WO1998026840A1 - Leadless multisite implantable stimulus and diagnostic system - Google Patents

Leadless multisite implantable stimulus and diagnostic system Download PDF

Info

Publication number
WO1998026840A1
WO1998026840A1 PCT/US1997/023012 US9723012W WO9826840A1 WO 1998026840 A1 WO1998026840 A1 WO 1998026840A1 US 9723012 W US9723012 W US 9723012W WO 9826840 A1 WO9826840 A1 WO 9826840A1
Authority
WO
WIPO (PCT)
Prior art keywords
data
power
high frequency
signals
transmitting
Prior art date
Application number
PCT/US1997/023012
Other languages
French (fr)
Inventor
Kenneth B. Stokes
Andrianus P. Donders
Original Assignee
Medtronic, Inc.
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 Medtronic, Inc. filed Critical Medtronic, Inc.
Priority to AU55267/98A priority Critical patent/AU5526798A/en
Publication of WO1998026840A1 publication Critical patent/WO1998026840A1/en

Links

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/37211Means for communicating with stimulators
    • A61N1/37252Details of algorithms or data aspects of communication system, e.g. handshaking, transmitting specific data or segmenting data
    • A61N1/37288Communication to several implantable medical devices within one patient
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/378Electrical supply
    • A61N1/3787Electrical supply from an external energy source
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/37211Means for communicating with stimulators
    • A61N1/37252Details of algorithms or data aspects of communication system, e.g. handshaking, transmitting specific data or segmenting data
    • A61N1/37254Pacemaker or defibrillator security, e.g. to prevent or inhibit programming alterations by hackers or unauthorised individuals

Definitions

  • This invention relates to implantable medical systems for delivery of stimulation treatment and the like and, particularly, leadless systems having multiple stimulus and/or data collection sites.
  • Implantable medical treatment systems have achieved great success and have come into widespread use in recent decades.
  • pacing systems including implanted pacemakers, are widely used to treat various cardiac conditions by delivery of stimulus pulses to the heart.
  • Another development is that of the implantable defibrillator, or pacemaker/cardioverter/defibrillator for delivering different types of shock therapy to a patient's heart, as well as pacing pulses.
  • Other areas that are under development and are being explored include implantable diagnostic devices for collecting information concerning the activity of a patient's heart or other organ, and relay of collected data to an external programmer; and various neuro stimulation devices.
  • a pacing lead is subject to about 38 million flexes per year, it is subject to the body's defense mechanisms, and is placed in an extremely hostile environments. The result is that conductors fracture, insulation degrades for various reasons, and the leads can become infected. As is known, removal of chronically implanted leads is extremely difficult. In addition, when two or more leads are involved, the problems are compounded. The more hardware there is implanted, the greater is the risk of thrombosis (embolism, thoracic outlet syndrome, SVC syndrome, etc.), infection, valvular, and other tissue damage, etc.
  • a leadless plural site system where each site has an implanted device with its own battery source likewise has the problem of substantial additional expense attributable to the need of having a battery for each remote implanted device at each respective remote site.
  • the prior art provides examples of wireless data communication between two or more sites within a patient.
  • U.S. Patent 5,411,535 discloses a pacer system where data is sent from a main pacer unit to remote electrode units, for controlling delivery of pace pulses as well as providing sensed data from the electrode units back to the main pacer.
  • each remote location has its own battery supply. See also U.S. Patent 5,405,367, which discloses multiple stimulators devices at different sites.
  • Each of the implanted stimulator devices receives energy from an alternating magnetic field, i.e., through a transformer, from an external source.
  • a transparent difficulty with this system is that it requires frequent if not substantially continuous transfer from an external source to the implanted devices, which would be an unacceptable arrangement in most cases. See also U.S. Patent.
  • the prior art thus shows transformer-type coupling of energy from an external source to an implanted system, and wireless transmission of data between multiple implanted devices in a patient.
  • What is desirable in order to expand system capability for treatment at multiple patient sites is a more flexible implantable system with devices at plural sites; a system that does not require multiple leads from the implantable stimulator to the respective plural sites; and a system that has the capability of transmitting power from a single battery source to the respective site devices on an efficient basis.
  • the term "leadless” refers to the absence of a lead interconnecting the plural sites, it being understood that one or more of the site devices of the system may have a lead for delivery of stimulus pulses and/or sensing data.
  • the flexible system and method of this invention has the aim of providing a power source, e.g., a battery, in a central controller, and transmitting capability for transmitting power from the central controller to a remote device or to each of a plurality of remote site devices, the transmission being controlled in order to optimize power efficiency.
  • an implantable system and method for pacing or otherwise treating a patient and/or for collecting data having a controller unit and one or more site-specific devices separate from the controller unit, where the controller unit has a power source and a transmitter for transmitting to each remote device a high frequency signal comprising at least a power component derived from the power source.
  • Each remote unit in the system has a receiver for receiving the high frequency signal and a circuit for deriving power from it, and a power supply for storing the derived power and powering the unit.
  • the system preferably has the capability of transmitting data from the main controller unit along with the power, with a power component and a data component being modulated onto a common carrier for transmission to one or more of the remote devices.
  • each remote device has a transmitter for transmitting sensed data back to the main controller unit.
  • the system comprises capability for controlling the high frequency power transmission as a function of the " power requirements or demand at each remote unit.
  • each remote unit operates on a very low power basis except when system demand calls for it to deliver a treatment such as stimulus pulses, or to transmit sensed data back to the main controller unit.
  • Figure 1 is a schematic representation of an implanted plural site system in accordance with this invention.
  • Figure 2A is a block diagram of a controller unit in accordance with this invention which transmits power and data to a plurality of remote units;
  • Figure 2A is a block diagram of a controller unit in accordance with this invention which transmits power and data to a plurality of remote units;
  • 2B is a time representation of a decoded power component and data component, which is transmitted on a high frequency carrier to one or more remote stimulators in accordance with this invention.
  • Figure 3 A is a block diagram of a stimulation and/or sensing device at a remote site
  • Figure 3B is a simplified schematic of a remote device housed in a ceramic can which receives high frequency energy from the controller unit and provides stimulus pulses to a pacing electrode
  • Figure 3C is a simplified circuit diagram showing charging and discharging of an output capacitor for delivering stimulus pulses to a patient's heart from a remote device.
  • Figure 4A is a flow diagram showing the primary steps in the method of this invention whereby a remote device requests power from the controller and maintains itself in a low power mode except when required to be active;
  • Figure 4B is a simplified flow diagram showing the steps at the controller unit taken to deliver power on request;
  • Figure 4C is a flow diagram showing steps for adjusting transmission signal parameters.
  • FIG. 1 there is shown a schematic diagram of a system in accordance with this invention.
  • a main implantable controller unit 25 is illustrated, which provides transmission of power and data to each of remote units 26, 27, 28 and 29 as illustrated. Any number of remote units may be used within the scope of this invention.
  • each remote unit is shown diagrammatically as producing a signal which is delivered to a target location, in this instance in or near the heart.
  • unit 26 delivers pacing or cardioversion pulses to the right atrium
  • remote unit 27 delivers pacing or cardioversion pulses to the right ventricle
  • remote unit 28 delivers pacing or cardioversion pulses to the left atrium
  • remote unit 29 delivers stimulus pulses to another location.
  • each of the remote devices may have one or more electrodes positioned on its case and may be positioned so that the electrodes are in contact with the target site. Alternately, one or more of the remote devices may have a lead for delivering stimulus pulses to a target site.
  • each of units 25-29 is suitably provided with one or more sensors for detecting signals or other data from its environment, and there is two-way data transmission between controller 25 and each of the remote units 26-29.
  • the remote devices such as depicted schematically in Figure 3B are small enough to be implanted with an implant tool such as a catheter.
  • the catheter suitably has a steerable tip or is under stylet control, and is inserted through a vein to the heart.
  • the implant module, or unit is floated in the distal end of the catheter, with the distal electrode exposed.
  • the implant module is fixed to the heart at the desired location. This is done by controlling means either on or in the catheter, the implant module, or both. For example, a tined module can simply be pushed or ejected out of the end of the catheter.
  • a module can be provided with helical fixation means, and can be held in the catheter tip while the catheter is rotated to screw it into the myocardium, after which is it is released. In a known technique, a stylet attached to the implant module might be used to rotate it.
  • FIG 2A there is shown a schematic diagram of an implantable controller unit 25, which in the system and method of this invention provides power for transmission to each of the remote units.
  • Implantable unit 25 is in two-way communications with an external programmer 31 , through a communicator, or transmit/receive subsystem 33.
  • Battery 34 is connected to all of the circuitry of unit 25, meaning that it provides power to each of the blocks illustrated, as is " designated by lead 34 .
  • the battery is shown connected directly to an oscillator/modulator/power converter 36 which performs dual functions.
  • the power converter section receives power from the battery 34 and generates power wave forms, which modulate a carrier signal for carrying power.
  • the modulator portion 36 receives data signals from controller 38, and further modulates the carrier to carry such data signals for transmission to one or more of the remote devices.
  • the output of the modulator/power converter circuit 36 is coupled to transmitter 37, which transmits a high frequency signal containing a power component and a data component.
  • Controller 36 controls the transmission parameters, e.g., carrier frequency and amplitude, as discussed further below. The nature of the power and data wave form are discussed further in connection with Figure 2B below.
  • the construction of the transmitter can be in accord with several approaches.
  • a single point, omni-directional transmitting antenna, made of metal, can be used for high frequency transmission of the energy and data signals.
  • Such an approach has the advantage that the antenna can transmit to plural remote devices and need not be directionally tuned, but requires relatively high energy.
  • Another approach is to use transmitting and receiving antennas configured as primary and secondary transformer windings, oriented for directional transmission.
  • the efficiency depends upon the size of the antennae, and the distance between them, which is generally on the order of 5-8 cm, or several inches.
  • the transmission is substantially perpendicular to each antenna coil.
  • Controller unit 25 additionally has a receiver 42, for receiving high frequency communications from each of the remote devices which are part of the implanted system, e.g., devices 26-29 as shown in Figure 1.
  • the received signals are demodulated in demodulator circuit 43, the demodulated data then being coupled through to controller 38.
  • Controller 38 preferably incorporates a microprocessor and other required timing circuits, for effecting control of modulator/power converter circuit 36.
  • Controller 38 is also in two-way communication with memory 40, for storing data and for receiving algorithms as are called for, in a known fashion.
  • a sensor illustrated as activity sensor 45, which provides input data concerning patient activity, in a manner well known in the pacing art.
  • Electrodes 48 and 49 are illustrated " providing inputs to sensing amplifiers 46, the data from which is likewise coupled to controller 38. Electrodes 48, 49 may be housed either on the controller unit, or may be housed on leads extending from the controller unit; and, of course, such electrodes can be placed on one or more remote devices.
  • the collected data may, as in a pacemaker system, provide signals representative of cardiac activity either for control use or for diagnostic use. Data inputted from sensor 45 and/or electrodes 48. 49 may be collected and transmitted through communicator block 33 to external programmer 31 , for evaluation by a physician.
  • FIG. 2B there is shown a time diagram illustrating the nature of data encoded onto a high frequency carrier, which is transmitted from transmitter 37 to one or more external implanted devices.
  • the carrier is suitably a high frequency carrier.
  • the transmitted waveform must be in a frequency range that allows efficient transmission within the body using small antennae; which transmits power sufficient to carry to the remote units, e.g., up to about 10 cm, while being low enough to be provided by the controller battery over a nominal implant lifetime; and the signal may not be damaging to body tissue or cause unwanted stimulus generation.
  • the frequency is in a range of 30-250 MHZ; high frequencies around 250 MHZ are appropriate.
  • the amplitude of the signal is adjustable, depending on the spacing of the remote units.
  • the amplitude and frequency can be adjusted through controls from programmer 31 ; and in response to signal strength data sent back from the remote unit, as discussed further in connection with Figure 4C.
  • the parameters are interactive, being a function of antenna design, inter-unit geometry, and body conditions such as air in the lungs, liquid in the GI tract, etc. For this reason, the system and method include a transmission parameter test for adjusting frequency and amplitude in order to optimize transmission.
  • a constant asynchronous "trickle charge” signal which is a power carrying signal used to charge up a special purpose capacitor provided in each remote device (see block 58, Figure
  • a reset code as illustrated at 76, to communicate to the remote device that the trickle charge has been completed.
  • an identification code to communicate with one or more particular external devices. This feature is optional, and may be used to direct control data that has been generated at the controller or " received from the external programmer, to selected one or more remote devices.
  • the information or data signal is delivered, as illustrated at 80.
  • This data may be encoded in any desired manner, and carries control data to instruct the remote stimulator or device as to its operation. The manner of encoding and demodulating the data is a matter of design choice, and may be done in any conventional manner.
  • FIG. 3A there is shown a block diagram of a remote device 50, in accordance with this invention.
  • a receiver circuit 52 is provided for receiving and filtering out the carrier signal which has been transmitted from the controller unit, which carrier signal carries both the power and data components.
  • the received signal is decoded in circuit 54, and separated into power and data components.
  • the decoded power component is coupled to rectifier 56, the output of which is a DC voltage which is coupled to a large capacitor, or "SUPER CAP" which is part of power supply 58 for the remote unit.
  • Cap 58 can have a value of about 0.3F, and yet be physically quite small.
  • controller 60 which suitably comprises a microprocessor or equivalent logic and associated memory. Controller 60 is used to control the activities of the remote device, which include delivering stimulus pulses through driver 61 and electrodes 64, and receiving sensed information picked up at electrodes 64 and amplified at 62. These procedures and circuits are well known in the art. Also, as illustrated, an activity sensor 67 or a plurality of sensors provide data inputs to controller 60. This data can be stored for transmission back to the main controller unit, and/or can be used internally for control of the remote device.
  • Controller 60 outputs data through transmitter 66 to controller unit 25.
  • Block 60 includes a suitable high frequency carrier oscillator and modulator.
  • the transmitted data may be sensed data, e.g., data representative of cardiac events for processing at the controller unit; or, as discussed further in connection with Figure 4, it may involve request signals for controlling the transmission of power back to the remote device.
  • sensed data e.g., data representative of cardiac events for processing at the controller unit; or, as discussed further in connection with Figure 4, it may involve request signals for controlling the transmission of power back to the remote device.
  • the processing of sensed information may be divided between the main controller unit 25 and each of the remote units 50, and that such division is a matter of design choice.
  • the assignment of processing tasks may be made through programmer 31 , and relayed by transmission of data to each of the remote units.
  • the controller unit 25 receives data from each of the remote units, and accordingly can process all of this data to make global control decisions.
  • FIG 3B a simplified schematic of an implanted device or module 70 which receives high frequency power from controller unit 25.
  • the implantable device has a housing in the form of a ceramic can 72, which permits efficient penetration of the high frequency signal for reception by the receiver and power supply circuitry which is illustrated at 73.
  • the receiver includes a micro antenna, illustrated schematically at 74. This schematic illustrates flow of power internal to this device from the receiver through to cap 58, and in turn through output circuitry 77 to a pacing button, or surface electrode 75 which is positioned on the ceramic can.
  • a miniature accelerometer 76 is placed within the module, e.g., on the ceramic substrate, to provide capture detection signals.
  • FIG. 3C there is shown a simplified schematic diagram of output circuitry by which stimulus pulses are delivered to a target site, such as the patient's heart.
  • the SUPER CAP 58 delivers energy through a switchable charge circuit 78, which in turn is controlled by controller 60.
  • controller 60 switches discharge circuit 79 to provide a circuit path through the heart, thereby delivering the stimulus pulse in a known and conventional manner.
  • Accelerometer 76 is shown providing input signals to controller 60, for purposes of capture detection. Signals generated by the accelerometer as a result of heart wall motion are used to inform the controller 60 that a contraction has occurred, thus providing capture detection without requiring sophisticated electronics and " associated problems such as electrode polarization.
  • FIGS. 4 A and 4B there are shown simplified flow diagrams illustrating the method of this invention for providing power to one or more of the remote units "on request," i.e., when and as the remote unit signals that it needs power.
  • the routine of Figure 4A which represents steps taken in the remote device, may be run periodically, at any desired interval.
  • events and data received from controller 25 are monitored at 82. Such events may be detection of cardiac P or QRS waves, a cardiac arrhythmia, etc.
  • the routine branches to 85 and goes into full power mode, but if no, it goes to 88 and goes into low power mode. Following this, at 90 it is determined whether the power request flag is presently set. If yes, at 92 the device waits until a power signal has been received, and then goes to 94 to monitor the capacitor. If the power request flag is not on, the routine goes directly from 90 to 94 and monitors the cap. Following monitoring of the charge on the capacitor, at 96 it is determined whether the capacitor needs additional power. If yes, the routine goes to 97 and determines whether the power request flag is already set. If yes, the routine exits; if no, at 98 the flag is set, and a power request signal is transmitted to the main controller. Returning to 96, if the cap does not need power, the routine goes to 100 and determines whether the power request flag is set. If no, the routine exits; if yes, at 101 the flag is reset, and a no power request is sent to the main controller.
  • FIG. 4B there is shown a simplified flow diagram of steps taken at the main controller unit, to regulate transfer of power to one or more remote units.
  • data that has been collected and stored in memory 40 of controller 25 is analyzed, and at 103 a decision is made as to whether to send a wake- up call to a unit, to make sure it is in a full power mode.
  • a wake-up call may be initiated, for example, by a decision to have a remote pacemaker unit go through a threshold test, or by a decision that regular pacing activity should be resumed because of monitored data or received programmer information.
  • the routine branches to block 104, and sends a wake-up call to a designated remote unit; then at block 106 controller 38 controls unit 25 to send power to the unit.
  • the routine goes to block 105 and determines whether there has been a power request from a remote device.
  • a remote device if there is more than one remote device, as in the preferred embodiment of this invention, a determination is made with respect to each such remote device. If there has been a power request, the routine goes to 106 and sends power in the normal manner. If there has been no power request flag, the routine exits.
  • FIG. 4C there is shown a flow diagram of the primary steps taken in performing a test to determine whether there should be any parameter adjustment of the signal transmitted from controller 25 to one or more remote devices.
  • the frequency and amplitude parameters are affected by conditions in the body, such that they should adjusted at time of implant and subsequently.
  • the routine of Figure 4C shows a technique for determining at the remote site the effect of changing parameters, and providing feedback to the main controller for a determination of whether an adjustment can be made to improve efficiency.
  • the program can be initiated by a command from an external programmer, or can be automatically initiated by the implanted system, e.g., once a week or at any other desired interval.
  • the routine scans the controller transmit frequency through a predetermined range, e.g., delivers power signals carrying a trickle charge 75 as seen in Figure 2B with a first frequency n times, then increments the frequency and delivers the next n transmissions, etc.
  • a predetermined range e.g., delivers power signals carrying a trickle charge 75 as seen in Figure 2B with a first frequency n times, then increments the frequency and delivers the next n transmissions, etc.
  • an identification or sync pulse is transmitted between power transmissions, to indicate frequency steps during the scan.
  • signals are generated at decoder 54 representing the level of the received power signal, and these levels along with the identification or sync data are stored in controller 60, as indicated at 122.
  • the controller After the frequency scan, at 123 the controller goes through a scan of signal amplitude, and again, as indicated at 125, the decoder detects the received signals and stores representations of the power levels associated with the different amplitude transmissions. Following the two scans, at 126 the remote device transmits the stored data back to the controller. At 128, the main controller analyzes the data, and determines therefrom whether an adjustment of frequency or amplitude is indicated, so as to improve efficiency of power transmission. For example, the data may indicate that a certain frequency shift results in a relatively significant increase in received power without any increase in transmitted power; while an increase in transmitted power due to an amplitude increase does not provide a proportionate increase in received power.
  • the transmitter parameters can be initially adjusted for efficient operation.
  • the parameters are tuned to adapt to changed body circumstances so as to maintain optimally efficient transmission.
  • Such transmitter adjustment along with the above-described technique of providing power to each remote device upon request, enables efficient power transfer to each remote device.

