US20090226328A1 - Remote Data Monitor For Heart Pump System - Google Patents

Remote Data Monitor For Heart Pump System Download PDF

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Publication number
US20090226328A1
US20090226328A1 US11720023 US72002305A US2009226328A1 US 20090226328 A1 US20090226328 A1 US 20090226328A1 US 11720023 US11720023 US 11720023 US 72002305 A US72002305 A US 72002305A US 2009226328 A1 US2009226328 A1 US 2009226328A1
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Prior art keywords
pump
controller
module
method
monitor
Prior art date
Legal status (The legal status 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 status listed.)
Abandoned
Application number
US11720023
Inventor
Gino F. Morello
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
RELIANT HEART Inc
Original Assignee
MicroMed Tech Inc
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/101Non-positive displacement pumps, e.g. impeller, centrifugal, vane pumps
    • A61M1/1012Constructional features thereof
    • A61M1/1013Types of bearings
    • A61M1/1015Magnetic bearings
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/101Non-positive displacement pumps, e.g. impeller, centrifugal, vane pumps
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/101Non-positive displacement pumps, e.g. impeller, centrifugal, vane pumps
    • A61M1/1029Drive systems therefor
    • A61M1/1031Drive systems therefor using a motor with canned rotor, i.e. a motor enclosed within a casing along with the rotor so that the motor bearings are lubricated by the blood that is being pumped
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/1086Regulating or controlling systems therefor
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/12Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps implantable into the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/12Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps implantable into the body
    • A61M1/122Heart assist devices, i.e. for assisting an ailing heart, using additional pumping means in the blood circuit
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/33Controlling, regulating or measuring
    • A61M2205/3331Pressure; Flow
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/33Controlling, regulating or measuring
    • A61M2205/3331Pressure; Flow
    • A61M2205/3334Measuring or controlling the flow rate
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/35Communication
    • A61M2205/3546Range
    • A61M2205/3569Range sublocal, e.g. between console and disposable
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/35Communication
    • A61M2205/3576Communication with non implanted data transmission devices, e.g. using external transmitter or receiver
    • A61M2205/3592Communication with non implanted data transmission devices, e.g. using external transmitter or receiver using telemetric means, e.g. radio or optical transmission

Abstract

A pump control system includes a controller module for controlling a pump, such as an implantable blood pump. A remote monitor is adapted to communicate with the controller module via a wireless communications medium, such as a low-power radio s frequency link. The remote monitor provides a user interface similar or identical to the controller module, providing a user the ability to remotely monitor the pump's performance and to respond to alarms.

