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WO2018177765A1 - Pompe de nutrition à réglage de nuit - Google Patents

Pompe de nutrition à réglage de nuit Download PDF

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Publication number
WO2018177765A1
WO2018177765A1 PCT/EP2018/056559 EP2018056559W WO2018177765A1 WO 2018177765 A1 WO2018177765 A1 WO 2018177765A1 EP 2018056559 W EP2018056559 W EP 2018056559W WO 2018177765 A1 WO2018177765 A1 WO 2018177765A1
Authority
WO
WIPO (PCT)
Prior art keywords
pump
duty cycle
mode
delivery
silent
Prior art date
Application number
PCT/EP2018/056559
Other languages
English (en)
Inventor
Benjamin DORION
Eric Johnson
Steven Bernard
Michael Reuben JEDWAB
Original Assignee
Axium Mtech SA
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Axium Mtech SA filed Critical Axium Mtech SA
Publication of WO2018177765A1 publication Critical patent/WO2018177765A1/fr

Links

Classifications

    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61J—CONTAINERS SPECIALLY ADAPTED FOR MEDICAL OR PHARMACEUTICAL PURPOSES; DEVICES OR METHODS SPECIALLY ADAPTED FOR BRINGING PHARMACEUTICAL PRODUCTS INTO PARTICULAR PHYSICAL OR ADMINISTERING FORMS; DEVICES FOR ADMINISTERING FOOD OR MEDICINES ORALLY; BABY COMFORTERS; DEVICES FOR RECEIVING SPITTLE
    • A61J15/00—Feeding-tubes for therapeutic purposes
    • A61J15/0026—Parts, details or accessories for feeding-tubes
    • A61J15/0076—Feeding pumps
    • 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
    • A61M2005/14506—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons mechanically driven, e.g. spring or 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
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/10—General characteristics of the apparatus with powered movement mechanisms
    • 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
    • A61M2205/42—Reducing noise