Abstract

There is provided an implantable system and method for delivering stimulus pulses and/or collecting data from a plurality of sites within a patient's body, having a main controller device with a power source, a stimulator/sensing devices at each of said sites, and circuitry for high frequency transmission of power from the main unit to each of the remote devices. Power is transferred by converting it into a high frequency at the controller unit, and periodically or on request transmitting it to the respective devices. The main controller unit and each respective device also preferably has one or more sensors for collecting data and processor circuitry for analyzing such data. Each remote device has a transmitter for transmitting collected data back to the main controller; the main controller has encoding circuitry for encoding a data component onto the high frequency carrier along with the power component. The controller unit and the respective devices are also equipped with circuitry for controlling power transmission on a need basis, i.e., when the remote device needs power and requests it. The system also performs a transmission parameter test, and adjusts parameters of the transmitted signal, such as frequency and amplitude, as may be indicated.

Description

LEADLESS MULTISITE IMPLANT ABLE STIMULUS AND DIAGNOSTIC SYSTEM Field of the Invention
This invention relates to implantable medical systems for delivery of stimulation treatment and the like and, particularly, leadless systems having multiple stimulus and/or data collection sites.
BACKGROUND OF THE INVENTION Implantable medical treatment systems have achieved great success and have come into widespread use in recent decades. For example, pacing systems, including implanted pacemakers, are widely used to treat various cardiac conditions by delivery of stimulus pulses to the heart.. Another development is that of the implantable defibrillator, or pacemaker/cardioverter/defibrillator for delivering different types of shock therapy to a patient's heart, as well as pacing pulses. Other areas that are under development and are being explored include implantable diagnostic devices for collecting information concerning the activity of a patient's heart or other organ, and relay of collected data to an external programmer; and various neuro stimulation devices.
The development of increasingly sophisticated implantable medical systems has led to a desire for a greater system capability in terms of applying stimuli to different selected sites, or locations, as well as collecting data from different sites in order to control the manner of stimulation automatically or to transmit collected data to the physician for evaluation. The desire to expand implanted systems in order to treat plural sites creates a need for increased system flexibility, but without substantial increase of system cost. An important aspect of providing such multisite systems is that of simplifying the power requirements at each site. If plural sites are utilized but each site requires a special purpose lead connected to a common device for delivering stimulus pulses and/or collecting data, this may result in a complex system requiring extensive implant time, such that many physicians may not want to deal with it. Moreover, in implanted pacemaker systems, the long-term reliability for the lead or leads remains a potential problem, or "weak link" in the system. For example, a pacing lead is subject to about 38 million flexes per year, it is subject to the body's defense mechanisms, and is placed in an extremely hostile environments. The result is that conductors fracture, insulation degrades for various reasons, and the leads can become infected. As is known, removal of chronically implanted leads is extremely difficult. In addition, when two or more leads are involved, the problems are compounded. The more hardware there is implanted, the greater is the risk of thrombosis (embolism, thoracic outlet syndrome, SVC syndrome, etc.), infection, valvular, and other tissue damage, etc. Thus, in an ideal system such leads are eliminated entirely. However, a leadless plural site system where each site has an implanted device with its own battery source likewise has the problem of substantial additional expense attributable to the need of having a battery for each remote implanted device at each respective remote site. The prior art provides examples of wireless data communication between two or more sites within a patient. For example, U.S. Patent 5,411,535 discloses a pacer system where data is sent from a main pacer unit to remote electrode units, for controlling delivery of pace pulses as well as providing sensed data from the electrode units back to the main pacer. However, each remote location has its own battery supply. See also U.S. Patent 5,405,367, which discloses multiple stimulators devices at different sites. Each of the implanted stimulator devices receives energy from an alternating magnetic field, i.e., through a transformer, from an external source. A transparent difficulty with this system is that it requires frequent if not substantially continuous transfer from an external source to the implanted devices, which would be an unacceptable arrangement in most cases. See also U.S. Patent.
4,886,064, which discloses sensor units separate from an implanted pacemaker unit, where the sensor units wirelessly transmit data to the pacemaker. However, each sensor unit has its own battery power source.
The prior art thus shows transformer-type coupling of energy from an external source to an implanted system, and wireless transmission of data between multiple implanted devices in a patient. What is desirable in order to expand system capability for treatment at multiple patient sites is a more flexible implantable system with devices at plural sites; a system that does not require multiple leads from the implantable stimulator to the respective plural sites; and a system that has the capability of transmitting power from a single battery source to the respective site devices on an efficient basis.
SUMMARY OF THE INVENTION It is an overall object of this invention to provide an implantable leadless system for stimulating plural sites in a patient and/or collecting data from such sites for external transmission. As used herein, the term "leadless" refers to the absence of a lead interconnecting the plural sites, it being understood that one or more of the site devices of the system may have a lead for delivery of stimulus pulses and/or sensing data. The flexible system and method of this invention has the aim of providing a power source, e.g., a battery, in a central controller, and transmitting capability for transmitting power from the central controller to a remote device or to each of a plurality of remote site devices, the transmission being controlled in order to optimize power efficiency.
In accordance with the above object, there is provided an implantable system and method for pacing or otherwise treating a patient and/or for collecting data, the system having a controller unit and one or more site-specific devices separate from the controller unit, where the controller unit has a power source and a transmitter for transmitting to each remote device a high frequency signal comprising at least a power component derived from the power source. Each remote unit in the system has a receiver for receiving the high frequency signal and a circuit for deriving power from it, and a power supply for storing the derived power and powering the unit. Further, the system preferably has the capability of transmitting data from the main controller unit along with the power, with a power component and a data component being modulated onto a common carrier for transmission to one or more of the remote devices. Similarly, each remote device has a transmitter for transmitting sensed data back to the main controller unit.
In a further embodiment of the invention, the system comprises capability for controlling the high frequency power transmission as a function of the" power requirements or demand at each remote unit. In this embodiment, each remote unit operates on a very low power basis except when system demand calls for it to deliver a treatment such as stimulus pulses, or to transmit sensed data back to the main controller unit. BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1 is a schematic representation of an implanted plural site system in accordance with this invention. Figure 2A is a block diagram of a controller unit in accordance with this invention which transmits power and data to a plurality of remote units; Figure
2B is a time representation of a decoded power component and data component, which is transmitted on a high frequency carrier to one or more remote stimulators in accordance with this invention.
Figure 3 A is a block diagram of a stimulation and/or sensing device at a remote site; Figure 3B is a simplified schematic of a remote device housed in a ceramic can which receives high frequency energy from the controller unit and provides stimulus pulses to a pacing electrode; Figure 3C is a simplified circuit diagram showing charging and discharging of an output capacitor for delivering stimulus pulses to a patient's heart from a remote device.
Figure 4A is a flow diagram showing the primary steps in the method of this invention whereby a remote device requests power from the controller and maintains itself in a low power mode except when required to be active; Figure 4B is a simplified flow diagram showing the steps at the controller unit taken to deliver power on request; Figure 4C is a flow diagram showing steps for adjusting transmission signal parameters.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
Referring now to Figure 1 , there is shown a schematic diagram of a system in accordance with this invention. A main implantable controller unit 25 is illustrated, which provides transmission of power and data to each of remote units 26, 27, 28 and 29 as illustrated. Any number of remote units may be used within the scope of this invention. As illustrated, each remote unit is shown diagrammatically as producing a signal which is delivered to a target location, in this instance in or near the heart. Thus, unit 26 delivers pacing or cardioversion pulses to the right atrium; remote unit 27 delivers pacing or cardioversion pulses to the right ventricle; remote unit 28 delivers pacing or cardioversion pulses to the left atrium; and remote unit 29 delivers stimulus pulses to another location. For example, septal stimulation adjacent to the right ventricular outflow tract (RVOT) would capture the conduction system, which has value in providing better cardiac output due to a more natural contraction pattern, potentially useful for CHF. Stimulation can be directed to other areas near the RVOT, for treating HOCM by stimulating the septum to contract before the rest of the ventricle. Each of the remote devices may have one or more electrodes positioned on its case and may be positioned so that the electrodes are in contact with the target site. Alternately, one or more of the remote devices may have a lead for delivering stimulus pulses to a target site. As discussed further hereinbelow, each of units 25-29 is suitably provided with one or more sensors for detecting signals or other data from its environment, and there is two-way data transmission between controller 25 and each of the remote units 26-29.
In practice, the remote devices such as depicted schematically in Figure 3B are small enough to be implanted with an implant tool such as a catheter. The catheter suitably has a steerable tip or is under stylet control, and is inserted through a vein to the heart. The implant module, or unit, is floated in the distal end of the catheter, with the distal electrode exposed. After an appropriate location is found by the physician, e.g., by using typical parameters such as P-wave amplitudes in the atrium or ventricular thresholds, the implant module is fixed to the heart at the desired location. This is done by controlling means either on or in the catheter, the implant module, or both. For example, a tined module can simply be pushed or ejected out of the end of the catheter. A module can be provided with helical fixation means, and can be held in the catheter tip while the catheter is rotated to screw it into the myocardium, after which is it is released. In a known technique, a stylet attached to the implant module might be used to rotate it. Referring now to Figure 2A, there is shown a schematic diagram of an implantable controller unit 25, which in the system and method of this invention provides power for transmission to each of the remote units. Implantable unit 25 is in two-way communications with an external programmer 31 , through a communicator, or transmit/receive subsystem 33. Battery 34 is connected to all of the circuitry of unit 25, meaning that it provides power to each of the blocks illustrated, as is" designated by lead 34 . The battery is shown connected directly to an oscillator/modulator/power converter 36 which performs dual functions. First, the power converter section receives power from the battery 34 and generates power wave forms, which modulate a carrier signal for carrying power. Further, the modulator portion 36 receives data signals from controller 38, and further modulates the carrier to carry such data signals for transmission to one or more of the remote devices. The output of the modulator/power converter circuit 36 is coupled to transmitter 37, which transmits a high frequency signal containing a power component and a data component. Controller 36 controls the transmission parameters, e.g., carrier frequency and amplitude, as discussed further below. The nature of the power and data wave form are discussed further in connection with Figure 2B below.
The construction of the transmitter can be in accord with several approaches. A single point, omni-directional transmitting antenna, made of metal, can be used for high frequency transmission of the energy and data signals. Such an approach has the advantage that the antenna can transmit to plural remote devices and need not be directionally tuned, but requires relatively high energy. Another approach is to use transmitting and receiving antennas configured as primary and secondary transformer windings, oriented for directional transmission. Here, the efficiency depends upon the size of the antennae, and the distance between them, which is generally on the order of 5-8 cm, or several inches. For this directional arrangement, the transmission is substantially perpendicular to each antenna coil.
Controller unit 25 additionally has a receiver 42, for receiving high frequency communications from each of the remote devices which are part of the implanted system, e.g., devices 26-29 as shown in Figure 1. The received signals are demodulated in demodulator circuit 43, the demodulated data then being coupled through to controller 38. Controller 38 preferably incorporates a microprocessor and other required timing circuits, for effecting control of modulator/power converter circuit 36. Controller 38 is also in two-way communication with memory 40, for storing data and for receiving algorithms as are called for, in a known fashion. Additionally connected to controller 38 is a sensor, illustrated as activity sensor 45, which provides input data concerning patient activity, in a manner well known in the pacing art. This data is processed by controller 38 and used for controlling the modulation carried out in block 36. Additionally, electrodes 48 and 49 are illustrated" providing inputs to sensing amplifiers 46, the data from which is likewise coupled to controller 38. Electrodes 48, 49 may be housed either on the controller unit, or may be housed on leads extending from the controller unit; and, of course, such electrodes can be placed on one or more remote devices. The collected data may, as in a pacemaker system, provide signals representative of cardiac activity either for control use or for diagnostic use. Data inputted from sensor 45 and/or electrodes 48. 49 may be collected and transmitted through communicator block 33 to external programmer 31 , for evaluation by a physician. Referring now to Figure 2B, there is shown a time diagram illustrating the nature of data encoded onto a high frequency carrier, which is transmitted from transmitter 37 to one or more external implanted devices. The carrier, not shown, is suitably a high frequency carrier. The transmitted waveform must be in a frequency range that allows efficient transmission within the body using small antennae; which transmits power sufficient to carry to the remote units, e.g., up to about 10 cm, while being low enough to be provided by the controller battery over a nominal implant lifetime; and the signal may not be damaging to body tissue or cause unwanted stimulus generation. The frequency is in a range of 30-250 MHZ; high frequencies around 250 MHZ are appropriate. The amplitude of the signal is adjustable, depending on the spacing of the remote units. The amplitude and frequency can be adjusted through controls from programmer 31 ; and in response to signal strength data sent back from the remote unit, as discussed further in connection with Figure 4C. The parameters are interactive, being a function of antenna design, inter-unit geometry, and body conditions such as air in the lungs, liquid in the GI tract, etc. For this reason, the system and method include a transmission parameter test for adjusting frequency and amplitude in order to optimize transmission.
Still referring to Figure 2B at 75 there is shown a constant asynchronous "trickle charge" signal, which is a power carrying signal used to charge up a special purpose capacitor provided in each remote device (see block 58, Figure
3A). Following this in time sequence, there may optionally be a reset code as illustrated at 76, to communicate to the remote device that the trickle charge has been completed. Following this in time, at 78 there is delivered an identification code to communicate with one or more particular external devices. This feature is optional, and may be used to direct control data that has been generated at the controller or" received from the external programmer, to selected one or more remote devices. Following this, the information or data signal is delivered, as illustrated at 80. This data may be encoded in any desired manner, and carries control data to instruct the remote stimulator or device as to its operation. The manner of encoding and demodulating the data is a matter of design choice, and may be done in any conventional manner. The power is transmitted between "events" such as stimulation, sensing data transmission from a remote unit, etc. Referring now to Figure 3A, there is shown a block diagram of a remote device 50, in accordance with this invention. A receiver circuit 52 is provided for receiving and filtering out the carrier signal which has been transmitted from the controller unit, which carrier signal carries both the power and data components. The received signal is decoded in circuit 54, and separated into power and data components. The decoded power component is coupled to rectifier 56, the output of which is a DC voltage which is coupled to a large capacitor, or "SUPER CAP" which is part of power supply 58 for the remote unit. Cap 58 can have a value of about 0.3F, and yet be physically quite small. Such a capacitance value is large enough to power the device for pacing for several weeks before needing a trickle recharge, by using modern low threshold, high impedance electrodes. Power supply 58 provides power to all circuitry of the device, as indicated by arrow 58 . Returning to decode block 54, the data component of the received signal is coupled to controller 60, which suitably comprises a microprocessor or equivalent logic and associated memory. Controller 60 is used to control the activities of the remote device, which include delivering stimulus pulses through driver 61 and electrodes 64, and receiving sensed information picked up at electrodes 64 and amplified at 62. These procedures and circuits are well known in the art. Also, as illustrated, an activity sensor 67 or a plurality of sensors provide data inputs to controller 60. This data can be stored for transmission back to the main controller unit, and/or can be used internally for control of the remote device.
Controller 60 outputs data through transmitter 66 to controller unit 25. Block 60 includes a suitable high frequency carrier oscillator and modulator. The transmitted data may be sensed data, e.g., data representative of cardiac events for processing at the controller unit; or, as discussed further in connection with Figure 4, it may involve request signals for controlling the transmission of power back to the remote device. I is to be understood that the processing of sensed information may be divided between the main controller unit 25 and each of the remote units 50, and that such division is a matter of design choice. Thus, at the time of implant, the assignment of processing tasks may be made through programmer 31 , and relayed by transmission of data to each of the remote units. Of course, the controller unit 25 receives data from each of the remote units, and accordingly can process all of this data to make global control decisions. Referring now to Figure 3B, there is shown a simplified schematic of an implanted device or module 70 which receives high frequency power from controller unit 25. The implantable device has a housing in the form of a ceramic can 72, which permits efficient penetration of the high frequency signal for reception by the receiver and power supply circuitry which is illustrated at 73. The receiver includes a micro antenna, illustrated schematically at 74. This schematic illustrates flow of power internal to this device from the receiver through to cap 58, and in turn through output circuitry 77 to a pacing button, or surface electrode 75 which is positioned on the ceramic can. The use of one or more surface pacing electrodes 75 in this manner enables implantation and positioning of devices to deliver the desired treatment signals without the use of a lead, as discussed above. A miniature accelerometer 76 is placed within the module, e.g., on the ceramic substrate, to provide capture detection signals.
Referring now to Figure 3C, there is shown a simplified schematic diagram of output circuitry by which stimulus pulses are delivered to a target site, such as the patient's heart. The SUPER CAP 58 delivers energy through a switchable charge circuit 78, which in turn is controlled by controller 60. When the charge circuit is switched to a charge position, power from CAP 58 is delivered across output capacitor C0- When the capacitor is charged, and it is time to deliver a stimulus pulse to the heart, controller 60 switches discharge circuit 79 to provide a circuit path through the heart, thereby delivering the stimulus pulse in a known and conventional manner. Accelerometer 76 is shown providing input signals to controller 60, for purposes of capture detection. Signals generated by the accelerometer as a result of heart wall motion are used to inform the controller 60 that a contraction has occurred, thus providing capture detection without requiring sophisticated electronics and" associated problems such as electrode polarization.
Referring now to Figures 4 A and 4B, there are shown simplified flow diagrams illustrating the method of this invention for providing power to one or more of the remote units "on request," i.e., when and as the remote unit signals that it needs power. The routine of Figure 4A, which represents steps taken in the remote device, may be run periodically, at any desired interval. At the start of the routine, events and data received from controller 25 are monitored at 82. Such events may be detection of cardiac P or QRS waves, a cardiac arrhythmia, etc. At 84, it is determined whether there has been a wake-up command from the main controller. If yes, the routine immediately goes to 85 and sets the remote device in full power mode. If no, the routine goes to 87 and determines whether an event has been detected that requires power. If yes, the routine branches to 85 and goes into full power mode, but if no, it goes to 88 and goes into low power mode. Following this, at 90 it is determined whether the power request flag is presently set. If yes, at 92 the device waits until a power signal has been received, and then goes to 94 to monitor the capacitor. If the power request flag is not on, the routine goes directly from 90 to 94 and monitors the cap. Following monitoring of the charge on the capacitor, at 96 it is determined whether the capacitor needs additional power. If yes, the routine goes to 97 and determines whether the power request flag is already set. If yes, the routine exits; if no, at 98 the flag is set, and a power request signal is transmitted to the main controller. Returning to 96, if the cap does not need power, the routine goes to 100 and determines whether the power request flag is set. If no, the routine exits; if yes, at 101 the flag is reset, and a no power request is sent to the main controller.
Referring now to Figure 4B, there is shown a simplified flow diagram of steps taken at the main controller unit, to regulate transfer of power to one or more remote units. At 102, data that has been collected and stored in memory 40 of controller 25 is analyzed, and at 103 a decision is made as to whether to send a wake- up call to a unit, to make sure it is in a full power mode. Such a wake-up call may be initiated, for example, by a decision to have a remote pacemaker unit go through a threshold test, or by a decision that regular pacing activity should be resumed because of monitored data or received programmer information. If a wake-up call is to be sent, the routine branches to block 104, and sends a wake-up call to a designated remote unit; then at block 106 controller 38 controls unit 25 to send power to the unit. "
If no wake-up call is to be sent, the routine goes to block 105 and determines whether there has been a power request from a remote device.. Of course, if there is more than one remote device, as in the preferred embodiment of this invention, a determination is made with respect to each such remote device. If there has been a power request, the routine goes to 106 and sends power in the normal manner. If there has been no power request flag, the routine exits.
Referring now to Figure 4C, there is shown a flow diagram of the primary steps taken in performing a test to determine whether there should be any parameter adjustment of the signal transmitted from controller 25 to one or more remote devices. As discussed above, the frequency and amplitude parameters are affected by conditions in the body, such that they should adjusted at time of implant and subsequently. The routine of Figure 4C shows a technique for determining at the remote site the effect of changing parameters, and providing feedback to the main controller for a determination of whether an adjustment can be made to improve efficiency. The program can be initiated by a command from an external programmer, or can be automatically initiated by the implanted system, e.g., once a week or at any other desired interval. At step 120, the routine scans the controller transmit frequency through a predetermined range, e.g., delivers power signals carrying a trickle charge 75 as seen in Figure 2B with a first frequency n times, then increments the frequency and delivers the next n transmissions, etc. Suitably an identification or sync pulse is transmitted between power transmissions, to indicate frequency steps during the scan. When the respective signals are received at remote device 50, signals are generated at decoder 54 representing the level of the received power signal, and these levels along with the identification or sync data are stored in controller 60, as indicated at 122. After the frequency scan, at 123 the controller goes through a scan of signal amplitude, and again, as indicated at 125, the decoder detects the received signals and stores representations of the power levels associated with the different amplitude transmissions. Following the two scans, at 126 the remote device transmits the stored data back to the controller. At 128, the main controller analyzes the data, and determines therefrom whether an adjustment of frequency or amplitude is indicated, so as to improve efficiency of power transmission. For example, the data may indicate that a certain frequency shift results in a relatively significant increase in received power without any increase in transmitted power; while an increase in transmitted power due to an amplitude increase does not provide a proportionate increase in received power. By performing this test at the time of system implant, the transmitter parameters can be initially adjusted for efficient operation. By subsequently performing the test periodically, the parameters are tuned to adapt to changed body circumstances so as to maintain optimally efficient transmission. Such transmitter adjustment, along with the above-described technique of providing power to each remote device upon request, enables efficient power transfer to each remote device.