Description

    CROSS REFERENCE TO RELATED APPLICATION
  • This application claims the benefit of U.S. Provisional Patent Application No. 60/522,874, entitled “REMOTE DATA MONITOR FOR HEART PUMP SYSTEM,” filed on Nov. 16, 2004, which is incorporated by reference.
  • BACKGROUND
  • The invention relates generally to heart pump systems and, more specifically, to a remote monitor for such pumps.
  • Implantable blood pump systems are generally employed either to completely replace a human heart that is not functioning properly, or to boost blood circulation in patients whose heart still functions but is not pumping blood at an adequate rate. Known implantable blood pump systems are primarily used as a “bridge to transplant.” In other words, existing blood pump system applications are mainly temporary fixes, intended to keep a patient alive until a donor is available. However, the shortage of human organ donors, coupled with improvements in blood pump reliability make long-term, or even permanent blood pump implementations a reality.
  • Despite this need, existing implantable pump systems have not been satisfactory for long term use. Known systems of the continuous flow type are designed primarily for use in a hospital setting. These systems typically include the implanted pump device, a power source such as a rechargeable battery, a motor controller for operating the pump motor, and an external operator console. While some existing implantable pump systems allow for operation while decoupled from the operator console, operating these systems “stand-alone” can be a risky endeavor. This is due, at least in part, to the lack of an adequate user interface when the system is decoupled from the console.
  • Moreover, prior blood pump systems are not conducive to long-term use outside an institutional setting. Known systems often require a large, fixed operator console for the system to function. While prior art operator consoles may be cart mounted to be wheeled about the hospital, at home use of known systems is difficult at best. Other problems of prior pump systems that have limited their mobility and use to relatively short times are related to motor controller size and shape limitations.
  • Thus, there is a need for a pump control system that addresses the shortcomings associated with the prior art.
  • SUMMARY
  • In accordance with certain teachings of the present disclosure, a pump control system includes a controller module for controlling a pump, such as an implantable blood pump. A remote monitor is adapted to communicate with the controller module via a wireless communications medium, such as a low-power radio frequency link. The remote monitor provides a user interface similar or identical to the controller module, providing a user the ability to remotely monitor the pump's performance and to respond to alarms.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • Other objects and advantages of the invention will become apparent upon reading the following detailed description and upon reference to the drawings in which:
  • FIG. 1 is a block diagram of a pump system in accordance with teachings of the present disclosure.
  • FIG. 2 illustrates an exemplary implantable heart pump in accordance with an embodiment of the system disclosed herein.
  • While the invention is susceptible to various modifications and alternative forms, specific embodiments thereof have been shown by way of example in the drawings and are herein described in detail. It should be understood, however, that the description herein of specific embodiments is not intended to limit the invention to the particular forms disclosed, but on the contrary, the intention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the appended claims.
  • DETAILED DESCRIPTION
  • Illustrative embodiments of the invention are described below. In the interest of clarity, not all features of an actual implementation are described in this specification. It will of course be appreciated that in the development of any such actual embodiment, numerous implementation-specific decisions must be made to achieve the developers' specific goals, such as compliance with system-related and business-related constraints, which will vary from one implementation to another. Moreover, it will be appreciated that such a development effort might be complex and time-consuming, but would nevertheless be a routine undertaking for those of ordinary skill in the art having the benefit of this disclosure.
  • Turning to the figures, and in particular to FIG. 1, a ventricle assist device (VAD) system 10 in accordance with an embodiment of the present invention is illustrated. The VAD system 10 includes components designed to be implanted within a human body and components external to the body. The components of the system 10 that are implantable include a pump 12 and a flow sensor 14. The external components include a portable controller module 16 and a remote monitor module 18. The implanted components are connected to the controller module 16 via a percutaneous cable. The controller module 16 may be mounted to a support device, such as a user's belt 23 or to a vest worn by the user, for example. Additional components of a VAD system are shown and described in U.S. Pat. No. 6,183,412, which is incorporated by reference.
  • The controller module 16 includes a processor, such as a microcontroller 80, which in one embodiment of the invention is a model PIC16C77 microcontroller manufactured by Microchip Technology. The microcontroller 80 includes a multiple channel analogue to digital (A/D) converter, which receives indications of motor parameters from the motor controller 84. Thus, the controller module 16 may monitor parameters such as instantaneous motor current, the DC component or mean value of the motor current, and motor speed.
  • The embodiment shown in FIG. 1 further includes an integral flow meter 86. At least one flow sensor 14 is implanted down stream of the pump 12. Alternately, a flow sensor 14 may be integrated with the pump 12. The flow meter 86 is coupled between the implanted flow sensor 14 and the microcontroller 80. The flow meter 86 receives data from the flow sensor 14 and outputs flow rate date to the microcontroller 80, allowing the system to monitor instantaneous flow rate.
  • The VAD System 10 may incorporate an implantable continuous-flow blood pump, such as the various embodiments of axial flow pumps disclosed in U.S. Pat. No. 5,527,159 or in U.S. Pat. No. 5,947,892, both of which are incorporated herein by reference in their entirety. An example of a blood pump suitable for use in an embodiment of the invention is illustrated in FIG. 2. The exemplary pump 12 includes a pump housing 32, a diffuser 34, a flow straightener 36, and a brushless DC motor 38, which includes a stator 40 and a rotor 42. The housing 32 includes a flow tube 44 having a blood flow path 46 therethrough, a blood inlet 48, and a blood outlet 50.
  • The stator 40 is attached to the pump housing 32, is preferably located outside the flow tube 44, and has a stator field winding 52 for producing a stator magnetic field. In one embodiment, the stator 40 includes three stator windings and may be three phase “Y” or “Delta” wound. The rotor 42 is located within the flow tube 44 for rotation in response to the stator magnetic field, and includes an inducer 58 and an impeller 60. Excitation current is applied to the stator windings 52 to generate a rotating magnetic field. A plurality of magnets 62 are coupled to the rotor 42. The magnets 62, and thus the rotor 42, follow the rotating magnetic field to produce rotary motion.
