019-03-05 | Abbott Diabetes Care Inc. | Integrated analyte sensor and infusion device and methods therefor |
US9119582B2 (en) | 2006-06-30 | 2015-09-01 | Abbott Diabetes Care, Inc. | Integrated analyte sensor and infusion device and methods therefor |
US8512244B2 (en) | 2006-06-30 | 2013-08-20 | Abbott Diabetes Care Inc. | Integrated analyte sensor and infusion device and methods therefor |
US11918782B2 (en) | 2006-06-30 | 2024-03-05 | Abbott Diabetes Care Inc. | Integrated analyte sensor and infusion device and methods therefor |
US11445910B2 (en) | 2006-08-07 | 2022-09-20 | Abbott Diabetes Care Inc. | Method and system for providing data management in integrated analyte monitoring and infusion system |
US10206629B2 (en) | 2006-08-07 | 2019-02-19 | Abbott Diabetes Care Inc. | Method and system for providing integrated analyte monitoring and infusion system therapy management |
US9697332B2 (en) | 2006-08-07 | 2017-07-04 | Abbott Diabetes Care Inc. | Method and system for providing data management in integrated analyte monitoring and infusion system |
US8727982B2 (en) | 2006-08-07 | 2014-05-20 | Abbott Diabetes Care Inc. | Method and system for providing integrated analyte monitoring and infusion system therapy management |
US11967408B2 (en) | 2006-08-07 | 2024-04-23 | Abbott Diabetes Care Inc. | Method and system for providing integrated analyte monitoring and infusion system therapy management |
US8206296B2 (en) | 2006-08-07 | 2012-06-26 | Abbott Diabetes Care Inc. | Method and system for providing integrated analyte monitoring and infusion system therapy management |
US11806110B2 (en) | 2006-08-07 | 2023-11-07 | Abbott Diabetes Care Inc. | Method and system for providing data management in integrated analyte monitoring and infusion system |
US8932216B2 (en) | 2006-08-07 | 2015-01-13 | Abbott Diabetes Care Inc. | Method and system for providing data management in integrated analyte monitoring and infusion system |
US8202267B2 (en) | 2006-10-10 | 2012-06-19 | Medsolve Technologies, Inc. | Method and apparatus for infusing liquid to a body |
US9064107B2 (en) | 2006-10-31 | 2015-06-23 | Abbott Diabetes Care Inc. | Infusion devices and methods |
US11837358B2 (en) | 2006-10-31 | 2023-12-05 | Abbott Diabetes Care Inc. | Infusion devices and methods |
US8579853B2 (en) | 2006-10-31 | 2013-11-12 | Abbott Diabetes Care Inc. | Infusion devices and methods |
US10007759B2 (en) | 2006-10-31 | 2018-06-26 | Abbott Diabetes Care Inc. | Infusion devices and methods |
US11043300B2 (en) | 2006-10-31 | 2021-06-22 | Abbott Diabetes Care Inc. | Infusion devices and methods |
US12073941B2 (en) | 2006-10-31 | 2024-08-27 | Abbott Diabetes Care Inc. | Infusion device and methods |
US11508476B2 (en) | 2006-10-31 | 2022-11-22 | Abbott Diabetes Care, Inc. | Infusion devices and methods |
US8496646B2 (en) | 2007-02-09 | 2013-07-30 | Deka Products Limited Partnership | Infusion pump assembly |
US8641618B2 (en) | 2007-06-27 | 2014-02-04 | Abbott Diabetes Care Inc. | Method and structure for securing a monitoring device element |
US8502682B2 (en) | 2007-06-28 | 2013-08-06 | Abbott Diabetes Care Inc. | Signal converting cradle for medical condition monitoring and management system |
US8085151B2 (en) | 2007-06-28 | 2011-12-27 | Abbott Diabetes Care Inc. | Signal converting cradle for medical condition monitoring and management system |
US9005169B2 (en) | 2007-10-16 | 2015-04-14 | Cequr Sa | Cannula insertion device and related methods |
US9968747B2 (en) | 2007-10-16 | 2018-05-15 | Cequr Sa | Cannula insertion device and related methods |
US20090143732A1 (en) * | 2007-11-29 | 2009-06-04 | Insulet Corporation | Interfacing a prefilled syringe with an infusion pump to fill the infusion pump |