Claims

1. An implantable stimulating system for stimulating a patient, said system having a controller unit and at least one stimulating unit remote from said controller unit, said controller unit having a power source, data generation means for generating data signals, and first transmission means connected to said power source and said data generation means for transmitting to said at least one stimulating unit high frequency signals comprising a power component derived from said power source and a data component carrying said data signals, and said at least one stimulating unit comprising stimulating means for providing stimulus pulses to said patient, receiving means for receiving said high frequency signals and separating therefrom said power and data components, supply means for receiving said separated power component and storing power from same for powering said at least one stimulating unit, and control means for using said separated data component to control operation of said pacing means.
2. The system as described in claim 1, wherein said first transmission means comprises periodic means for periodically transmitting said high frequency signal with at least said power component, whereby power is periodically received and stored by said stimulating unit.
3. The system as described in claim 1, wherein said at least one stimulating unit comprises data means for obtaining second data signals representative of patient cardiac activity, and second transmission means for sending said second data signals to said controller unit; and said controller unit comprises second receiving means for receiving said second data signals.
4. The system as described in claim 3, wherein said at least one stimulating unit comprises power request means for controlling said second transmission means to send request signals requesting power transmission from said controller unit, and said controller unit has power respond means for initiating transmission of a said high frequency signal with said power component in response to receipt of said request signals.
5. The system as described in claim 3, wherein said at least one stimulating unit comprises second sensor means for sensing patient parameters and for generating said second data signals to represent said patient parameters..
6. The system as described in claim 1, wherein said controller unit comprises first sensor means for sensing signals representative of patient cardiac activity and for generating first cardiac data representative of said cardiac activity, and said data generation means comprises encoding means for encoding said data signals with said first cardiac data.
7. The system as described in claim 6, wherein said first sensor means further senses signals representative of patient physical activity.
8. The system as described in claim 1, wherein said first transmission means has time means for time separating the transmission of said power and data components.
9. The system as described in claim 1, wherein said first transmission means has converting means for converting power from said power source into a said high frequency signal, and modulation means for modulating said high frequency signal with said data component.
10. An implantable system for delivering stimulus pulses to a plurality of respective locations in a patient, comprising: a first device having a power source and transmitting means for transmitting high frequency signals carrying power external to said first device; and a plurality of respective second devices, each positioned at a respective one of said locations, each of said second devices having receiving means for receiving power transmitted by said first device and stimulus means for delivering stimulus pulses to said patient.
1 1. The system as described in claim 10, wherein said transmitting means has a high frequency signal source and modulating means for modulating said high frequency signals with a power signal.
12. The system as described in claim 11, wherein said first device has data encoding means for encoding data control signals on said high frequency signals, whereby said signals carry a power component and a data component.
13. The system as described in claim 10, wherein each said second device comprises a sensor for sensing patient information, and control means for controlling operation of said second device as a function of said patient information.
14. The system as described in claim 13, wherein each said second device comprises a transmitter for transmitting data representative of said patient information to said first device.
15. The system as described in claim 10, wherein said first device has sensor means for sensing patient data, and data encoding means for encoding said patient data to modulate said high frequency signals with said data.
16. The system as described in claim 10, wherein said first device comprises a power transfer controller for controlling the timing of transmitting said high frequency signals.
17. The system as described in claim 10, wherein each of said" second devices comprises circuits for carrying out predetermined functions, and comprising power control means for controlling delivery of power from said receiving means to at least some of said circuits.
18. The system as described in claim 10, wherein each of said second devices has request means for transmitting to said first device a request for transmission of power to it.
19. The system as described in claim 10, wherein each of said second devices comprises circuits for performing plurality of predetermined functions and control means for controlling at least some of said circuits to operate in a power sleep or awake mode, and wherein said first device comprises wake-up means for transmitting an instruction to at least one of said second devices to control said circuits to operate in an awake mode.
20. A method for delivering power to a plurality of devices positioned at respective locations in a patient's body, comprising: providing a main device having a power source; generating in said main device high frequency signals encoded with a power component, and transmitting said signals to said plurality of devices.
21. The method as described in claim 20, comprising encoding control data on said high frequency signals, and transmitting said high frequency signals with said control data to at least one of said plurality of devices.
22. The method as described in claim 20, comprising controlling each of said plurality of devices to operate in a sleep or awake mode.
23. The method as described in claim 22, wherein comprising transmitting a signal from one of said plurality of devices to said main device to request a power transmission to it.
24. The method as described in claim 23, comprising transmitting ' from said main device to at least one of said plurality devices a command to operate in the awake mode.
25. The method as described in claim 20, comprising varying one or more parameters of said high frequency signals, detecting the received signals at a remote device, sending data representative of said received signals from said remote device to said main device, and adjusting said one or more parameters as a function of said representative data.
26. An implantable system having at least one remote unit at a given body site and a main device equipped with a battery power source, said at least one remote unit having receiving means for receiving power from high frequency signals and storage means for storing said received power, said main device having transmitter means for transmitting high frequency signals carrying at least a power component to said remote unit.
27. The system as described in claim 26, wherein said main device has control means for controlling the timing of transmitting said high frequency signals to said at least one remote unit.
28. The system as described in claim 27, wherein said main device has adjust means for adjusting a parameter of said high frequency signals.
29. The system as described in claim 28, comprising a plurality of said remote units, each positioned at a respective given body site.
30. The system as described in claim 29, wherein each said remote unit has data collection means for collecting data representative of its operation, and remote transmission means for transmitting said collected data to said main device, and said control means has means for performing said controlling as a function of said collected data.
31. The system as described in claim 30, wherein said control " means has means for performing said adjusting as a function of said collected data.
PCT/US1997/023012 1996-12-18 1997-12-10 Leadless multisite implantable stimulus and diagnostic system WO1998026840A1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU55267/98A AU5526798A (en) 1996-12-18 1997-12-10 Leadless multisite implantable stimulus and diagnostic system

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US08/768,384 US5814089A (en) 1996-12-18 1996-12-18 Leadless multisite implantable stimulus and diagnostic system
US08/768,384 1996-12-18

Publications (1)

Publication Number Publication Date
WO1998026840A1 true WO1998026840A1 (en) 1998-06-25

Family

ID=25082340

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1997/023012 WO1998026840A1 (en) 1996-12-18 1997-12-10 Leadless multisite implantable stimulus and diagnostic system

Country Status (3)

Country Link
US (1) US5814089A (en)
AU (1) AU5526798A (en)
WO (1) WO1998026840A1 (en)

Cited By (85)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1222943A1 (en) * 2001-01-16 2002-07-17 Kenergy Inc Wireless cardiac pacing system with vascular electrode-stents
WO2006124833A2 (en) * 2005-05-18 2006-11-23 Cardiac Pacemakers, Inc. Modular antitachyarrhythmia therapy system
EP1744809A1 (en) * 2004-05-04 2007-01-24 University Of Rochester Leadless implantable intravascular electrophysiologic device for neurologic/cardiovascular sensing and stimulation
WO2007019207A1 (en) * 2005-08-08 2007-02-15 Kenergy, Inc. Intravascular stimulation system with wireless power supply
WO2007090014A1 (en) 2006-01-31 2007-08-09 Medtronic, Inc Subcutaneous icd with separate cardiac rhythm sensor
WO2007087875A1 (en) * 2006-01-13 2007-08-09 Universität Duisburg-Essen Stimulation system, in particular a cardiac pacemaker
FR2903912A1 (en) * 2006-07-20 2008-01-25 Commissariat Energie Atomique Implantable pacemaker for treating e.g. bradycardia, has control modules each including control system to modify stimulation parameters of heart via actuator module if difference between contraction signals exceeds fixed threshold
WO2008034005A2 (en) * 2006-09-13 2008-03-20 Boston Scientific Scimed, Inc. Cardiac stimulation using leadless electrode assemblies
WO2008066424A1 (en) * 2006-11-30 2008-06-05 St. Jude Medical Ab Device and method for initiating communication with a selected implantable medical device by means of a directional antenna
US7894915B1 (en) 2006-10-27 2011-02-22 Pacesetter, Inc. Implantable medical device
US7899537B1 (en) 2006-10-27 2011-03-01 Pacesetter, Inc. Pericardial cardioverter defibrillator
WO2012007131A1 (en) * 2010-07-13 2012-01-19 Peter Osypka Central control unit of implants
US8180456B2 (en) 2009-06-09 2012-05-15 Pacesetter, Inc. Systems and methods to configure a multi-electrode lead
US8849416B2 (en) 2004-05-04 2014-09-30 University Of Rochester Implantable bio-electro-physiologic interface matrix
US9072911B2 (en) 2004-10-20 2015-07-07 Boston Scientific Scimed, Inc. Leadless cardiac stimulation systems
US9308374B2 (en) 2006-07-21 2016-04-12 Boston Scientific Scimed, Inc. Delivery of cardiac stimulation devices
US9393405B2 (en) 2008-02-07 2016-07-19 Cardiac Pacemakers, Inc. Wireless tissue electrostimulation
US9526909B2 (en) 2014-08-28 2016-12-27 Cardiac Pacemakers, Inc. Medical device with triggered blanking period
US9545513B2 (en) 2004-10-20 2017-01-17 Cardiac Pacemakers, Inc. Leadless cardiac stimulation systems
US9592391B2 (en) 2014-01-10 2017-03-14 Cardiac Pacemakers, Inc. Systems and methods for detecting cardiac arrhythmias
US9669230B2 (en) 2015-02-06 2017-06-06 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
US9853743B2 (en) 2015-08-20 2017-12-26 Cardiac Pacemakers, Inc. Systems and methods for communication between medical devices
US9956414B2 (en) 2015-08-27 2018-05-01 Cardiac Pacemakers, Inc. Temporal configuration of a motion sensor in an implantable medical device
US9968787B2 (en) 2015-08-27 2018-05-15 Cardiac Pacemakers, Inc. Spatial configuration of a motion sensor in an implantable medical device
US10022538B2 (en) 2005-12-09 2018-07-17 Boston Scientific Scimed, Inc. Cardiac stimulation system
US10029107B1 (en) 2017-01-26 2018-07-24 Cardiac Pacemakers, Inc. Leadless device with overmolded components
US10050700B2 (en) 2015-03-18 2018-08-14 Cardiac Pacemakers, Inc. Communications in a medical device system with temporal optimization
US10046167B2 (en) 2015-02-09 2018-08-14 Cardiac Pacemakers, Inc. Implantable medical device with radiopaque ID tag
US10065041B2 (en) 2015-10-08 2018-09-04 Cardiac Pacemakers, Inc. Devices and methods for adjusting pacing rates in an implantable medical device
US10092760B2 (en) 2015-09-11 2018-10-09 Cardiac Pacemakers, Inc. Arrhythmia detection and confirmation
US10137305B2 (en) 2015-08-28 2018-11-27 Cardiac Pacemakers, Inc. Systems and methods for behaviorally responsive signal detection and therapy delivery
US10159842B2 (en) 2015-08-28 2018-12-25 Cardiac Pacemakers, Inc. System and method for detecting tamponade
US10183170B2 (en) 2015-12-17 2019-01-22 Cardiac Pacemakers, Inc. Conducted communication in a medical device system
US10213610B2 (en) 2015-03-18 2019-02-26 Cardiac Pacemakers, Inc. Communications in a medical device system with link quality assessment
US10220213B2 (en) 2015-02-06 2019-03-05 Cardiac Pacemakers, Inc. Systems and methods for safe delivery of electrical stimulation therapy
US10226631B2 (en) 2015-08-28 2019-03-12 Cardiac Pacemakers, Inc. Systems and methods for infarct detection
US10328272B2 (en) 2016-05-10 2019-06-25 Cardiac Pacemakers, Inc. Retrievability for implantable medical devices
US10350423B2 (en) 2016-02-04 2019-07-16 Cardiac Pacemakers, Inc. Delivery system with force sensor for leadless cardiac device
US10357159B2 (en) 2015-08-20 2019-07-23 Cardiac Pacemakers, Inc Systems and methods for communication between medical devices
US10391319B2 (en) 2016-08-19 2019-08-27 Cardiac Pacemakers, Inc. Trans septal implantable medical device
US10413733B2 (en) 2016-10-27 2019-09-17 Cardiac Pacemakers, Inc. Implantable medical device with gyroscope
US10426962B2 (en) 2016-07-07 2019-10-01 Cardiac Pacemakers, Inc. Leadless pacemaker using pressure measurements for pacing capture verification
US10434317B2 (en) 2016-10-31 2019-10-08 Cardiac Pacemakers, Inc. Systems and methods for activity level pacing
US10434314B2 (en) 2016-10-27 2019-10-08 Cardiac Pacemakers, Inc. Use of a separate device in managing the pace pulse energy of a cardiac pacemaker
US10463305B2 (en) 2016-10-27 2019-11-05 Cardiac Pacemakers, Inc. Multi-device cardiac resynchronization therapy with timing enhancements
US10512784B2 (en) 2016-06-27 2019-12-24 Cardiac Pacemakers, Inc. Cardiac therapy system using subcutaneously sensed P-waves for resynchronization pacing management
US10561330B2 (en) 2016-10-27 2020-02-18 Cardiac Pacemakers, Inc. Implantable medical device having a sense channel with performance adjustment
US10583303B2 (en) 2016-01-19 2020-03-10 Cardiac Pacemakers, Inc. Devices and methods for wirelessly recharging a rechargeable battery of an implantable medical device
US10583301B2 (en) 2016-11-08 2020-03-10 Cardiac Pacemakers, Inc. Implantable medical device for atrial deployment
US10617874B2 (en) 2016-10-31 2020-04-14 Cardiac Pacemakers, Inc. Systems and methods for activity level pacing
US10632313B2 (en) 2016-11-09 2020-04-28 Cardiac Pacemakers, Inc. Systems, devices, and methods for setting cardiac pacing pulse parameters for a cardiac pacing device
US10639486B2 (en) 2016-11-21 2020-05-05 Cardiac Pacemakers, Inc. Implantable medical device with recharge coil
US10668294B2 (en) 2016-05-10 2020-06-02 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker configured for over the wire delivery
US10688304B2 (en) 2016-07-20 2020-06-23 Cardiac Pacemakers, Inc. Method and system for utilizing an atrial contraction timing fiducial in a leadless cardiac pacemaker system
US10722720B2 (en) 2014-01-10 2020-07-28 Cardiac Pacemakers, Inc. Methods and systems for improved communication between medical devices
US10737102B2 (en) 2017-01-26 2020-08-11 Cardiac Pacemakers, Inc. Leadless implantable device with detachable fixation
US10758724B2 (en) 2016-10-27 2020-09-01 Cardiac Pacemakers, Inc. Implantable medical device delivery system with integrated sensor
US10758737B2 (en) 2016-09-21 2020-09-01 Cardiac Pacemakers, Inc. Using sensor data from an intracardially implanted medical device to influence operation of an extracardially implantable cardioverter
US10765871B2 (en) 2016-10-27 2020-09-08 Cardiac Pacemakers, Inc. Implantable medical device with pressure sensor
US10780278B2 (en) 2016-08-24 2020-09-22 Cardiac Pacemakers, Inc. Integrated multi-device cardiac resynchronization therapy using P-wave to pace timing
US10821288B2 (en) 2017-04-03 2020-11-03 Cardiac Pacemakers, Inc. Cardiac pacemaker with pacing pulse energy adjustment based on sensed heart rate
US10835753B2 (en) 2017-01-26 2020-11-17 Cardiac Pacemakers, Inc. Intra-body device communication with redundant message transmission
US10870008B2 (en) 2016-08-24 2020-12-22 Cardiac Pacemakers, Inc. Cardiac resynchronization using fusion promotion for timing management
US10874861B2 (en) 2018-01-04 2020-12-29 Cardiac Pacemakers, Inc. Dual chamber pacing without beat-to-beat communication
US10881863B2 (en) 2016-11-21 2021-01-05 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker with multimode communication
US10881869B2 (en) 2016-11-21 2021-01-05 Cardiac Pacemakers, Inc. Wireless re-charge of an implantable medical device
US10894163B2 (en) 2016-11-21 2021-01-19 Cardiac Pacemakers, Inc. LCP based predictive timing for cardiac resynchronization
US10905889B2 (en) 2016-09-21 2021-02-02 Cardiac Pacemakers, Inc. Leadless stimulation device with a housing that houses internal components of the leadless stimulation device and functions as the battery case and a terminal of an internal battery
US10905872B2 (en) 2017-04-03 2021-02-02 Cardiac Pacemakers, Inc. Implantable medical device with a movable electrode biased toward an extended position
US10905886B2 (en) 2015-12-28 2021-02-02 Cardiac Pacemakers, Inc. Implantable medical device for deployment across the atrioventricular septum
US10918875B2 (en) 2017-08-18 2021-02-16 Cardiac Pacemakers, Inc. Implantable medical device with a flux concentrator and a receiving coil disposed about the flux concentrator
US10994145B2 (en) 2016-09-21 2021-05-04 Cardiac Pacemakers, Inc. Implantable cardiac monitor
US11052258B2 (en) 2017-12-01 2021-07-06 Cardiac Pacemakers, Inc. Methods and systems for detecting atrial contraction timing fiducials within a search window from a ventricularly implanted leadless cardiac pacemaker
US11065459B2 (en) 2017-08-18 2021-07-20 Cardiac Pacemakers, Inc. Implantable medical device with pressure sensor
US11071870B2 (en) 2017-12-01 2021-07-27 Cardiac Pacemakers, Inc. Methods and systems for detecting atrial contraction timing fiducials and determining a cardiac interval from a ventricularly implanted leadless cardiac pacemaker
US11116988B2 (en) 2016-03-31 2021-09-14 Cardiac Pacemakers, Inc. Implantable medical device with rechargeable battery
US11147979B2 (en) 2016-11-21 2021-10-19 Cardiac Pacemakers, Inc. Implantable medical device with a magnetically permeable housing and an inductive coil disposed about the housing
US11185703B2 (en) 2017-11-07 2021-11-30 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker for bundle of his pacing
US11207532B2 (en) 2017-01-04 2021-12-28 Cardiac Pacemakers, Inc. Dynamic sensing updates using postural input in a multiple device cardiac rhythm management system
US11207527B2 (en) 2016-07-06 2021-12-28 Cardiac Pacemakers, Inc. Method and system for determining an atrial contraction timing fiducial in a leadless cardiac pacemaker system
US11235163B2 (en) 2017-09-20 2022-02-01 Cardiac Pacemakers, Inc. Implantable medical device with multiple modes of operation
US11260216B2 (en) 2017-12-01 2022-03-01 Cardiac Pacemakers, Inc. Methods and systems for detecting atrial contraction timing fiducials during ventricular filling from a ventricularly implanted leadless cardiac pacemaker
US11285326B2 (en) 2015-03-04 2022-03-29 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
US11529523B2 (en) 2018-01-04 2022-12-20 Cardiac Pacemakers, Inc. Handheld bridge device for providing a communication bridge between an implanted medical device and a smartphone
US11813463B2 (en) 2017-12-01 2023-11-14 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker with reversionary behavior