  • The remote data monitor (RDM) 18 is a small portable handheld device that includes a processing device 112 and a user interface 110 that effectively replicates the user interface 111 of the controller module 16 remotely via a wireless communication link 120. In an exemplary embodiment, the wireless link 120 is a low-power radio frequency (RF) link usable over a maximum distance of approximately 300 feet (100 meters) using the system's standard antenna configuration. While in use, the device provides the user with the ability to remotely monitor the VAD pump's 12 performance and to respond to alarms. The pump controller 16 and remote monitor(s) 18 may be programmed via the clinical data acquisition system or the remote monitor 18 may be programmed telemetrically by the pump controller 16, for example.
  • The wireless link 120 includes antennas, which my suitably comprise simple monopoles. The system's antennas maybe constructed from ferrite rods or with traces on the system's internal printed circuit board. Integral antennas may be used exclusively, or external antennas may be employed for increased range capability, or a combination of integral and external antennas may be used.
  • The integrity of the link 120 will be continuously verified while the device is in operation. In the event that the remote monitor 18 is located too far from the VAD controller 16, the RF link becomes “noisy” or unusable, or if the monitor's 18 batteries are low, the VAD controller 16 will continue to function and alarm normally. More specifically, in exemplary implementations, the remote monitor 18 periodically transmits status information back to the pump controller 16 to conform proper link operation. The remote monitor 18 may monitor and display received signal strength information, and the pump controller 16 can increase or decrease its transmitter output power proportional to the signal strength reported back from the remote monitor 18.
  • The carrier may be angle modulated (i.e. frequency modulated (FM) or phase modulated (PM)) to minimize the effects of external noise induced errors. Alternatively, the carrier may be amplitude modulated (AM) to maximize battery life. Forward error correction techniques may be used to maximize the integrity of the communication link. Spread spectrum techniques are used to further minimize externally induced noise from compromising the communication link between the pump controller and corresponding remote monitor. The receiver may request that a transmission be retransmitted in the event of an error. In typical installations, transmissions are within the US and European ISM (i.e. Industrial, Scientific, Medical) band.
  • Multiple controller 16 and remote monitor 18 pairs may be used in close proximity to one another. Each pump controller 16 and corresponding remote monitor 18 may communicate on a designated frequency or frequency pair or on the same frequency or frequency pair. Transmitted data packets contain the address of the intended remote monitor 16. Each pump controller 16 first “listens” to confirm if another pump controller 16 is transmitting. In the event there is no other transmission, the pump controller 16 may begin transmitting and, conversely, in the event another transmission is “heard” the pump controller 16 will wait for the channel to be clear. In other implementations, one pump controller 16 may broadcast to several remote monitors 16 (e.g. one with the patient, one with the caregiver).
  • The data transmitted between the pump controller 16 and remote monitor 18 may be encoded such that the remote monitor 18 only responds to data transmitted with a unique address or to transmissions containing the correct address. A hardware or software based correlator may be used to identify the address.
  • In certain embodiments, the remote monitor 18 is approximately 3 inches wide by 2 inches high by 1 inch thick, weighs less than 5 oz., includes a wrist-strap such that it may be worn by the caregiver or patient on the wrist, and includes a combination belt clip/tilt stand for use on the patient's or caregiver's belt or nightstand. The device 18 may be powered from an internal rechargeable battery to be completely portable or it may be plugged into the ac mains using an optional power adapter. Additionally, the device 18 may be plugged into an automotive power outlet for continuous operation while on long trips in an automobile or airplane. The device 18 will support simultaneous charging of the internal battery while monitoring the VAD controller 16 (e.g. at night while patient and parent/caregiver are sleeping).
  • The remote monitor's 18 user interface is identical to the VAD controller 18 interface and includes a tricolor light emitting diode (LED) backlit graphic liquid crystal display (LCD) to display multi-lingual diagnostic and emergency messages, a sealed two-button keypad with tactile feedback and rim-embossing to silence alarms and scroll through diagnostic message displays, three bicolor LEDs indicating individual battery status and fail-safe mode operation, two distinct, variable pitch, variable loudness audible enunciators, and an optional audible voice output for diagnostic and emergency alarms.
  • The backlit LCD can indicate functional pump information to the patient and/or caregiver, and in exemplary embodiments, the backlight utilizes multiple colors to convey functional and alarm information to the patient and caregiver (e.g. green=normal, yellow-diagnostic alarm, red=emergency alarm).
  • The audible alarms may be elicited through piezo buzzer enunciators. The variable loudness audible enunciators maybe be operated such that the pitch and/or volume changes proportionally to the length of time that the alarm is activated. The audible voice output may be elicited through a voice coil type speaker element. A natural language speech synthesizer may be employed, including a phoneme based speech synthesizer enabling audible speech to be generated in a multiplicity of languages. Further, the natural language voice's pitch and cadence may be programmed to simulate a male or female adult voice based on the patient or caregiver's preference. Still further, the natural language voice output's pitch and cadence may be programmed to simulate a less-intimidating child's voice for pediatric cases. A motor with integral eccentric may be enabled to vibrate during any alarming condition to help in alerting the patient or caregiver.
  • Optionally, in pediatric applications, a wireless audio channel may be added to integrate the functionality of a commercial “baby monitor” into the system. A transmitter with a microphone or other sound detecting device transmits audio signals to a receiver integrated into the remote monitor 18, which further includes an output device such as a speaker. This minimizes the number of different systems the parent or caregiver must use and manage. This function would also include a volume control to allow the parent or caregiver to set the device's output to the desired audio level.
  • The above description of exemplary embodiments of the invention are made by way of example and not for purposes of limitation. Many variations may be made to the embodiments and methods disclosed herein without departing from the scope and spirit of the present invention. The present invention is intended to be limited only by the scope and spirit of the following claims.