US7918825B2 (en) | 2007-11-29 | 2011-04-05 | Insulet Corporation | Interfacing a prefilled syringe with an infusion pump to fill the infusion pump |
US11404776B2 (en) | 2007-12-31 | 2022-08-02 | Deka Products Limited Partnership | Split ring resonator antenna adapted for use in wirelessly controlled medical device |
US8491570B2 (en) | 2007-12-31 | 2013-07-23 | Deka Products Limited Partnership | Infusion pump assembly |
US8414563B2 (en) | 2007-12-31 | 2013-04-09 | Deka Products Limited Partnership | Pump assembly with switch |
US11701300B2 (en) | 2007-12-31 | 2023-07-18 | Deka Products Limited Partnership | Method for fluid delivery |
US11534542B2 (en) | 2007-12-31 | 2022-12-27 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US11497686B2 (en) | 2007-12-31 | 2022-11-15 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US11642283B2 (en) | 2007-12-31 | 2023-05-09 | Deka Products Limited Partnership | Method for fluid delivery |
US9526830B2 (en) | 2007-12-31 | 2016-12-27 | Deka Products Limited Partnership | Wearable pump assembly |
US11723841B2 (en) | 2007-12-31 | 2023-08-15 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US11894609B2 (en) | 2007-12-31 | 2024-02-06 | Deka Products Limited Partnership | Split ring resonator antenna adapted for use in wirelessly controlled medical device |
US8986253B2 (en) | 2008-01-25 | 2015-03-24 | Tandem Diabetes Care, Inc. | Two chamber pumps and related methods |
US8708961B2 (en) | 2008-01-28 | 2014-04-29 | Medsolve Technologies, Inc. | Apparatus for infusing liquid to a body |
US11865299B2 (en) | 2008-08-20 | 2024-01-09 | Insulet Corporation | Infusion pump systems and methods |
US8408421B2 (en) | 2008-09-16 | 2013-04-02 | Tandem Diabetes Care, Inc. | Flow regulating stopcocks and related methods |
US8448824B2 (en) | 2008-09-16 | 2013-05-28 | Tandem Diabetes Care, Inc. | Slideable flow metering devices and related methods |
US8650937B2 (en) | 2008-09-19 | 2014-02-18 | Tandem Diabetes Care, Inc. | Solute concentration measurement device and related methods |
US8262616B2 (en) | 2008-10-10 | 2012-09-11 | Deka Products Limited Partnership | Infusion pump assembly |
US8223028B2 (en) | 2008-10-10 | 2012-07-17 | Deka Products Limited Partnership | Occlusion detection system and method |
US8016789B2 (en) | 2008-10-10 | 2011-09-13 | Deka Products Limited Partnership | Pump assembly with a removable cover assembly |
US8066672B2 (en) | 2008-10-10 | 2011-11-29 | Deka Products Limited Partnership | Infusion pump assembly with a backup power supply |
US8708376B2 (en) | 2008-10-10 | 2014-04-29 | Deka Products Limited Partnership | Medium connector |
US8267892B2 (en) | 2008-10-10 | 2012-09-18 | Deka Products Limited Partnership | Multi-language / multi-processor infusion pump assembly |
US9180245B2 (en) | 2008-10-10 | 2015-11-10 | Deka Products Limited Partnership | System and method for administering an infusible fluid |
US11839739B2 (en) | 2009-01-12 | 2023-12-12 | Becton, Dickinson And Company | Infusion set and/or patch pump having at least one of an in-dwelling rigid catheter with flexible features and/or a flexible catheter attachment |
US9782536B2 (en) | 2009-01-12 | 2017-10-10 | Becton, Dickinson And Company | Infusion set and/or patch pump having at least one of an in-dwelling rigid catheter with flexible features and/or a flexible catheter attachment |
US11013854B2 (en) | 2009-01-12 | 2021-05-25 | Becton, Dickinson And Company | Infusion set and/or patch pump having at least one of an in-dwelling rigid catheter with flexible features and/or a flexible catheter attachment |
US8560082B2 (en) | 2009-01-30 | 2013-10-15 | Abbott Diabetes Care Inc. | Computerized determination of insulin pump therapy parameters using real time and retrospective data processing |