Families Citing this family (281)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1997029802A2 (en) 1996-02-20 1997-08-21 Advanced Bionics Corporation Improved implantable microstimulator and systems employing the same
US7460911B2 (en) * 1997-02-26 2008-12-02 Alfred E. Mann Foundation For Scientific Research System and method suitable for treatment of a patient with a neurological deficit by sequentially stimulating neural pathways using a system of discrete implantable medical devices
US6164284A (en) * 1997-02-26 2000-12-26 Schulman; Joseph H. System of implantable devices for monitoring and/or affecting body parameters
US5991664A (en) * 1997-03-09 1999-11-23 Cochlear Limited Compact inductive arrangement for medical implant data and power transfer
AU1093099A (en) * 1997-10-17 1999-05-10 Penn State Research Foundation; The Muscle stimulating device and method for diagnosing and treating a breathin g disorder
US6122550A (en) * 1998-02-06 2000-09-19 Kozhemiakin; Alexander Device for therapeutic action on human organism
US6141588A (en) * 1998-07-24 2000-10-31 Intermedics Inc. Cardiac simulation system having multiple stimulators for anti-arrhythmia therapy
US6402689B1 (en) 1998-09-30 2002-06-11 Sicel Technologies, Inc. Methods, systems, and associated implantable devices for dynamic monitoring of physiological and biological properties of tumors
ATE408369T1 (en) * 1998-09-30 2008-10-15 Sicel Technologies Inc METHODS, SYSTEMS AND ASSOCIATED IMPLANTABLE DEVICES FOR DYNAMIC MONITORING OF TUMORS
US6358202B1 (en) 1999-01-25 2002-03-19 Sun Microsystems, Inc. Network for implanted computer devices
US6317615B1 (en) * 1999-04-19 2001-11-13 Cardiac Pacemakers, Inc. Method and system for reducing arterial restenosis in the presence of an intravascular stent
DE19930245A1 (en) * 1999-06-25 2000-12-28 Biotronik Mess & Therapieg Electromedical implant
DE19930256A1 (en) 1999-06-25 2000-12-28 Biotronik Mess & Therapieg Near and far field telemetry implant
DE19930262A1 (en) 1999-06-25 2000-12-28 Biotronik Mess & Therapieg Electromedical implant, especially pacemaker, has telemetry device transmitter containing oscillator with first transistor and resonator, buffer stage, antenna driver with second transistor
DE19930241A1 (en) 1999-06-25 2000-12-28 Biotronik Mess & Therapieg Procedure for data transmission in implant monitoring
DE19930250A1 (en) 1999-06-25 2001-02-15 Biotronik Mess & Therapieg Device for monitoring data, in particular from an electromedical implant
DE19930263A1 (en) 1999-06-25 2000-12-28 Biotronik Mess & Therapieg Method and device for data transmission between an electromedical implant and an external device
US8155752B2 (en) 2000-03-17 2012-04-10 Boston Scientific Neuromodulation Corporation Implantable medical device with single coil for charging and communicating
US6631296B1 (en) * 2000-03-17 2003-10-07 Advanced Bionics Corporation Voltage converter for implantable microstimulator using RF-powering coil
US6895281B1 (en) * 2000-03-31 2005-05-17 Cardiac Pacemakers, Inc. Inductive coil apparatus for bio-medical telemetry
US6654638B1 (en) * 2000-04-06 2003-11-25 Cardiac Pacemakers, Inc. Ultrasonically activated electrodes
US8527046B2 (en) 2000-04-20 2013-09-03 Medtronic, Inc. MRI-compatible implantable device
US6574511B2 (en) * 2000-04-21 2003-06-03 Medtronic, Inc. Passive data collection system from a fleet of medical instruments and implantable devices
US7499742B2 (en) 2001-09-26 2009-03-03 Cvrx, Inc. Electrode structures and methods for their use in cardiovascular reflex control
US7623926B2 (en) 2000-09-27 2009-11-24 Cvrx, Inc. Stimulus regimens for cardiovascular reflex control
US7616997B2 (en) 2000-09-27 2009-11-10 Kieval Robert S Devices and methods for cardiovascular reflex control via coupled electrodes
US7840271B2 (en) 2000-09-27 2010-11-23 Cvrx, Inc. Stimulus regimens for cardiovascular reflex control
US8086314B1 (en) 2000-09-27 2011-12-27 Cvrx, Inc. Devices and methods for cardiovascular reflex control
US6764446B2 (en) 2000-10-16 2004-07-20 Remon Medical Technologies Ltd Implantable pressure sensors and methods for making and using them
US7198603B2 (en) * 2003-04-14 2007-04-03 Remon Medical Technologies, Inc. Apparatus and methods using acoustic telemetry for intrabody communications
US7283874B2 (en) 2000-10-16 2007-10-16 Remon Medical Technologies Ltd. Acoustically powered implantable stimulating device
US7024248B2 (en) 2000-10-16 2006-04-04 Remon Medical Technologies Ltd Systems and methods for communicating with implantable devices
AU2002214696A1 (en) * 2000-10-25 2002-05-06 Ryan Byleveld Apparatus for dispensing electrotherapy treatment programs
US7519421B2 (en) * 2001-01-16 2009-04-14 Kenergy, Inc. Vagal nerve stimulation using vascular implanted devices for treatment of atrial fibrillation
US6829509B1 (en) 2001-02-20 2004-12-07 Biophan Technologies, Inc. Electromagnetic interference immune tissue invasive system
US20020116029A1 (en) 2001-02-20 2002-08-22 Victor Miller MRI-compatible pacemaker with power carrying photonic catheter and isolated pulse generating electronics providing VOO functionality
US7209783B2 (en) * 2001-06-15 2007-04-24 Cardiac Pacemakers, Inc. Ablation stent for treating atrial fibrillation
US7493162B2 (en) * 2001-06-15 2009-02-17 Cardiac Pacemakers, Inc. Pulmonary vein stent for treating atrial fibrillation
US6731979B2 (en) 2001-08-30 2004-05-04 Biophan Technologies Inc. Pulse width cardiac pacing apparatus
US7340303B2 (en) 2001-09-25 2008-03-04 Cardiac Pacemakers, Inc. Evoked response sensing for ischemia detection
WO2003033070A1 (en) * 2001-10-16 2003-04-24 Case Western Reserve University Neural prosthesis
US20030105409A1 (en) 2001-11-14 2003-06-05 Donoghue John Philip Neurological signal decoding
US7557353B2 (en) 2001-11-30 2009-07-07 Sicel Technologies, Inc. Single-use external dosimeters for use in radiation therapies
AUPS006902A0 (en) * 2002-01-21 2002-02-07 Neopraxis Pty Ltd A multi-purpose fes system
US7231252B2 (en) * 2002-01-21 2007-06-12 Neopraxis Pty Ltd. FES stimulator having multiple bundled leads
US20090088813A1 (en) * 2004-03-12 2009-04-02 Brockway Brian P Cardiac Rhythm Management Device
US8321036B2 (en) * 2002-02-15 2012-11-27 Data Sciences International, Inc. Cardiac rhythm management device
US7236821B2 (en) 2002-02-19 2007-06-26 Cardiac Pacemakers, Inc. Chronically-implanted device for sensing and therapy
US8301248B1 (en) 2002-03-06 2012-10-30 Boston Scientific Neuromodulation Corporation Sequenced and simultaneous stimulation for treating congestive heart failure
AUPS101502A0 (en) * 2002-03-11 2002-04-11 Neopraxis Pty Ltd Wireless fes system
AU2003220599A1 (en) * 2002-03-27 2003-10-13 Cvrx, Inc. Devices and methods for cardiovascular reflex control via coupled electrodes
US6711440B2 (en) 2002-04-11 2004-03-23 Biophan Technologies, Inc. MRI-compatible medical device with passive generation of optical sensing signals
US6725092B2 (en) 2002-04-25 2004-04-20 Biophan Technologies, Inc. Electromagnetic radiation immune medical assist device adapter
WO2003101532A2 (en) * 2002-06-04 2003-12-11 Cyberkinetics, Inc. Optically-connected implants and related systems and methods of use
US7089055B2 (en) 2002-06-28 2006-08-08 Cardiac Pacemakers, Inc. Method and apparatus for delivering pre-shock defibrillation therapy
US7212851B2 (en) * 2002-10-24 2007-05-01 Brown University Research Foundation Microstructured arrays for cortex interaction and related methods of manufacture and use
US7072711B2 (en) 2002-11-12 2006-07-04 Cardiac Pacemakers, Inc. Implantable device for delivering cardiac drug therapy
US8712549B2 (en) 2002-12-11 2014-04-29 Proteus Digital Health, Inc. Method and system for monitoring and treating hemodynamic parameters
US7065409B2 (en) * 2002-12-13 2006-06-20 Cardiac Pacemakers, Inc. Device communications of an implantable medical device and an external system
US7009511B2 (en) 2002-12-17 2006-03-07 Cardiac Pacemakers, Inc. Repeater device for communications with an implantable medical device
US7127300B2 (en) * 2002-12-23 2006-10-24 Cardiac Pacemakers, Inc. Method and apparatus for enabling data communication between an implantable medical device and a patient management system
US7395117B2 (en) * 2002-12-23 2008-07-01 Cardiac Pacemakers, Inc. Implantable medical device having long-term wireless capabilities
US6978182B2 (en) * 2002-12-27 2005-12-20 Cardiac Pacemakers, Inc. Advanced patient management system including interrogator/transceiver unit
US20040128161A1 (en) * 2002-12-27 2004-07-01 Mazar Scott T. System and method for ad hoc communications with an implantable medical device
EP1585441A4 (en) * 2003-01-24 2008-05-21 Proteus Biomedical Inc Methods and systems for measuring cardiac parameters
US7200439B2 (en) 2003-01-24 2007-04-03 Proteus Biomedical, Inc. Method and apparatus for enhancing cardiac pacing
US7267649B2 (en) * 2003-01-24 2007-09-11 Proteus Biomedical, Inc. Method and system for remote hemodynamic monitoring
US7082336B2 (en) 2003-06-04 2006-07-25 Synecor, Llc Implantable intravascular device for defibrillation and/or pacing
US7617007B2 (en) 2003-06-04 2009-11-10 Synecor Llc Method and apparatus for retaining medical implants within body vessels
WO2005000398A2 (en) 2003-06-04 2005-01-06 Synecor Intravascular electrophysiological system and methods
US8239045B2 (en) 2003-06-04 2012-08-07 Synecor Llc Device and method for retaining a medical device within a vessel
US7320675B2 (en) 2003-08-21 2008-01-22 Cardiac Pacemakers, Inc. Method and apparatus for modulating cellular metabolism during post-ischemia or heart failure
US6917833B2 (en) * 2003-09-16 2005-07-12 Kenergy, Inc. Omnidirectional antenna for wireless communication with implanted medical devices
US8489196B2 (en) * 2003-10-03 2013-07-16 Medtronic, Inc. System, apparatus and method for interacting with a targeted tissue of a patient
US7003350B2 (en) * 2003-11-03 2006-02-21 Kenergy, Inc. Intravenous cardiac pacing system with wireless power supply
US20050125041A1 (en) 2003-11-05 2005-06-09 Xiaoyi Min Methods for ventricular pacing
US20050143589A1 (en) * 2003-11-09 2005-06-30 Donoghue John P. Calibration systems and methods for neural interface devices
US20050113744A1 (en) * 2003-11-21 2005-05-26 Cyberkinetics, Inc. Agent delivery systems and related methods under control of biological electrical signals
US7751877B2 (en) * 2003-11-25 2010-07-06 Braingate Co., Llc Neural interface system with embedded id
EP1701766A2 (en) 2003-12-12 2006-09-20 Synecor, LLC Implantable medical device having pre-implant exoskeleton
US7957798B2 (en) * 2003-12-17 2011-06-07 Physio-Control, Inc. Defibrillator/monitor system having a pod with leads capable of wirelessly communicating
US10413742B2 (en) 2008-03-05 2019-09-17 Physio-Control, Inc. Defibrillator patient monitoring pod
US7647097B2 (en) * 2003-12-29 2010-01-12 Braingate Co., Llc Transcutaneous implant
US20050203366A1 (en) * 2004-03-12 2005-09-15 Donoghue John P. Neurological event monitoring and therapy systems and related methods
GB2412069A (en) * 2004-03-18 2005-09-21 Invivo Technology Ltd Cardiac stimulation system having wireless communication to a stimulator directly attached to the external heart surface.
US7212110B1 (en) * 2004-04-19 2007-05-01 Advanced Neuromodulation Systems, Inc. Implantable device and system and method for wireless communication
EP1753506A4 (en) * 2004-05-04 2008-06-11 Univ Rochester Leadless implantable cardioverter defibrillator
US7794499B2 (en) 2004-06-08 2010-09-14 Theken Disc, L.L.C. Prosthetic intervertebral spinal disc with integral microprocessor