Definitions

  • the present disclosure relates generally to devices and methods for incorporating a nighttime setting for systems and pumps used to administer multiple fluids such as enteral feeding solutions. More specifically, the present disclosure is directed to a system and method for improving the user experience for pumps that are operated nocturnally.
  • an infusion set can provide an enteral solution containing nutrition and optional medication to the patient.
  • the infusion set can be used with a pump (e.g., a peristaltic pump) to regulate the amount and the rate at which the enteral solution is delivered from a reservoir to the patient.
  • a pump e.g., a peristaltic pump
  • the amount of enteral solution administered to the patient must be precisely controlled, especially if the enteral solution contains potent compounds.
  • the engagement of the tube to a peristaltic pump controls the flow of fluid to the patient according to the speed of the peristaltic pump.
  • Certain patients and patient settings require continuous enteral nutrition, which can be delivered according to a prescription.
  • Current systems drive the prescriptions according to a set flow rate and a set period of time to achieve a desired total volume delivered.
  • the prescriptions involve running the pump for an extended duration, spanning an entire day and night at a time. Due to the extended time period required to achieve continuous feeding, many prescriptions typically require nocturnal pumping. With nighttime pumping comes a series of additional complications or annoyances to be rectified that are not typically problems when nutrition deliveries occur with near a non-sleeping patient nearby.
  • the present disclosure provides a continuous or intermittent enteral nutrition delivery system that includes a night-time setting to quiet extraneous noises from the pump to benefit the experience of the patient during sleeping hours.
  • pumps used for delivering nutrition cause undesirable noises when operating in different typical settings.
  • the causes of pump operation noise differ based upon the type of pump, the nutrition prescription, and whether the pump is operating on a battery or connected to AC mains voltage.
  • Various embodiments include a pump system for delivering an enteral nutrition composition in a delivery session, the pump system comprising a pump, an input device, a controller, a memory device and a processor.
  • the processor is configured to execute instructions stored on the memory device to cause the controller to enable a user to input a prescription for the delivery session and select a silent operating mode via the input device.
  • pump system is configured to calculate a silent mode duty cycle profile to achieve a first desired flow rate for the delivery session according to the prescription.
  • the silent mode duty cycle profile is calculated based upon (i) a designated silent operating mode pump speed, and (ii) the first desired flow rate for the delivery session according to the prescription.
  • the pump operates at the designated silent operating mode pump speed according to the silent mode duty cycle profile.
  • Another embodiment includes a pump system for delivering an enteral nutrition composition in a delivery session, the pump system comprising a pump, an input device, a controller, a memory device and a processor.
  • the processor is configured to execute instructions stored on the memory device to cause the controller to enable a user to input a prescription for the delivery session via the input device.
  • the pump is operated at a first pump speed and a first desired flow rate according to the prescription for the delivery session. A user may then select a silent operating mode via the input device.
  • the pump system calculates a duty cycle profile to achieve the first desired flow rate for the delivery session according to the prescription, wherein the duty cycle profile is calculated based upon: (i) a designated silent operating mode pump speed slower than the first pump speed; and (ii) the first desired flow rate for the delivery session according to the prescription.
  • the pump then operates at the designated silent operating mode pump speed according to the second duty cycle profile.
  • Another embodiment includes a pump system for delivering an enteral nutrition composition in a delivery session, the pump system comprising a pump, an input device, a controller, a memory device and a processor.
  • the processor is configured to execute instructions stored on the memory device to cause the controller to enable a user to input a prescription for the delivery session via the input device and calculate a first duty cycle profile to achieve a first desired fiow rate for the delivery session according to the prescription.
  • the first duty cycle profile is calculated based upon (a) a first pump speed, and (b) the first desired flow rate for the delivery session according to the prescription.
  • the pump system operates the pump at the first pump speed according to the first duty cycle profile. The user may then select, via the input device, a silent operating mode of the pump system.
  • the pump system calculates a second duty cycle profile to achieve the first desired flow rate for the delivery session according to the prescription, wherein the second duty cycle profile is calculated based upon: (i) a second pump speed, the second pump speed being slower than the first pump speed; and (ii) the first desired flow rate for the delivery session according to the prescription.
  • the pump operates at the second pump speed according to the second duty cycle profile.
  • FIG. 1 shows a graph illustrating the motor speed vs. time of a nutrition pump of a first delivery embodiment.
  • FIG. 2 shows a graph illustrating the motor speed vs. time of a nutrition pump of a second delivery embodiment.