US8573027B2 (en) | 2009-02-27 | 2013-11-05 | Tandem Diabetes Care, Inc. | Methods and devices for determination of flow reservoir volume |
US9250106B2 (en) | 2009-02-27 | 2016-02-02 | Tandem Diabetes Care, Inc. | Methods and devices for determination of flow reservoir volume |
US8467972B2 (en) | 2009-04-28 | 2013-06-18 | Abbott Diabetes Care Inc. | Closed loop blood glucose control algorithm analysis |
US8939928B2 (en) | 2009-07-23 | 2015-01-27 | Becton, Dickinson And Company | Medical device having capacitive coupling communication and energy harvesting |
US11052190B2 (en) | 2009-07-23 | 2021-07-06 | Becton, Dickinson And Company | Medical device having capacitive coupling communication and energy harvesting |
US8798934B2 (en) | 2009-07-23 | 2014-08-05 | Abbott Diabetes Care Inc. | Real time management of data relating to physiological control of glucose levels |
US9764083B1 (en) | 2009-07-23 | 2017-09-19 | Becton, Dickinson And Company | Medical device having capacitive coupling communication and energy harvesting |
US11951280B2 (en) | 2009-07-23 | 2024-04-09 | Becton, Dickinson And Company | Medical device having capacitive coupling communication and energy harvesting |
US10872102B2 (en) | 2009-07-23 | 2020-12-22 | Abbott Diabetes Care Inc. | Real time management of data relating to physiological control of glucose levels |
US8298184B2 (en) | 2009-07-30 | 2012-10-30 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US12042627B2 (en) | 2009-07-30 | 2024-07-23 | Tandem Diabetes Care, Inc. | Infusion pump systems and methods |
US9211377B2 (en) | 2009-07-30 | 2015-12-15 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US11285263B2 (en) | 2009-07-30 | 2022-03-29 | Tandem Diabetes Care, Inc. | Infusion pump systems and methods |
US8926561B2 (en) | 2009-07-30 | 2015-01-06 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8758323B2 (en) | 2009-07-30 | 2014-06-24 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8287495B2 (en) | 2009-07-30 | 2012-10-16 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US11135362B2 (en) | 2009-07-30 | 2021-10-05 | Tandem Diabetes Care, Inc. | Infusion pump systems and methods |
US20110046558A1 (en) * | 2009-08-18 | 2011-02-24 | Peter Gravesen | Medicine delivery device having detachable pressure sensing unit |
US10226588B2 (en) | 2009-08-18 | 2019-03-12 | Cequr Sa | Methods for detecting failure states in a medicine delivery device |
US9022972B2 (en) | 2009-08-18 | 2015-05-05 | Cequr Sa | Medicine delivery device having detachable pressure sensing unit |
US8547239B2 (en) | 2009-08-18 | 2013-10-01 | Cequr Sa | Methods for detecting failure states in a medicine delivery device |
US9694147B2 (en) | 2009-08-18 | 2017-07-04 | Cequr Sa | Methods for detecting failure states in a medicine delivery device |
US9174009B2 (en) | 2009-08-18 | 2015-11-03 | Cequr Sa | Methods for detecting failure states in a medicine delivery device |
US10300196B2 (en) | 2009-08-18 | 2019-05-28 | Cequr Sa | Medicine delivery device having detachable pressure sensing unit |
US8672873B2 (en) | 2009-08-18 | 2014-03-18 | Cequr Sa | Medicine delivery device having detachable pressure sensing unit |
US9039654B2 (en) | 2009-08-18 | 2015-05-26 | Cequr Sa | Medicine delivery device having detachable pressure sensing unit |
US10092691B2 (en) | 2009-09-02 | 2018-10-09 | Becton, Dickinson And Company | Flexible and conformal patch pump |
US11052189B2 (en) | 2009-09-02 | 2021-07-06 | Becton, Dickinson And Company | Flexible and conformal patch pump |
US11471592B2 (en) | 2009-09-02 | 2022-10-18 | Becton, Dickinson And Company | Extended use medical device |
US11744937B2 (en) | 2009-09-02 | 2023-09-05 | Becton, Dickinson And Company | Flexible and conformal patch pump |
US9375529B2 (en) | 2009-09-02 | 2016-06-28 | Becton, Dickinson And Company | Extended use medical device |