US7765001B2 (en) 2005-08-31 2010-07-27 Ebr Systems, Inc. Methods and systems for heart failure prevention and treatments using ultrasound and leadless implantable devices
US7630767B1 (en) 2004-07-14 2009-12-08 Pacesetter, Inc. System and method for communicating information using encoded pacing pulses within an implantable medical system
US7743151B2 (en) * 2004-08-05 2010-06-22 Cardiac Pacemakers, Inc. System and method for providing digital data communications over a wireless intra-body network
US20060058627A1 (en) * 2004-08-13 2006-03-16 Flaherty J C Biological interface systems with wireless connection and related methods
US7567841B2 (en) 2004-08-20 2009-07-28 Cardiac Pacemakers, Inc. Method and apparatus for delivering combined electrical and drug therapies
WO2006029090A2 (en) * 2004-09-02 2006-03-16 Proteus Biomedical, Inc. Methods and apparatus for tissue activation and monitoring
US8560041B2 (en) * 2004-10-04 2013-10-15 Braingate Co., Llc Biological interface system
US7200437B1 (en) 2004-10-13 2007-04-03 Pacesetter, Inc. Tissue contact for satellite cardiac pacemaker
US7647109B2 (en) 2004-10-20 2010-01-12 Boston Scientific Scimed, Inc. Leadless cardiac stimulation systems
US8150509B2 (en) 2004-10-21 2012-04-03 Cardiac Pacemakers, Inc. Systems and methods for drug therapy enhancement using expected pharmacodynamic models
US8374693B2 (en) * 2004-12-03 2013-02-12 Cardiac Pacemakers, Inc. Systems and methods for timing-based communication between implantable medical devices
US8818504B2 (en) 2004-12-16 2014-08-26 Cardiac Pacemakers Inc Leadless cardiac stimulation device employing distributed logic
US7558631B2 (en) 2004-12-21 2009-07-07 Ebr Systems, Inc. Leadless tissue stimulation systems and methods
EP1835964B1 (en) * 2004-12-21 2016-03-09 EBR Systems, Inc. Leadless cardiac system for pacing and arrhythmia treatment
US7606621B2 (en) * 2004-12-21 2009-10-20 Ebr Systems, Inc. Implantable transducer devices
US20060137699A1 (en) * 2004-12-23 2006-06-29 Moore Mark P Providing data destination information to a medical device
US7901368B2 (en) 2005-01-06 2011-03-08 Braingate Co., Llc Neurally controlled patient ambulation system
US8095209B2 (en) * 2005-01-06 2012-01-10 Braingate Co., Llc Biological interface system with gated control signal
US7295874B2 (en) * 2005-01-06 2007-11-13 Cardiac Pacemakers, Inc. Intermittent stress augmentation pacing for cardioprotective effect
US7991461B2 (en) * 2005-01-06 2011-08-02 Braingate Co., Llc Patient training routine for biological interface system
US20060167564A1 (en) * 2005-01-10 2006-07-27 Flaherty J C Limb and digit movement system
WO2006076175A2 (en) * 2005-01-10 2006-07-20 Cyberkinetics Neurotechnology Systems, Inc. Biological interface system with patient training apparatus
US7881780B2 (en) * 2005-01-18 2011-02-01 Braingate Co., Llc Biological interface system with thresholded configuration
US7310556B2 (en) * 2005-03-24 2007-12-18 Kenergy, Inc. Implantable medical stimulation apparatus with intra-conductor capacitive energy storage
US8036743B2 (en) 2005-03-31 2011-10-11 Proteus Biomedical, Inc. Automated optimization of multi-electrode pacing for cardiac resynchronization
US7499748B2 (en) 2005-04-11 2009-03-03 Cardiac Pacemakers, Inc. Transvascular neural stimulation device
US7634313B1 (en) * 2005-04-11 2009-12-15 Pacesetter, Inc. Failsafe satellite pacemaker system
US7565195B1 (en) 2005-04-11 2009-07-21 Pacesetter, Inc. Failsafe satellite pacemaker system
US7991467B2 (en) * 2005-04-26 2011-08-02 Medtronic, Inc. Remotely enabled pacemaker and implantable subcutaneous cardioverter/defibrillator system
US7617003B2 (en) * 2005-05-16 2009-11-10 Cardiac Pacemakers, Inc. System for selective activation of a nerve trunk using a transvascular reshaping lead
US7295879B2 (en) * 2005-06-24 2007-11-13 Kenergy, Inc. Double helical antenna assembly for a wireless intravascular medical device
US7752059B2 (en) 2005-07-05 2010-07-06 Cardiac Pacemakers, Inc. Optimization of timing for data collection and analysis in advanced patient management system
WO2007013065A2 (en) 2005-07-25 2007-02-01 Rainbow Medical Ltd. Electrical stimulation of blood vessels
WO2007021804A2 (en) 2005-08-12 2007-02-22 Proteus Biomedical, Inc. Evaluation of depolarization wave conduction velocity
US7702392B2 (en) 2005-09-12 2010-04-20 Ebr Systems, Inc. Methods and apparatus for determining cardiac stimulation sites using hemodynamic data
US7749265B2 (en) * 2005-10-05 2010-07-06 Kenergy, Inc. Radio frequency antenna for a wireless intravascular medical device
US9358400B2 (en) * 2005-10-14 2016-06-07 Pacesetter, Inc. Leadless cardiac pacemaker
US9168383B2 (en) 2005-10-14 2015-10-27 Pacesetter, Inc. Leadless cardiac pacemaker with conducted communication
US7729773B2 (en) * 2005-10-19 2010-06-01 Advanced Neuromodualation Systems, Inc. Neural stimulation and optical monitoring systems and methods
US7616990B2 (en) 2005-10-24 2009-11-10 Cardiac Pacemakers, Inc. Implantable and rechargeable neural stimulator
US20070106143A1 (en) * 2005-11-08 2007-05-10 Flaherty J C Electrode arrays and related methods
US8050774B2 (en) 2005-12-22 2011-11-01 Boston Scientific Scimed, Inc. Electrode apparatus, systems and methods
US20100023021A1 (en) * 2005-12-27 2010-01-28 Flaherty J Christopher Biological Interface and Insertion
US20070156126A1 (en) * 2005-12-29 2007-07-05 Flaherty J C Medical device insertion system and related methods
US8078278B2 (en) 2006-01-10 2011-12-13 Remon Medical Technologies Ltd. Body attachable unit in wireless communication with implantable devices
US7616992B2 (en) * 2006-01-30 2009-11-10 Medtronic, Inc. Intravascular medical device
US7519424B2 (en) * 2006-01-30 2009-04-14 Medtronic, Inc. Intravascular medical device
US7627376B2 (en) * 2006-01-30 2009-12-01 Medtronic, Inc. Intravascular medical device
WO2007109076A1 (en) * 2006-03-15 2007-09-27 Cherik Bulkes Composite waveform based method and apparatus for animal tissue stimulation
US7937161B2 (en) 2006-03-31 2011-05-03 Boston Scientific Scimed, Inc. Cardiac stimulation electrodes, delivery devices, and implantation configurations
US7650185B2 (en) * 2006-04-25 2010-01-19 Cardiac Pacemakers, Inc. System and method for walking an implantable medical device from a sleep state
US8406901B2 (en) 2006-04-27 2013-03-26 Medtronic, Inc. Sutureless implantable medical device fixation
US20070288077A1 (en) * 2006-06-07 2007-12-13 Cherik Bulkes Self-anchoring electrical lead with multiple electrodes
WO2007146076A2 (en) * 2006-06-07 2007-12-21 Cherik Bulkes Biological tissue stimulator with flexible electrode carrier
US20070288183A1 (en) * 2006-06-07 2007-12-13 Cherik Bulkes Analog signal transition detector
US8078283B2 (en) 2006-06-20 2011-12-13 Ebr Systems, Inc. Systems and methods for implantable leadless bone stimulation
US8290600B2 (en) * 2006-07-21 2012-10-16 Boston Scientific Scimed, Inc. Electrical stimulation of body tissue using interconnected electrode assemblies
US7908334B2 (en) * 2006-07-21 2011-03-15 Cardiac Pacemakers, Inc. System and method for addressing implantable devices
US20080039904A1 (en) * 2006-08-08 2008-02-14 Cherik Bulkes Intravascular implant system
US20080077184A1 (en) * 2006-09-27 2008-03-27 Stephen Denker Intravascular Stimulation System With Wireless Power Supply
US9492657B2 (en) * 2006-11-30 2016-11-15 Medtronic, Inc. Method of implanting a medical device including a fixation element
US7778706B1 (en) 2006-12-13 2010-08-17 Pacesetter, Inc. Rate adaptive biventricular and cardiac resynchronization therapy
US7702390B1 (en) 2006-12-13 2010-04-20 Pacesetter, Inc. Rate adaptive biventricular and cardiac resynchronization therapy
US20080171941A1 (en) * 2007-01-12 2008-07-17 Huelskamp Paul J Low power methods for pressure waveform signal sampling using implantable medical devices
US7792588B2 (en) * 2007-01-26 2010-09-07 Medtronic, Inc. Radio frequency transponder based implantable medical system
CN101396582B (en) * 2007-02-16 2012-05-30 圣美申医疗科技(上海)有限公司 No-electrode ultrathin minitype multifunctional heart rhythm regulation and control device
EP2139556B1 (en) 2007-03-26 2014-04-23 Remon Medical Technologies Ltd. Biased acoustic switch for implantable medical device
WO2008137452A1 (en) * 2007-05-04 2008-11-13 Kenergy Royalty Company, Llc Implantable high efficiency digital stimulation device
US8718773B2 (en) 2007-05-23 2014-05-06 Ebr Systems, Inc. Optimizing energy transmission in a leadless tissue stimulation system
US8019419B1 (en) * 2007-09-25 2011-09-13 Dorin Panescu Methods and apparatus for leadless, battery-less, wireless stimulation of tissue
US7953493B2 (en) 2007-12-27 2011-05-31 Ebr Systems, Inc. Optimizing size of implantable medical devices by isolating the power source
US8041431B2 (en) * 2008-01-07 2011-10-18 Cardiac Pacemakers, Inc. System and method for in situ trimming of oscillators in a pair of implantable medical devices
US8915866B2 (en) * 2008-01-18 2014-12-23 Warsaw Orthopedic, Inc. Implantable sensor and associated methods
US8538535B2 (en) 2010-08-05 2013-09-17 Rainbow Medical Ltd. Enhancing perfusion by contraction
US8301262B2 (en) * 2008-02-06 2012-10-30 Cardiac Pacemakers, Inc. Direct inductive/acoustic converter for implantable medical device
EP2092958B1 (en) * 2008-02-22 2017-05-24 Cochlear Limited Interleaving power and data in a transcutaneous communications link
US8473069B2 (en) 2008-02-28 2013-06-25 Proteus Digital Health, Inc. Integrated circuit implementation and fault control system, device, and method
US7941217B1 (en) 2008-03-25 2011-05-10 Pacesetter, Inc. Techniques for promoting biventricular synchrony and stimulation device efficiency using intentional fusion
EP2265166B1 (en) 2008-03-25 2020-08-05 EBR Systems, Inc. Temporary electrode connection for wireless pacing systems
DE102008016364A1 (en) * 2008-03-29 2009-10-01 Biotronik Crm Patent Ag Signal line of an implantable electromedical device
DE102008020123A1 (en) * 2008-04-22 2009-10-29 Biotronik Crm Patent Ag Ventricular cardiac stimulator
US20090275998A1 (en) 2008-04-30 2009-11-05 Medtronic, Inc. Extra-cardiac implantable device with fusion pacing capability
US20090299423A1 (en) * 2008-06-03 2009-12-03 Pacesetter, Inc. Systems and methods for determining inter-atrial conduction delays using multi-pole left ventricular pacing/sensing leads
US8798761B2 (en) 2008-06-27 2014-08-05 Cardiac Pacemakers, Inc. Systems and methods of monitoring the acoustic coupling of medical devices
US20100016911A1 (en) 2008-07-16 2010-01-21 Ebr Systems, Inc. Local Lead To Improve Energy Efficiency In Implantable Wireless Acoustic Stimulators
EP2337609B1 (en) 2008-08-14 2016-08-17 Cardiac Pacemakers, Inc. Performance assessment and adaptation of an acoustic communication link
US8593107B2 (en) 2008-10-27 2013-11-26 Cardiac Pacemakers, Inc. Methods and systems for recharging an implanted device by delivering a section of a charging device adjacent the implanted device within a body
US8442634B2 (en) * 2008-12-04 2013-05-14 Pacesetter, Inc. Systems and methods for controlling ventricular pacing in patients with long inter-atrial conduction delays
US8527068B2 (en) 2009-02-02 2013-09-03 Nanostim, Inc. Leadless cardiac pacemaker with secondary fixation capability
US9233254B2 (en) * 2009-02-17 2016-01-12 Boston Scientific Neuromodulation Corporation Selectable boost converter and charge pump for compliance voltage generation in an implantable stimulator device
EP2424588A4 (en) * 2009-04-29 2013-05-22 Proteus Digital Health Inc Methods and apparatus for leads for implantable devices
US8786049B2 (en) 2009-07-23 2014-07-22 Proteus Digital Health, Inc. Solid-state thin-film capacitor
US9186519B2 (en) * 2010-01-28 2015-11-17 Medtronic, Inc. Wireless communication with an implantable medical device