  • FIG. 3 shows a graph illustrating the applied voltage vs. motor speed of a nutrition pump at a given torque.
  • FIG. 4 shows a graph illustrating the power vs. motor speed of a nutrition pump.
  • FIG. 5 shows a graph illustrating the efficiency vs. motor speed of a nutrition pump.
  • the devices and apparatuses disclosed herein may lack any element that is not specifically disclosed.
  • a disclosure of an embodiment using the term “comprising” includes a disclosure of embodiments “consisting essentially of and “consisting of the components identified.
  • the methods disclosed herein may lack any step that is not specifically disclosed herein.
  • a disclosure of an embodiment using the term “comprising” includes a disclosure of embodiments “consisting essentially of and “consisting of the steps identified.
  • Enteral feeding pumps are devices that control the timing and the amount of nutrition delivered to a patient during enteral feeding.
  • Enteral feeding is the administration of nutrient fluids to a patient who cannot eat via normal ingestion routes.
  • Enteral administration typically occurs through a set of tubes between a feeding bag and a catheter inserted into the patient.
  • a disposable cassette typically carries at least a portion of the tubing so that spent tubing may be easily disposed of.
  • Enteral feeding pumps can operate as part of a stand-alone nutrition delivery system or as part of a larger interconnected network of pumping apparatuses, controllers, servers, and databases.
  • a doctor or clinician provides a prescription for an amount (e.g., volume, calories) and duration of continuous feeding or intermittent feeding regimen based upon the profile of each individual patient.
  • Enteral feeding systems of various embodiments are operable either by being plugged into an AC mains outlet, or alternatively by relying on a battery backup to provide ambulatory functionality. It should be appreciated that having the flexibility of a battery backup is desirable to allow for patient mobility without delivery interruption.
  • any suitable level of AC mains voltage connection is appropriate, including but not limited to 100V, 110V, 115V, 120V, 125V, 127V, 210V, 220V, 230V, 240V, or any other suitable voltage level available.
  • an enteral feeding pump system includes an associated user interface or suitable display device (collectively hereinafter “user interface") that enables interaction between the patient or clinician and the pump system via a suitable associated input device.
  • a user or clinician via the input device and user interface, has the ability to at least program the pump with pumping parameters, input a patient prescription, alter pump parameters based upon setting, time of day, prescription, and personal preference, and monitor a continuous or intermittent enteral feeding pump delivery. It should be appreciated that such pump programming inputs may be achieved remotely according to known remote programming methods, as well as locally using an associated input device.
  • an associated mobile device may be paired to the pump to allow user interaction.
  • the patient or clinician may select one or more nighttime settings from the user interface to configure the pump for nocturnal nutrition delivery.
  • the selection/deselection of nighttime/daytime settings can be manual or automatic (e.g., based upon time of day, ambient light or other known sensors, pump parameters, status of prescription, or any combination thereof).
  • the selection/deselection may also be scheduled on a one-time basis or on a recurring basis.
  • the nighttime mode cannot be activated unless the pump is plugged into the AC mains voltage.
  • nighttime mode will typically drain a battery used for ambulatory pumping at a more rapid rate than normal daytime mode. Therefore, in some embodiments, if the pump is not plugged into the AC mains voltage, the nighttime mode is unavailable for selection by the user in order to protect the battery from accidental drainage.
  • Nutrition delivery systems typically employ rotary peristaltic pumps to deliver the nutrition to the patient.
  • a rotary peristaltic pump may have an armature attached to a motor.
  • the armature has two or more rollers positioned on the radially distal end of the armature.
  • To pump fluid through a flexible tube the tube is seated into a raceway so that when the armature rotates, the rollers come into pinching contact with the tube for an arcuate length of tubing within the raceway, forcing liquid forward through the lines.
  • the motor speeds up, the rollers force liquid along the flexible tube at a higher flow rate.
  • rotary peristaltic pumps do not possess the capability of varying the motor speed beyond one or a few set speeds.
  • a desired precise higher or lower flow rate may not be achieved simply by speeding up or slowing down the rotational speed of the pump, but by running the pump in 'duty cycles'.
  • Running a rotary peristaltic pump in duty cycles enables the programmer or operator to effectively vary flow rates over time by switching the constant-speed pump on for a calculated period of time and then off for a calculated period of time.
  • the term "motor” may refer to a direct drive motor (with no gearbox) or a motor and gearbox combination.
  • the term "rotations per minute" or rpm are applicable to brushed direct current motors with gearboxes attached.
  • a rotary peristaltic pump operates at a constant 50 rotations per minute (rpm). It should be appreciated that the interior cross-sectional area of the tubing dictates the amount of nutrition that a 50 rpm motor will pump to the patient.
  • flexible tubing is being used that allows 0.20513 ml to be pumped for each full pump rotation. Such a system would produce an approximate pumping flow rate of 10.256 ml minute. Operating uninterrupted at full speed for an hour, this pump would deliver about 615 ml of nutrition to a patient.