US9750444B2 (en) | 2009-09-30 | 2017-09-05 | Abbott Diabetes Care Inc. | Interconnect for on-body analyte monitoring device |
US11259725B2 (en) | 2009-09-30 | 2022-03-01 | Abbott Diabetes Care Inc. | Interconnect for on-body analyte monitoring device |
US10765351B2 (en) | 2009-09-30 | 2020-09-08 | Abbott Diabetes Care Inc. | Interconnect for on-body analyte monitoring device |
US9381300B2 (en) | 2010-09-24 | 2016-07-05 | Perqflo, Llc | Infusion pumps |
US9308320B2 (en) | 2010-09-24 | 2016-04-12 | Perqflo, Llc | Infusion pumps |
US8915879B2 (en) | 2010-09-24 | 2014-12-23 | Perqflo, Llc | Infusion pumps |
US9498573B2 (en) | 2010-09-24 | 2016-11-22 | Perqflo, Llc | Infusion pumps |
US9320849B2 (en) | 2010-09-24 | 2016-04-26 | Perqflo, Llc | Infusion pumps |
US8430849B2 (en) | 2010-09-24 | 2013-04-30 | Perqflo, Llc | Infusion pumps and plunger pusher position-responsive cartridge lock for infusion pumps |
US8777901B2 (en) | 2010-09-24 | 2014-07-15 | Perqflo, Llc | Infusion pumps |
US11547792B2 (en) | 2010-09-24 | 2023-01-10 | Medtronic Minimed, Inc. | Infusion pumps |
US9216249B2 (en) | 2010-09-24 | 2015-12-22 | Perqflo, Llc | Infusion pumps |
US9750875B2 (en) | 2010-09-24 | 2017-09-05 | Perqflo, Llc | Infusion pumps |
US10272196B2 (en) | 2010-09-24 | 2019-04-30 | Perqflo, Llc | Infusion pumps |
US9211378B2 (en) | 2010-10-22 | 2015-12-15 | Cequr Sa | Methods and systems for dosing a medicament |
US10967124B2 (en) | 2010-11-20 | 2021-04-06 | Medtronic Minimed, Inc. | Infusion pumps |
US8905972B2 (en) | 2010-11-20 | 2014-12-09 | Perqflo, Llc | Infusion pumps |
US10029045B2 (en) | 2010-11-20 | 2018-07-24 | Perqflo, Llc | Infusion pumps |
US8814831B2 (en) | 2010-11-30 | 2014-08-26 | Becton, Dickinson And Company | Ballistic microneedle infusion device |
US9480792B2 (en) | 2010-11-30 | 2016-11-01 | Becton, Dickinson And Company | Ballistic microneedle infusion device |
US9844635B2 (en) * | 2010-11-30 | 2017-12-19 | Becton, Dickinson And Company | Adjustable height needle infusion device |
US20140324017A1 (en) * | 2010-11-30 | 2014-10-30 | Becton, Dickinson And Company | Adjustable Height Needle Infusion Device |
US9950109B2 (en) | 2010-11-30 | 2018-04-24 | Becton, Dickinson And Company | Slide-activated angled inserter and cantilevered ballistic insertion for intradermal drug infusion |
US8795230B2 (en) | 2010-11-30 | 2014-08-05 | Becton, Dickinson And Company | Adjustable height needle infusion device |
US10828418B2 (en) | 2010-11-30 | 2020-11-10 | Becton, Dickinson And Company | Slide-activated angled inserter and cantilevered ballistic insertion for intradermal drug infusion |
US10434285B2 (en) | 2011-02-09 | 2019-10-08 | Becton, Dickinson And Company | Self-contained inserter for drug delivery infusion set |
US11534089B2 (en) | 2011-02-28 | 2022-12-27 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
US9433757B2 (en) | 2011-03-03 | 2016-09-06 | Becton, Dickinson And Company | Compact spring inserter for drug delivery infusion set |
US10625017B2 (en) | 2012-03-05 | 2020-04-21 | Becton, Dickinson And Company | Wireless communication for on-body medical devices |
US9623173B2 (en) | 2012-03-05 | 2017-04-18 | Becton, Dickinson And Company | Wireless communication for on-body medical devices |
US11524151B2 (en) | 2012-03-07 | 2022-12-13 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US10124112B2 (en) | 2012-03-30 | 2018-11-13 | Insulet Corporation | Fluid delivery device and transcutaneous access tool with blood glucose monitoring for use therewith |
EP4201327A1 (en) | 2012-03-30 | 2023-06-28 | Insulet Corporation | Fluid delivery device with transcutaneous access tool, insertion mechanism and blood glucose monitoring for use therewith |