US9042995B2 (en) * 2010-02-03 2015-05-26 Medtronic, Inc. Implantable medical devices and systems having power management for recharge sessions
WO2011097289A1 (en) 2010-02-03 2011-08-11 Medtronic, Inc. Implantable medical devices and systems having dual frequency inductive telemetry and recharge
US8788045B2 (en) 2010-06-08 2014-07-22 Bluewind Medical Ltd. Tibial nerve stimulation
US9254091B2 (en) 2010-07-28 2016-02-09 Medtronic, Inc. Measurement of cardiac cycle length and pressure metrics from pulmonary arterial pressure
EP2627403A4 (en) 2010-10-12 2014-03-26 Nanostim Inc Temperature sensor for a leadless cardiac pacemaker
US9060692B2 (en) 2010-10-12 2015-06-23 Pacesetter, Inc. Temperature sensor for a leadless cardiac pacemaker
JP2013540022A (en) 2010-10-13 2013-10-31 ナノスティム・インコーポレイテッド Leadless cardiac pacemaker with screw anti-rotation element
US8718770B2 (en) 2010-10-21 2014-05-06 Medtronic, Inc. Capture threshold measurement for selection of pacing vector
US9457186B2 (en) 2010-11-15 2016-10-04 Bluewind Medical Ltd. Bilateral feedback
US9186504B2 (en) 2010-11-15 2015-11-17 Rainbow Medical Ltd Sleep apnea treatment
JP2014501136A (en) 2010-12-13 2014-01-20 ナノスティム・インコーポレイテッド Delivery catheter system and method
WO2012082755A1 (en) 2010-12-13 2012-06-21 Nanostim, Inc. Pacemaker retrieval systems and methods
EP2654889B1 (en) 2010-12-20 2017-03-01 Pacesetter, Inc. Leadless pacemaker with radial fixation mechanism
TWI492738B (en) * 2010-12-24 2015-07-21 Nat Univ Chung Cheng Implantable closed loop micro stimuli
US9775982B2 (en) 2010-12-29 2017-10-03 Medtronic, Inc. Implantable medical device fixation
US10112045B2 (en) 2010-12-29 2018-10-30 Medtronic, Inc. Implantable medical device fixation
US8386051B2 (en) * 2010-12-30 2013-02-26 Medtronic, Inc. Disabling an implantable medical device
US9314205B2 (en) 2011-04-28 2016-04-19 Medtronic, Inc. Measurement of cardiac cycle length and pressure metrics from pulmonary arterial pressure
US9136728B2 (en) 2011-04-28 2015-09-15 Medtronic, Inc. Implantable medical devices and systems having inductive telemetry and recharge on a single coil
US8827913B2 (en) 2011-05-03 2014-09-09 Medtronic, Inc. Verification of pressure metrics
US8355784B2 (en) 2011-05-13 2013-01-15 Medtronic, Inc. Dynamic representation of multipolar leads in a programmer interface
US20130027186A1 (en) * 2011-07-26 2013-01-31 Can Cinbis Ultralow-power implantable hub-based wireless implantable sensor communication
US9526637B2 (en) 2011-09-09 2016-12-27 Enopace Biomedical Ltd. Wireless endovascular stent-based electrodes
US9775991B1 (en) 2011-10-11 2017-10-03 A-Hamid Hakki Endovascular electrode system for tissue stimulation with embedded generator
US10500394B1 (en) 2011-10-11 2019-12-10 A-Hamid Hakki Pacemaker system equipped with a flexible intercostal generator
US8781605B2 (en) 2011-10-31 2014-07-15 Pacesetter, Inc. Unitary dual-chamber leadless intra-cardiac medical device and method of implanting same
US9017341B2 (en) 2011-10-31 2015-04-28 Pacesetter, Inc. Multi-piece dual-chamber leadless intra-cardiac medical device and method of implanting same
US8634912B2 (en) 2011-11-04 2014-01-21 Pacesetter, Inc. Dual-chamber leadless intra-cardiac medical device with intra-cardiac extension
US8700181B2 (en) 2011-11-03 2014-04-15 Pacesetter, Inc. Single-chamber leadless intra-cardiac medical device with dual-chamber functionality and shaped stabilization intra-cardiac extension
US8996109B2 (en) 2012-01-17 2015-03-31 Pacesetter, Inc. Leadless intra-cardiac medical device with dual chamber sensing through electrical and/or mechanical sensing
WO2013067496A2 (en) 2011-11-04 2013-05-10 Nanostim, Inc. Leadless cardiac pacemaker with integral battery and redundant welds
US9265436B2 (en) 2011-11-04 2016-02-23 Pacesetter, Inc. Leadless intra-cardiac medical device with built-in telemetry system
US20150018728A1 (en) 2012-01-26 2015-01-15 Bluewind Medical Ltd. Wireless neurostimulators
US9854982B2 (en) 2012-03-26 2018-01-02 Medtronic, Inc. Implantable medical device deployment within a vessel
US9339197B2 (en) 2012-03-26 2016-05-17 Medtronic, Inc. Intravascular implantable medical device introduction
US9220906B2 (en) 2012-03-26 2015-12-29 Medtronic, Inc. Tethered implantable medical device deployment
US9833625B2 (en) 2012-03-26 2017-12-05 Medtronic, Inc. Implantable medical device delivery with inner and outer sheaths
US9717421B2 (en) 2012-03-26 2017-08-01 Medtronic, Inc. Implantable medical device delivery catheter with tether
US10485435B2 (en) 2012-03-26 2019-11-26 Medtronic, Inc. Pass-through implantable medical device delivery catheter with removeable distal tip
GB2501077B (en) 2012-04-10 2016-06-15 Gloucestershire Hospitals Nhs Found Trust Apparatus for artificial cardiac stimulation and method of using the same
US9457197B2 (en) 2012-05-08 2016-10-04 Physio-Control, Inc. Utility module system
US10303852B2 (en) 2012-07-02 2019-05-28 Physio-Control, Inc. Decision support tool for use with a medical monitor-defibrillator
EP2879758B1 (en) 2012-08-01 2018-04-18 Pacesetter, Inc. Biostimulator circuit with flying cell
US9351648B2 (en) 2012-08-24 2016-05-31 Medtronic, Inc. Implantable medical device electrode assembly
AU2013337780B2 (en) * 2012-10-31 2018-04-05 The Board Of Trustees Of The Leland Stanford Junior University Wireless implantable sensing devices
WO2014087337A1 (en) 2012-12-06 2014-06-12 Bluewind Medical Ltd. Delivery of implantable neurostimulators
US8670842B1 (en) 2012-12-14 2014-03-11 Pacesetter, Inc. Intra-cardiac implantable medical device
GB2519302B (en) 2013-10-15 2016-04-20 Gloucestershire Hospitals Nhs Foundation Trust Apparatus for artificial cardiac stimulation and method of using the same
EP3065673A4 (en) 2013-11-06 2017-07-12 Enopace Biomedical Ltd. Wireless endovascular stent-based electrodes
US9789319B2 (en) 2013-11-21 2017-10-17 Medtronic, Inc. Systems and methods for leadless cardiac resynchronization therapy
CN106163610B (en) * 2014-01-10 2019-11-15 心脏起搏器股份公司 The movable communication of the therapy of first implantable medical device to another implantable medical device
US10004913B2 (en) 2014-03-03 2018-06-26 The Board Of Trustees Of The Leland Stanford Junior University Methods and apparatus for power conversion and data transmission in implantable sensors, stimulators, and actuators
US9486623B2 (en) 2014-03-05 2016-11-08 Rainbow Medical Ltd. Electrical stimulation of a pancreas
US9669224B2 (en) 2014-05-06 2017-06-06 Medtronic, Inc. Triggered pacing system
US9492671B2 (en) 2014-05-06 2016-11-15 Medtronic, Inc. Acoustically triggered therapy delivery
US10434329B2 (en) 2014-05-09 2019-10-08 The Board Of Trustees Of The Leland Stanford Junior University Autofocus wireless power transfer to implantable devices in freely moving animals
US10390720B2 (en) 2014-07-17 2019-08-27 Medtronic, Inc. Leadless pacing system including sensing extension
US9399140B2 (en) 2014-07-25 2016-07-26 Medtronic, Inc. Atrial contraction detection by a ventricular leadless pacing device for atrio-synchronous ventricular pacing
US9694189B2 (en) 2014-08-06 2017-07-04 Cardiac Pacemakers, Inc. Method and apparatus for communicating between medical devices
US9757570B2 (en) 2014-08-06 2017-09-12 Cardiac Pacemakers, Inc. Communications in a medical device system
US9808631B2 (en) 2014-08-06 2017-11-07 Cardiac Pacemakers, Inc. Communication between a plurality of medical devices using time delays between communication pulses to distinguish between symbols
US9492668B2 (en) 2014-11-11 2016-11-15 Medtronic, Inc. Mode switching by a ventricular leadless pacing device
US9623234B2 (en) 2014-11-11 2017-04-18 Medtronic, Inc. Leadless pacing device implantation
US9492669B2 (en) 2014-11-11 2016-11-15 Medtronic, Inc. Mode switching by a ventricular leadless pacing device
US9724519B2 (en) 2014-11-11 2017-08-08 Medtronic, Inc. Ventricular leadless pacing device mode switching
US20170311836A1 (en) * 2014-11-20 2017-11-02 Brigham And Women's Hospital, Inc. System and Method for Wave Interference Analysis and Titration
US9289612B1 (en) 2014-12-11 2016-03-22 Medtronic Inc. Coordination of ventricular pacing in a leadless pacing system
US9597521B2 (en) 2015-01-21 2017-03-21 Bluewind Medical Ltd. Transmitting coils for neurostimulation
US9764146B2 (en) 2015-01-21 2017-09-19 Bluewind Medical Ltd. Extracorporeal implant controllers
US10004896B2 (en) 2015-01-21 2018-06-26 Bluewind Medical Ltd. Anchors and implant devices
US9750943B2 (en) 2015-02-26 2017-09-05 Medtronic, Inc. Monitoring of pacing capture using acceleration
US9782589B2 (en) 2015-06-10 2017-10-10 Bluewind Medical Ltd. Implantable electrostimulator for improving blood flow
US10004906B2 (en) 2015-07-16 2018-06-26 Medtronic, Inc. Confirming sensed atrial events for pacing during resynchronization therapy in a cardiac medical device and medical device system
US10105540B2 (en) 2015-11-09 2018-10-23 Bluewind Medical Ltd. Optimization of application of current
US9713707B2 (en) 2015-11-12 2017-07-25 Bluewind Medical Ltd. Inhibition of implant migration
US11166628B2 (en) 2016-02-02 2021-11-09 Physio-Control, Inc. Laryngoscope with handle-grip activated recording
US9731138B1 (en) 2016-02-17 2017-08-15 Medtronic, Inc. System and method for cardiac pacing
US9802055B2 (en) 2016-04-04 2017-10-31 Medtronic, Inc. Ultrasound powered pulse delivery device
EP3484577A4 (en) 2016-07-18 2020-03-25 Nalu Medical, Inc. Methods and systems for treating pelvic disorders and pain conditions
WO2018085665A1 (en) * 2016-11-04 2018-05-11 Galvani Bioelectronics Limited System for wirelessly coupling in vivo
US10124178B2 (en) 2016-11-23 2018-11-13 Bluewind Medical Ltd. Implant and delivery tool therefor
US20180353764A1 (en) 2017-06-13 2018-12-13 Bluewind Medical Ltd. Antenna configuration
US10694967B2 (en) 2017-10-18 2020-06-30 Medtronic, Inc. State-based atrial event detection
JP2021518192A (en) 2018-03-23 2021-08-02 メドトロニック,インコーポレイテッド VfA cardiac resynchronization therapy
EP3768160B1 (en) 2018-03-23 2023-06-07 Medtronic, Inc. Vfa cardiac therapy for tachycardia
US11400296B2 (en) 2018-03-23 2022-08-02 Medtronic, Inc. AV synchronous VfA cardiac therapy
US10596383B2 (en) 2018-04-03 2020-03-24 Medtronic, Inc. Feature based sensing for leadless pacing therapy
WO2020065582A1 (en) 2018-09-26 2020-04-02 Medtronic, Inc. Capture in ventricle-from-atrium cardiac therapy
US10874850B2 (en) 2018-09-28 2020-12-29 Medtronic, Inc. Impedance-based verification for delivery of implantable medical devices
US11679265B2 (en) 2019-02-14 2023-06-20 Medtronic, Inc. Lead-in-lead systems and methods for cardiac therapy
US11697025B2 (en) 2019-03-29 2023-07-11 Medtronic, Inc. Cardiac conduction system capture
US11213676B2 (en) 2019-04-01 2022-01-04 Medtronic, Inc. Delivery systems for VfA cardiac therapy
US11712188B2 (en) 2019-05-07 2023-08-01 Medtronic, Inc. Posterior left bundle branch engagement
US11331475B2 (en) 2019-05-07 2022-05-17 Medtronic, Inc. Tether assemblies for medical device delivery systems
US11305127B2 (en) 2019-08-26 2022-04-19 Medtronic Inc. VfA delivery and implant region detection
US11813466B2 (en) 2020-01-27 2023-11-14 Medtronic, Inc. Atrioventricular nodal stimulation
US11304659B2 (en) 2020-03-20 2022-04-19 Xenter, Inc. Operatively coupled data and power transfer device for medical guidewires and catheters with sensors
US11911168B2 (en) 2020-04-03 2024-02-27 Medtronic, Inc. Cardiac conduction system therapy benefit determination
US11813464B2 (en) 2020-07-31 2023-11-14 Medtronic, Inc. Cardiac conduction system evaluation
US11400299B1 (en) 2021-09-14 2022-08-02 Rainbow Medical Ltd. Flexible antenna for stimulator