  • each 39 seconds of operation is one duty cycle: one cycle of being switched on for 39 seconds, after which the pump is switched off for 21 seconds.
  • Knowing the tubing size then allows one to calculate the precise amount of fluid delivered over N duty cycles. Therefore, if the graph of FIG. 1 was extrapolated to include sixty duty cycles (i.e., one hour of operation), then the total area under the bars (102, 104, 106... ⁇ 6 ⁇ ) could be used with the known tube geometry to calculate the total fluid delivered in the time T 60 minutes; in the case of DELIVERY A, 400ml.
  • the pumping would be quieter and more desirable if the operator could achieve the same total hourly delivery rate (400ml) with a longer duty cycle at a lower flow rate, if possible.
  • DELIVERY B outlined in the table below, the same 400ml/hr total hourly delivery flow rate may be achieved using the same flexible tubing internal cross section and the same 1 minute period of operation duration (duty cycle) + non-operation duration (pump switched off), but with the pump operating at 30 rpm instead of 50 rpm.
  • the pump would have to be switched on for about a 91% duty cycle, or 55 seconds of each minute. Since the DELIVERY B pump is operating at an rpm that is 40% slower than the DELIVERY A pump, even though the pump operates more continuously in DELIVERY B, the noise of its operation would be much less disturbing.
  • the cumulative shaded area under bars 202, 204, and 206 provides the total number of pump rotations of the duty cycles. Similar to DELIVERY A, knowing the tubing size then allows one to calculate the precise amount of fluid delivered over N duty cycles. If the graph of FIG. 2 was extrapolated to include sixty duty cycles (i.e., one hour of operation), then the total area under the bars (202, 204, 206...N 6 o) could be used with the known tube geometry to calculate the total fluid delivered, in this case, 400ml. It should be appreciated that, as with DELIVERY A, the speeds, flow rates, duty cycles and other parameters used for this description are wholly exemplary and not limiting. A range of flow rates optimal for nocturnal pumping or "silent mode" is discussed in greater detail below.
  • each pair of duty cycle duration plus non-operating duration need not be the same between silent pump mode and regular pump mode (i.e., the 1 minute duty cycle plus non-operating duration for DELIVERY A does not necessarily have to equal the duty cycle plus non-operating duration for DELIVERY B).
  • each operation duration plus non-operation duration may be customized for the silent pump mode to ensure the overall flow rate for the delivery session remains the same, while the pump speed slows down to an optimal (but not too slow) rate.
  • the processor and controller is configured to monitor real-time pump parameters to calculate and optimize the silent pump mode settings.
  • the processor and controller of the pumping system are configured to calculate a silent operating mode profile when the user indicates a desire to enter silent mode.
  • a silent operating mode profile when the user indicates a desire to enter silent mode.
  • any number of suitable variables can be considered and incorporated into a silent operating mode profile, including but not limited to: prescription, total fluid delivered in the delivery session, total fluid to be delivered in the delivery session, normal operating parameters (pump speed, duty cycle), time of silent mode activation (immediate or scheduled), patient profile, care setting, line type, pump capabilities, and flow rate.
  • the patient or clinician can schedule the time of entering silent mode for some point in the future (i.e., delay the start of the silent mode).
  • duty cycle may also be a function of the individual tolerance of the patient. Depending upon condition and health, some patients may not be able to continuously receive a trickle of feed for an extended period defined by the duty cycle recalculations (e.g., 8 hours).
  • the patient's or clinician's interaction with the pump system is possible via an input device either remote from or local to the pump.
  • the patient can schedule a pump's entry into silent mode via a mobile device paired with the pump system.
  • Typical DC motors used for nutrition pumps operate at a constant motor torque.
  • the speed of the motor shaft is controlled by varying the input voltage applied to the motor.
  • changing the input voltage can also mean changing a pulse width modulation (PWM) duty cycle to change the current delivered.
  • PWM pulse width modulation
  • FIG. 3 illustrates a graph plotting the input voltage vs. motor speed of a DC motor.
  • FIG. 4 illustrates a graph plotting output power vs. motor speed of a DC motor.
  • FIG. 5 illustrates a graph plotting efficiency vs. motor speed of a DC motor. It should be appreciated that both DELIVERY A and DELIVERY B profiles are superimposed on FIGS. 3 to 5 for ease of explanation, and are not intended to be to scale. Nor are the curves intended to accurately depict the precise profiles of the respective illustrations.
  • DELIVERY A operates at col , equal to 50 rpm, which is achieved at an input voltage of VI volts 304.
  • DELIVERY B operates at co2, equal to 30 rpm, the input voltage required is V2 volts 306.
  • specific motor speeds i.e., DELIVERY A at 50 rpm and DELIVERY B at 30 rpm
  • FIG. 4 a graph showing the power vs. rotation speed of a DC pump is illustrated 400.
  • Two curves are illustrated in FIG. 4: the Output Power and the Input Power.
  • Efficiency of a DC motor is highest when the output power is closest to the input power. As discussed in more detail below, the efficiency of the motor is calculated by dividing the output power by the input power. Therefore, when the motor is converting more of the input power to output power, efficiency (OUTPUT /INPUT) is closer to 100%. As the output power decreases as a proportion of the input power, the efficiency of the motor also goes down.