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US10420883B2 (en) | 2012-03-30 | 2019-09-24 | Insulet Corporation | Fluid delivery device, transcutaneous access tool and fluid drive mechanism for use therewith |
WO2013149186A1 (en) | 2012-03-30 | 2013-10-03 | Insulet Corporation | Fluid delivery device with transcutaneous access tool, insertion mechansim and blood glucose monitoring for use therewith |
US10130758B2 (en) | 2012-03-30 | 2018-11-20 | Insulet Corporation | Fluid delivery device, transcutaneous access tool and insertion mechanism for use therewith |
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EP3549524A1 (en) | 2012-03-30 | 2019-10-09 | Insulet Corporation | Fluid delivery device with transcutaneous access tool, insertion mechanism and blood glucose monitoring for use therewith |
US10569011B2 (en) | 2012-03-30 | 2020-02-25 | Insulet Corporation | Fluid delivery device, transcutaneous access tool and insertion mechanism for use therewith |
US11684713B2 (en) | 2012-03-30 | 2023-06-27 | Insulet Corporation | Fluid delivery device, transcutaneous access tool and insertion mechanism for use therewith |
US10258736B2 (en) | 2012-05-17 | 2019-04-16 | Tandem Diabetes Care, Inc. | Systems including vial adapter for fluid transfer |
US11676694B2 (en) | 2012-06-07 | 2023-06-13 | Tandem Diabetes Care, Inc. | Device and method for training users of ambulatory medical devices |
US20140088508A1 (en) * | 2012-09-24 | 2014-03-27 | Patrick Ryan | Drug-delivery devices with integrated needle-insertion mechanism |
US9962486B2 (en) | 2013-03-14 | 2018-05-08 | Tandem Diabetes Care, Inc. | System and method for detecting occlusions in an infusion pump |
US11597541B2 (en) | 2013-07-03 | 2023-03-07 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US12012241B2 (en) | 2013-07-03 | 2024-06-18 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US12064591B2 (en) | 2013-07-19 | 2024-08-20 | Insulet Corporation | Infusion pump system and method |
US11911590B2 (en) | 2013-12-26 | 2024-02-27 | Tandem Diabetes Care, Inc. | Integration of infusion pump with remote electronic device |
US11386996B2 (en) | 2014-01-30 | 2022-07-12 | Insulet Netherlands B.V. | Therapeutic product delivery system and method of pairing |
US10777319B2 (en) | 2014-01-30 | 2020-09-15 | Insulet Netherlands B.V. | Therapeutic product delivery system and method of pairing |
US10441717B2 (en) | 2014-04-15 | 2019-10-15 | Insulet Corporation | Monitoring a physiological parameter associated with tissue of a host to confirm delivery of medication |
EP3804786A1 (en) | 2014-04-15 | 2021-04-14 | Insulet Corporation | Monitoring a physiological parameter associated with tissue of a host to confirm delivery of medication |
US11383034B2 (en) | 2014-04-15 | 2022-07-12 | Insulet Corporation | Monitoring a physiological parameter associated with tissue of a host to confirm delivery of medication |
US10004845B2 (en) | 2014-04-18 | 2018-06-26 | Becton, Dickinson And Company | Split piston metering pump |
US11793929B2 (en) | 2014-04-18 | 2023-10-24 | Becton, Dickinson And Company | Split piston metering pump |
US10512719B2 (en) | 2014-04-18 | 2019-12-24 | Becton, Dickinson And Company | Split piston metering pump |
US9416775B2 (en) | 2014-07-02 | 2016-08-16 | Becton, Dickinson And Company | Internal cam metering pump |
US11464899B2 (en) | 2014-08-28 | 2022-10-11 | Becton, Dickinson And Company | Wireless communication for on-body medical devices |
US10946137B2 (en) | 2014-09-30 | 2021-03-16 | Medtronic Minimed, Inc. | Hybrid ambulatory infusion pumps |
US12070576B2 (en) | 2014-09-30 | 2024-08-27 | Medtronic Minimed, Inc. | Hybrid ambulatory infusion pumps |
US10159786B2 (en) | 2014-09-30 | 2018-12-25 | Perqflo, Llc | Hybrid ambulatory infusion pumps |