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0071131A2 (en) * 1981-07-30 1983-02-09 Jürgen J. Dipl.-Phys. Dr.-Ing. Hildebrandt Device for stimulating a human muscle
US4886064A (en) 1987-11-25 1989-12-12 Siemens Aktiengesellschaft Body activity controlled heart pacer
EP0362611A1 (en) * 1988-09-19 1990-04-11 Medtronic, Inc. Body bus medical device communication system
US5405367A (en) 1991-12-18 1995-04-11 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
US5411535A (en) 1992-03-03 1995-05-02 Terumo Kabushiki Kaisha Cardiac pacemaker using wireless transmission
GB2297037A (en) * 1995-01-19 1996-07-24 Vascor Inc Transcutaneous energy and information transmission apparatus

Family Cites Families (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3943936A (en) * 1970-09-21 1976-03-16 Rasor Associates, Inc. Self powered pacers and stimulators
US3824129A (en) * 1973-03-14 1974-07-16 Mallory & Co Inc P R Heart pacer rechargeable cell and protective control system
US3942535A (en) * 1973-09-27 1976-03-09 G. D. Searle & Co. Rechargeable tissue stimulating system
US4134408A (en) * 1976-11-12 1979-01-16 Research Corporation Cardiac pacer energy conservation system
US4245640A (en) * 1977-10-07 1981-01-20 Hunt Robert J Chest motion electricity generating device
US4166470A (en) * 1977-10-17 1979-09-04 Medtronic, Inc. Externally controlled and powered cardiac stimulating apparatus
JPS56106663A (en) * 1980-01-31 1981-08-25 Tokyo Shibaura Electric Co Transmitting medium for energy to organism buried device
US4763656A (en) * 1985-06-13 1988-08-16 Beatrice T. Kester Transcutaneous electrical nerve stimulation device and method
IT1214738B (en) * 1986-11-11 1990-01-18 Sbm Soc Brevetti Medicina IMPROVEMENT IN CARDIAC STIMULATION SYSTEMS VIA PACEMAKER
US4987897A (en) * 1989-09-18 1991-01-29 Medtronic, Inc. Body bus medical device communication system
JPH0659319B2 (en) * 1989-11-17 1994-08-10 三洋電機株式会社 Wireless low frequency therapy device
US5383915A (en) * 1991-04-10 1995-01-24 Angeion Corporation Wireless programmer/repeater system for an implanted medical device
US5193539A (en) * 1991-12-18 1993-03-16 Alfred E. Mann Foundation For Scientific Research Implantable microstimulator
US5314457A (en) * 1993-04-08 1994-05-24 Jeutter Dean C Regenerative electrical
US5476488A (en) * 1993-12-15 1995-12-19 Pacesetter, Inc. Telemetry system power control for implantable medical devices
US5487760A (en) * 1994-03-08 1996-01-30 Ats Medical, Inc. Heart valve prosthesis incorporating electronic sensing, monitoring and/or pacing circuitry
US5466246A (en) * 1994-07-29 1995-11-14 Pacesetter, Inc. Telemetry receiver for implantable device, incorporating digital signal processing
US5630835A (en) * 1995-07-24 1997-05-20 Cardiac Control Systems, Inc. Method and apparatus for the suppression of far-field interference signals for implantable device data transmission systems
US5683432A (en) * 1996-01-11 1997-11-04 Medtronic, Inc. Adaptive, performance-optimizing communication system for communicating with an implanted medical device