Claims (22)

1. A pump control system comprising:
a controller module connectable to an implanted heart pump; and
a monitor module adapted to communicate with the controller module via a wireless communications medium.
2. The pump control system of claim 1, wherein the controller module includes:
a processor;
a motor controller electrically coupled to the processor, the motor controller adapted to power the pump motor such that the pump motor operates at a desired speed, the motor controller adapted to output digital representations of pump motor operating parameters to the processor;
a user interface coupled to the processor; and
wherein the monitor module includes a user interface.
3. The pump control system of claim 1, wherein the controller module user interface matches the monitor module user interface.
4. The pump control system of claim 1, wherein the wireless communications medium is a bi-directional radio frequency (RF) fink.
5. The pump control system of claim 1, wherein monitor module includes a device for attaching to a user's wrist.
6. The pump control system of claim 1, wherein monitor module includes a device for attaching to a user's belt.
7. The pump control system of claim 1, wherein monitor module includes a device for receiving and outputting audio signals.
8. The pump control system of claim 1, wherein monitor module is programmed to periodically transmit status information to the controller module.
9. A method of operating a blood pump, comprising:
connecting a controller module to a blood pump; and
transmitting data between a monitor module and the controller module via a wireless communications medium.
10. The method of claim 9, transmitting data includes transmitting functional and alarm messages.
11. The method of claim 9, further comprising:
powering the pump such that the pump operates at a desired speed;
outputting digital representations of pump operating parameters on a user interface of the controller module;
transmitting the pump operating parameters to the monitor module; and
displaying the pump operating parameters on a user interface of the monitor module.
12. The method of claim 9, wherein transmitting data includes transmitting via a bi-directional radio frequency (RF) link.
13. The method of claim 9, further comprising: attaching the monitor module to a user's wrist.
14. The method of claim 9, further comprising attaching the monitor module to a user's belt.
15. The method of claim 9, further comprising transmitting status information from the module to the controller module.
16. The method of claim 15, wherein transmitting status information includes transmitting received signal strength information.
17. The method of claim 16, further comprising varying the transmit output power of the controller module in response to the received signal strength information.
18. The method of claim 9, wherein a plurality of controller modules are connected to a plurality of corresponding blood pumps, and wherein one monitor module communicates with the plurality of controller modules.
19. The method of claim 9, wherein a plurality of controller modules are connected to a plurality of corresponding blood pumps, and wherein each of the controller modules communicates with a corresponding monitor module on a predetermined frequency.
20. The method of claim 19, wherein data transmitted from the controller module includes the address of the intended monitor module.
21. The method of claim 9, wherein a plurality of monitor modules communicate with a single controller module.
22. The method of claim 9, wherein the controller module verifies that no other controller module is transmitting before transmitting data to the monitor module.
US11720023 2004-11-16 2005-11-16 Remote Data Monitor For Heart Pump System Abandoned US20090226328A1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
US52287404 true 2004-11-16 2004-11-16
US11720023 US20090226328A1 (en) 2004-11-16 2005-11-16 Remote Data Monitor For Heart Pump System
PCT/US2005/041743 WO2006055745A3 (en) 2004-11-16 2005-11-16 Remote data monitor for heart pump system