US10737024B2 (en) | 2015-02-18 | 2020-08-11 | Insulet Corporation | Fluid delivery and infusion devices, and methods of use thereof |
WO2016134137A1 (en) | 2015-02-18 | 2016-08-25 | Insulet Corporation | Fluid delivery and infusion devices, and methods of use thereof |
EP4400130A2 (en) | 2015-02-18 | 2024-07-17 | Insulet Corporation | Fluid delivery and infusion devices |
US11684712B2 (en) | 2015-02-18 | 2023-06-27 | Medtronic Minimed, Inc. | Ambulatory infusion pumps and reservoir assemblies for use with same |
EP3733227A1 (en) | 2015-02-18 | 2020-11-04 | Insulet Corporation | Fluid delivery and infusion devices |
US10448885B2 (en) | 2015-06-12 | 2019-10-22 | Insulet Corporation | Confirmation of delivery of medication to a host |
US10080841B2 (en) | 2015-11-18 | 2018-09-25 | President And Fellows Of Harvard College | Systems and methods for monitoring, managing, and treating asthma and anaphylaxis |
US10716896B2 (en) | 2015-11-24 | 2020-07-21 | Insulet Corporation | Wearable automated medication delivery system |
US11090434B2 (en) | 2015-11-24 | 2021-08-17 | Insulet Corporation | Automated drug delivery system |
US11744944B2 (en) | 2015-11-24 | 2023-09-05 | Insulet Corporation | Wearable automated medication delivery system |
US11364341B2 (en) | 2015-11-25 | 2022-06-21 | Insulet Corporation | Wearable medication delivery device |
US11929158B2 (en) | 2016-01-13 | 2024-03-12 | Insulet Corporation | User interface for diabetes management system |
US11857763B2 (en) | 2016-01-14 | 2024-01-02 | Insulet Corporation | Adjusting insulin delivery rates |
US11672909B2 (en) | 2016-02-12 | 2023-06-13 | Medtronic Minimed, Inc. | Ambulatory infusion pumps and assemblies for use with same |
US11497856B2 (en) | 2016-08-14 | 2022-11-15 | Insulet Corporation | Drug delivery device with indicator |
US11439765B2 (en) | 2016-08-14 | 2022-09-13 | Insulet Corporation | Variable fill drug delivery device |
US11724027B2 (en) | 2016-09-23 | 2023-08-15 | Insulet Corporation | Fluid delivery device with sensor |
US10751478B2 (en) | 2016-10-07 | 2020-08-25 | Insulet Corporation | Multi-stage delivery system |
US10780217B2 (en) | 2016-11-10 | 2020-09-22 | Insulet Corporation | Ratchet drive for on body delivery system |
US12076160B2 (en) | 2016-12-12 | 2024-09-03 | Insulet Corporation | Alarms and alerts for medication delivery devices and systems |
US11969579B2 (en) | 2017-01-13 | 2024-04-30 | Insulet Corporation | Insulin delivery methods, systems and devices |
US12042630B2 (en) | 2017-01-13 | 2024-07-23 | Insulet Corporation | System and method for adjusting insulin delivery |
US11633541B2 (en) | 2017-01-19 | 2023-04-25 | Insulet Corporation | Cartridge hold-up volume reduction |
US11045603B2 (en) | 2017-02-22 | 2021-06-29 | Insulet Corporation | Needle insertion mechanisms for drug containers |
US11229740B2 (en) | 2017-03-07 | 2022-01-25 | Insulet Corporation | Very high volume user filled drug delivery device |
US10973978B2 (en) | 2017-08-03 | 2021-04-13 | Insulet Corporation | Fluid flow regulation arrangements for drug delivery devices |
US11280327B2 (en) | 2017-08-03 | 2022-03-22 | Insulet Corporation | Micro piston pump |
US11786668B2 (en) | 2017-09-25 | 2023-10-17 | Insulet Corporation | Drug delivery devices, systems, and methods with force transfer elements |
US10898656B2 (en) | 2017-09-26 | 2021-01-26 | Insulet Corporation | Needle mechanism module for drug delivery device |
US11147931B2 (en) | 2017-11-17 | 2021-10-19 | Insulet Corporation | Drug delivery device with air and backflow elimination |
USD1020794S1 (en) | 2018-04-02 | 2024-04-02 | Bigfoot Biomedical, Inc. | Medication delivery device with icons |
US11523972B2 (en) | 2018-04-24 | 2022-12-13 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US11565043B2 (en) | 2018-05-04 | 2023-01-31 | Insulet Corporation | Safety constraints for a control algorithm based drug delivery system |