  • the input power is linear, and the output power is curved, with a peak.
  • the pump speeds of DELIVERY A and DELIVERY B are superimposed on the power v. motor speed graph of FIG. 4, with col rpm producing PI watts of power, and co2 rpm producing P2 watts of power.
  • the motor runs most efficiently at the motor speed which corresponds to the smallest difference between input power and output power. In this case, the most efficient speed is identified at the Max Efficiency (PM), at which point the distance between the Input Power curve and the Output Power curve is minimized, as indicated by distance 408.
  • PM Max Efficiency
  • DELIVERY A daytime mode motor speed col is very close to maximum efficiency (as illustrated by distance 404' between Input Power and Output Power), which explains why such speeds are typically used.
  • FIG. 4 illustrates the relative inefficiency of the DELIVERY B nighttime mode at motor speed co2.
  • the distance 406' between Input Power and Output Power of DELIVERY B is much greater than the col DELIVERY A speed efficiency 404' or the optimal efficiency 408.
  • the mechanical output power that the motor can deliver is divided by the power that the motor absorbs (input power). It should be appreciated that the output power and the absorbed power vary in relation to the speed of motor rotation.
  • FIG. 5 a graph illustrating the efficiency of DC motors is illustrated.
  • a DC motor attains maximum efficiency when it operates at greater than 50% of its no-load speed. Therefore, when the pump runs below 50% of its no-load speed, the efficiency of the motor is decreased.
  • Maximum efficiency (nearest to 100%) is achieved at 502 of the efficiency-to-motor speed graph 500 illustrated in FIG. 5. Due to losses from heat, friction, etc., pumps can never reach true 100% efficiency, but the graphs and models discussed herein show a hypothetical frictionless embodiment to convey the principles. It should be appreciated that the motor speed at 502 of FIG. 5 is equal to the motor speed at 408 of FIG. 4.
  • the motor is running at efficiency El%, which can be identified at point 504 on the efficiency curve 510.
  • the motor operates at speed co2 rpm.
  • FIG. 5 shows that the efficiency of the motor E2% is significantly lower at point 506 of the efficiency curve for DELIVERY B than for DELIVERY A.
  • Silent mode may also require a recalibration of occlusion alarm sensors and routines to detect same. It would be desirable to decrease the motor speed to quiet the pump noise during nocturnal pumping while minimizing the above drawbacks of running with lower efficiency. Many of the drawbacks listed above are eliminated entirely if the pump is constantly plugged into the AC mains voltage when running in nighttime mode. The trade-off of tethering the pump to an AC outlet during nighttime mode is worth the exchange for a quieter nocturnal operation and improved patient comfort.
  • the silent mode is the most effective for prescribed rates under about 300 ml/hour. In other embodiments, the silent mode is the most effective for prescribed rates under about 290 ml/hour. In other embodiments, the silent mode is the most effective for prescribed rates under about 280 ml/hour. In other embodiments, the silent mode is the most effective for prescribed rates under about 270 ml/hour. In other embodiments, the silent mode is the most effective for prescribed rates under about 260 ml/hour. In other embodiments, the silent mode is the most effective for prescribed rates under about 250 ml/hour. In other embodiments, the silent mode is the most effective for prescribed rates under about 240 ml/hour.
  • the silent mode is the most effective for prescribed rates under about 230 ml/hour. In other embodiments, the silent mode is the most effective for prescribed rates under about 220 ml/hour. In other embodiments, the silent mode is the most effective for prescribed rates under about 210 ml/hour. In other embodiments, the silent mode is the most effective for prescribed rates under about 200 ml/hour. According to various typical enteral feeding prescriptions, nocturnal feeding tends to require lower hourly flow rates (e.g., but not limited to about 100 to 150 ml/hour). It should be appreciated that, however, that higher flow rates are also contemplated for being run in night mode according to the discussion herein.
  • the pump system of the present disclosure is capable of a nocturnal silent mode, which is operable as one of a suite of "night mode" settings available to the patient or operator.
  • a panel of night mode settings could include (but is not limited to) the following options:
  • Night mode exiting - the first press of any button while in night mode turns off night mode and thus replaces the initial button function. Exiting night mode could also be initiated: after some period of time (e.g., returns to normal after 8 hours); changing any of the features automatically changed by night mode (e.g., switching Autodim off would automatically revert from night mode back to normal mode); or based on a prompt appearing when the pump is restarted, such as "Would you like to continue in night mode?"
  • the grouping of one or more selective night mode options allows the patient or operator to customize the nocturnal pumping experience on a case- by-case basis, capable of being activated via a single menu setting.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • General Health & Medical Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Anesthesiology (AREA)
  • Hematology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Biomedical Technology (AREA)
  • Engineering & Computer Science (AREA)
  • Vascular Medicine (AREA)
  • Infusion, Injection, And Reservoir Apparatuses (AREA)