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US11720023 US20090226328A1 (en) 2004-11-16 2005-11-16 Remote Data Monitor For Heart Pump System

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US20090226328A1 true true US20090226328A1 (en) 2009-09-10

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US (1) US20090226328A1 (en)
EP (1) EP1812094B1 (en)
JP (1) JP2008520285A (en)
CN (1) CN101056663B (en)
WO (1) WO2006055745A3 (en)

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US20140341726A1 (en) * 2013-05-14 2014-11-20 Heartware, Inc. Blood pump with separate mixed-flow and axial-flow impeller stages and multi-stage stators
US20150038771A1 (en) * 2013-08-02 2015-02-05 Circulite, Inc. Implantable system with secure remote control
US9287040B2 (en) 2012-07-27 2016-03-15 Thoratec Corporation Self-tuning resonant power transfer systems
US9583874B2 (en) 2014-10-06 2017-02-28 Thoratec Corporation Multiaxial connector for implantable devices
US9592397B2 (en) 2012-07-27 2017-03-14 Thoratec Corporation Thermal management for implantable wireless power transfer systems
RU2618909C2 (en) * 2013-10-03 2017-05-11 Бейджинг Рисёрч Инститьют Оф Присайз Мекатроникс Энд Контроулз Management system for blood discharge pump and blood discharge pump system
US9680310B2 (en) 2013-03-15 2017-06-13 Thoratec Corporation Integrated implantable TETS housing including fins and coil loops
US9805863B2 (en) 2012-07-27 2017-10-31 Thoratec Corporation Magnetic power transmission utilizing phased transmitter coil arrays and phased receiver coil arrays
US9825471B2 (en) 2012-07-27 2017-11-21 Thoratec Corporation Resonant power transfer systems with protective algorithm
US9855437B2 (en) 2013-11-11 2018-01-02 Tc1 Llc Hinged resonant power transfer coil
US10148126B2 (en) 2015-08-31 2018-12-04 Tc1 Llc Wireless energy transfer system and wearables
US10177604B2 (en) 2016-10-06 2019-01-08 Tc1 Llc Resonant power transfer systems having efficiency optimization based on receiver impedance

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WO2017015268A1 (en) 2015-07-20 2017-01-26 Thoratec Corporation Flow estimation using hall-effect sensors
CN105422432B (en) * 2015-12-08 2017-06-13 卧龙电气集团股份有限公司 Multi-mode intelligent pump frequency monitoring system

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