US12090301B2 (en) | 2018-05-04 | 2024-09-17 | Insulet Corporation | Safety constraints for a control algorithm based drug delivery system |
US10874803B2 (en) | 2018-05-31 | 2020-12-29 | Insulet Corporation | Drug cartridge with drive system |
US11458250B2 (en) | 2018-05-31 | 2022-10-04 | Insulet Corporation | System and techniques for drug reservoir volume detection |
US11229736B2 (en) | 2018-06-06 | 2022-01-25 | Insulet Corporation | Linear shuttle pump for drug delivery |
US11992653B2 (en) | 2018-07-18 | 2024-05-28 | Insulet Corporation | Drug delivery insertion apparatuses and system |
US11241532B2 (en) | 2018-08-29 | 2022-02-08 | Insulet Corporation | Drug delivery system with sensor having optimized communication and infusion site |
US11628251B2 (en) | 2018-09-28 | 2023-04-18 | Insulet Corporation | Activity mode for artificial pancreas system |
US11565039B2 (en) | 2018-10-11 | 2023-01-31 | Insulet Corporation | Event detection for drug delivery system |
WO2020097552A1 (en) * | 2018-11-08 | 2020-05-14 | Capillary Biomedical, Inc | Linear insertion device with rotational drive |
US11446435B2 (en) | 2018-11-28 | 2022-09-20 | Insulet Corporation | Drug delivery shuttle pump system and valve assembly |
USD1024090S1 (en) | 2019-01-09 | 2024-04-23 | Bigfoot Biomedical, Inc. | Display screen or portion thereof with graphical user interface associated with insulin delivery |
US11801344B2 (en) | 2019-09-13 | 2023-10-31 | Insulet Corporation | Blood glucose rate of change modulation of meal and correction insulin bolus quantity |
US11935637B2 (en) | 2019-09-27 | 2024-03-19 | Insulet Corporation | Onboarding and total daily insulin adaptivity |
US11369735B2 (en) | 2019-11-05 | 2022-06-28 | Insulet Corporation | Component positioning of a linear shuttle pump |
US11957875B2 (en) | 2019-12-06 | 2024-04-16 | Insulet Corporation | Techniques and devices providing adaptivity and personalization in diabetes treatment |
US11833329B2 (en) | 2019-12-20 | 2023-12-05 | Insulet Corporation | Techniques for improved automatic drug delivery performance using delivery tendencies from past delivery history and use patterns |
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US11607493B2 (en) | 2020-04-06 | 2023-03-21 | Insulet Corporation | Initial total daily insulin setting for user onboarding |
US11684716B2 (en) | 2020-07-31 | 2023-06-27 | Insulet Corporation | Techniques to reduce risk of occlusions in drug delivery systems |
US12097353B2 (en) | 2021-02-25 | 2024-09-24 | Medtronic Minimed, Inc. | Infusion pumps |
US11904140B2 (en) | 2021-03-10 | 2024-02-20 | Insulet Corporation | Adaptable asymmetric medicament cost component in a control system for medicament delivery |
US12090498B2 (en) | 2021-08-19 | 2024-09-17 | Insulet Corporation | Low-friction rolling plunger for a wearable drug delivery device |
US11738144B2 (en) | 2021-09-27 | 2023-08-29 | Insulet Corporation | Techniques enabling adaptation of parameters in aid systems by user input |
US11439754B1 (en) | 2021-12-01 | 2022-09-13 | Insulet Corporation | Optimizing embedded formulations for drug delivery |
US12097355B2 (en) | 2023-12-20 | 2024-09-24 | Insulet Corporation | Automatically or manually initiated meal bolus delivery with subsequent automatic safety constraint relaxation |
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EP1549382A2 (en) | 2005-07-06 |
US7128727B2 (en) | 2006-10-31 |
EP1549382A4 (en) | 2014-12-31 |
US20040064096A1 (en) | 2004-04-01 |
EP1549382B1 (en) | 2016-03-16 |
WO2004030716A2 (en) | 2004-04-15 |
AU2003270629A1 (en) | 2004-04-23 |
AU2003270629A8 (en) | 2004-04-23 |
WO2004030716A3 (en) | 2004-08-12 |
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