Abstract

Un système d'alimentation entérale comprend un réglage de nuit pendant lequel le système de pompe fonctionne de manière silencieuse pendant les heures de sommeil. Le système de pompe permet au patient d'entrer sélectivement en mode nocturne, et permet un fonctionnement plus silencieux en faisant fonctionner la pompe à un régime inférieur.
PCT/EP2018/056559 2017-03-30 2018-03-15 Pompe de nutrition à réglage de nuit WO2018177765A1 (fr)

Applications Claiming Priority (2)

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US201762478903P 2017-03-30 2017-03-30
US62/478,903 2017-03-30

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WO2018177765A1 true WO2018177765A1 (fr) 2018-10-04

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Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10765798B2 (en) 2019-01-24 2020-09-08 Medline Industries, Inc. Feeding syringe holder
USD906516S1 (en) 2019-07-01 2020-12-29 Medline Industries, Inc. Valve clip
USD920504S1 (en) 2019-07-01 2021-05-25 Medline Industries, Inc. Valve
US11110036B2 (en) 2019-07-01 2021-09-07 Medline Industries, Inc. Feeding set and enteral feeding pump assembly
US11344480B2 (en) 2018-07-26 2022-05-31 Medline Industries, Lp Enteral fluid delivery system

Citations (3)

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Publication number Priority date Publication date Assignee Title
US20090105650A1 (en) * 2007-10-18 2009-04-23 Roche Diagnostics Operations, Inc. Drug delivery pump drive using linear piezoelectric motor
US20120203198A1 (en) * 2011-02-09 2012-08-09 Searle Gary M Nighttime Basal Dosing Device
US20150073338A1 (en) * 2013-09-10 2015-03-12 Covidien Lp Enteral feeding pump with acceleration sensor and related methods therefor

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090105650A1 (en) * 2007-10-18 2009-04-23 Roche Diagnostics Operations, Inc. Drug delivery pump drive using linear piezoelectric motor
US20120203198A1 (en) * 2011-02-09 2012-08-09 Searle Gary M Nighttime Basal Dosing Device
US20150073338A1 (en) * 2013-09-10 2015-03-12 Covidien Lp Enteral feeding pump with acceleration sensor and related methods therefor

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11344480B2 (en) 2018-07-26 2022-05-31 Medline Industries, Lp Enteral fluid delivery system
US10765798B2 (en) 2019-01-24 2020-09-08 Medline Industries, Inc. Feeding syringe holder
USD906516S1 (en) 2019-07-01 2020-12-29 Medline Industries, Inc. Valve clip
USD920504S1 (en) 2019-07-01 2021-05-25 Medline Industries, Inc. Valve
USD925033S1 (en) 2019-07-01 2021-07-13 Medline Industries, Inc. Valve clip
US11110036B2 (en) 2019-07-01 2021-09-07 Medline Industries, Inc. Feeding set and enteral feeding pump assembly
USD972721S1 (en) 2019-07-01 2022-12-13 Medline Industries, Lp Valve
USD1010113S1 (en) 2019-07-01 2024-01-02 Medline Industries, Lp Valve
USD1065523S1 (en) 2019-07-01 2025-03-04 Medline Industries, Lp Valve

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