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0071131A2 (en) * 1981-07-30 1983-02-09 Jürgen J. Dipl.-Phys. Dr.-Ing. Hildebrandt Device for stimulating a human muscle
US4886064A (en) 1987-11-25 1989-12-12 Siemens Aktiengesellschaft Body activity controlled heart pacer
EP0362611A1 (en) * 1988-09-19 1990-04-11 Medtronic, Inc. Body bus medical device communication system
US5405367A (en) 1991-12-18 1995-04-11 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
US5411535A (en) 1992-03-03 1995-05-02 Terumo Kabushiki Kaisha Cardiac pacemaker using wireless transmission
GB2297037A (en) * 1995-01-19 1996-07-24 Vascor Inc Transcutaneous energy and information transmission apparatus

Cited By (126)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1222943A1 (en) * 2001-01-16 2002-07-17 Kenergy Inc Wireless cardiac pacing system with vascular electrode-stents
US8938300B2 (en) 2004-05-04 2015-01-20 University Of Rochester Leadless implantable intravascular electrophysiologic device for neurologic/cardiovascular sensing and stimulation
EP1744809A1 (en) * 2004-05-04 2007-01-24 University Of Rochester Leadless implantable intravascular electrophysiologic device for neurologic/cardiovascular sensing and stimulation
US8849416B2 (en) 2004-05-04 2014-09-30 University Of Rochester Implantable bio-electro-physiologic interface matrix
EP1744809A4 (en) * 2004-05-04 2008-05-07 Univ Rochester Leadless implantable intravascular electrophysiologic device for neurologic/cardiovascular sensing and stimulation
US10850092B2 (en) 2004-10-20 2020-12-01 Boston Scientific Scimed, Inc. Leadless cardiac stimulation systems
US9925386B2 (en) 2004-10-20 2018-03-27 Cardiac Pacemakers, Inc. Leadless cardiac stimulation systems
US9545513B2 (en) 2004-10-20 2017-01-17 Cardiac Pacemakers, Inc. Leadless cardiac stimulation systems
US10493288B2 (en) 2004-10-20 2019-12-03 Boston Scientific Scimed Inc. Leadless cardiac stimulation systems
US9072911B2 (en) 2004-10-20 2015-07-07 Boston Scientific Scimed, Inc. Leadless cardiac stimulation systems
US10076658B2 (en) 2004-10-20 2018-09-18 Cardiac Pacemakers, Inc. Leadless cardiac stimulation systems
US10029092B2 (en) 2004-10-20 2018-07-24 Boston Scientific Scimed, Inc. Leadless cardiac stimulation systems
WO2006124833A3 (en) * 2005-05-18 2007-05-31 Cardiac Pacemakers Inc Modular antitachyarrhythmia therapy system
US9993654B2 (en) 2005-05-18 2018-06-12 Cardiac Pacemakers, Inc. Modular antitachyarrhythmia therapy system
US10363428B2 (en) 2005-05-18 2019-07-30 Cardiac Pacemakers, Inc. Modular antitachyarrhythmia therapy system
US11083898B2 (en) 2005-05-18 2021-08-10 Cardiac Pacemakers, Inc. Modular antitachyarrhythmia therapy system
US9352164B2 (en) 2005-05-18 2016-05-31 Cardiac Pacemakers, Inc. Modular antitachyarrhythmia therapy system
US9242113B2 (en) 2005-05-18 2016-01-26 Cardiac Pacemarkers, Inc. Modular antitachyarrhythmia therapy system
US8391990B2 (en) 2005-05-18 2013-03-05 Cardiac Pacemakers, Inc. Modular antitachyarrhythmia therapy system
US8649859B2 (en) 2005-05-18 2014-02-11 Cardiac Pacemakers, Inc. Modular antitachyarrhythmia therapy system
US8903500B2 (en) 2005-05-18 2014-12-02 Cardiac Pacemakers, Inc. Modular antitachyarrhythmia therapy system
WO2006124833A2 (en) * 2005-05-18 2006-11-23 Cardiac Pacemakers, Inc. Modular antitachyarrhythmia therapy system
US9002467B2 (en) 2005-05-18 2015-04-07 Cardiac Pacemakers, Inc. Modular antitachyarrhythmia therapy system
WO2007019207A1 (en) * 2005-08-08 2007-02-15 Kenergy, Inc. Intravascular stimulation system with wireless power supply
US10022538B2 (en) 2005-12-09 2018-07-17 Boston Scientific Scimed, Inc. Cardiac stimulation system
US11766219B2 (en) 2005-12-09 2023-09-26 Boston Scientific Scimed, Inc. Cardiac stimulation system
US11154247B2 (en) 2005-12-09 2021-10-26 Boston Scientific Scimed, Inc. Cardiac stimulation system
US8321021B2 (en) 2006-01-13 2012-11-27 Universität Duisburg-Essen Stimulation system, in particular a cardiac pacemaker
WO2007087875A1 (en) * 2006-01-13 2007-08-09 Universität Duisburg-Essen Stimulation system, in particular a cardiac pacemaker
US8050759B2 (en) 2006-01-31 2011-11-01 Medtronic, Inc. Subcutaneous ICD with separate cardiac rhythm sensor
WO2007090014A1 (en) 2006-01-31 2007-08-09 Medtronic, Inc Subcutaneous icd with separate cardiac rhythm sensor
FR2903912A1 (en) * 2006-07-20 2008-01-25 Commissariat Energie Atomique Implantable pacemaker for treating e.g. bradycardia, has control modules each including control system to modify stimulation parameters of heart via actuator module if difference between contraction signals exceeds fixed threshold
US9308374B2 (en) 2006-07-21 2016-04-12 Boston Scientific Scimed, Inc. Delivery of cardiac stimulation devices
US10426952B2 (en) 2006-07-21 2019-10-01 Boston Scientific Scimed, Inc. Delivery of cardiac stimulation devices
US11338130B2 (en) 2006-07-21 2022-05-24 Boston Scientific Scimed, Inc. Delivery of cardiac stimulation devices
US9662487B2 (en) 2006-07-21 2017-05-30 Boston Scientific Scimed, Inc. Delivery of cardiac stimulation devices
WO2008034005A3 (en) * 2006-09-13 2008-07-10 Boston Scient Scimed Inc Cardiac stimulation using leadless electrode assemblies
US9956401B2 (en) 2006-09-13 2018-05-01 Boston Scientific Scimed, Inc. Cardiac stimulation using intravascularly-deliverable electrode assemblies
WO2008034005A2 (en) * 2006-09-13 2008-03-20 Boston Scientific Scimed, Inc. Cardiac stimulation using leadless electrode assemblies
US7899537B1 (en) 2006-10-27 2011-03-01 Pacesetter, Inc. Pericardial cardioverter defibrillator
US7894915B1 (en) 2006-10-27 2011-02-22 Pacesetter, Inc. Implantable medical device
WO2008066424A1 (en) * 2006-11-30 2008-06-05 St. Jude Medical Ab Device and method for initiating communication with a selected implantable medical device by means of a directional antenna
US9393405B2 (en) 2008-02-07 2016-07-19 Cardiac Pacemakers, Inc. Wireless tissue electrostimulation
US10307604B2 (en) 2008-02-07 2019-06-04 Cardiac Pacemakers, Inc. Wireless tissue electrostimulation
US9795797B2 (en) 2008-02-07 2017-10-24 Cardiac Pacemakers, Inc. Wireless tissue electrostimulation
US8180456B2 (en) 2009-06-09 2012-05-15 Pacesetter, Inc. Systems and methods to configure a multi-electrode lead
WO2012007131A1 (en) * 2010-07-13 2012-01-19 Peter Osypka Central control unit of implants
US9592391B2 (en) 2014-01-10 2017-03-14 Cardiac Pacemakers, Inc. Systems and methods for detecting cardiac arrhythmias
US10722720B2 (en) 2014-01-10 2020-07-28 Cardiac Pacemakers, Inc. Methods and systems for improved communication between medical devices
US9526909B2 (en) 2014-08-28 2016-12-27 Cardiac Pacemakers, Inc. Medical device with triggered blanking period
US10238882B2 (en) 2015-02-06 2019-03-26 Cardiac Pacemakers Systems and methods for treating cardiac arrhythmias
US10220213B2 (en) 2015-02-06 2019-03-05 Cardiac Pacemakers, Inc. Systems and methods for safe delivery of electrical stimulation therapy
US11020595B2 (en) 2015-02-06 2021-06-01 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
US9669230B2 (en) 2015-02-06 2017-06-06 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
US11224751B2 (en) 2015-02-06 2022-01-18 Cardiac Pacemakers, Inc. Systems and methods for safe delivery of electrical stimulation therapy
US10046167B2 (en) 2015-02-09 2018-08-14 Cardiac Pacemakers, Inc. Implantable medical device with radiopaque ID tag
US11020600B2 (en) 2015-02-09 2021-06-01 Cardiac Pacemakers, Inc. Implantable medical device with radiopaque ID tag
US11285326B2 (en) 2015-03-04 2022-03-29 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
US10213610B2 (en) 2015-03-18 2019-02-26 Cardiac Pacemakers, Inc. Communications in a medical device system with link quality assessment
US10946202B2 (en) 2015-03-18 2021-03-16 Cardiac Pacemakers, Inc. Communications in a medical device system with link quality assessment
US10050700B2 (en) 2015-03-18 2018-08-14 Cardiac Pacemakers, Inc. Communications in a medical device system with temporal optimization
US11476927B2 (en) 2015-03-18 2022-10-18 Cardiac Pacemakers, Inc. Communications in a medical device system with temporal optimization
US10357159B2 (en) 2015-08-20 2019-07-23 Cardiac Pacemakers, Inc Systems and methods for communication between medical devices
US9853743B2 (en) 2015-08-20 2017-12-26 Cardiac Pacemakers, Inc. Systems and methods for communication between medical devices
US9968787B2 (en) 2015-08-27 2018-05-15 Cardiac Pacemakers, Inc. Spatial configuration of a motion sensor in an implantable medical device
US10709892B2 (en) 2015-08-27 2020-07-14 Cardiac Pacemakers, Inc. Temporal configuration of a motion sensor in an implantable medical device
US9956414B2 (en) 2015-08-27 2018-05-01 Cardiac Pacemakers, Inc. Temporal configuration of a motion sensor in an implantable medical device
US10589101B2 (en) 2015-08-28 2020-03-17 Cardiac Pacemakers, Inc. System and method for detecting tamponade
US10226631B2 (en) 2015-08-28 2019-03-12 Cardiac Pacemakers, Inc. Systems and methods for infarct detection
US10159842B2 (en) 2015-08-28 2018-12-25 Cardiac Pacemakers, Inc. System and method for detecting tamponade
US10137305B2 (en) 2015-08-28 2018-11-27 Cardiac Pacemakers, Inc. Systems and methods for behaviorally responsive signal detection and therapy delivery
US10092760B2 (en) 2015-09-11 2018-10-09 Cardiac Pacemakers, Inc. Arrhythmia detection and confirmation
US10065041B2 (en) 2015-10-08 2018-09-04 Cardiac Pacemakers, Inc. Devices and methods for adjusting pacing rates in an implantable medical device
US10183170B2 (en) 2015-12-17 2019-01-22 Cardiac Pacemakers, Inc. Conducted communication in a medical device system
US10933245B2 (en) 2015-12-17 2021-03-02 Cardiac Pacemakers, Inc. Conducted communication in a medical device system
US10905886B2 (en) 2015-12-28 2021-02-02 Cardiac Pacemakers, Inc. Implantable medical device for deployment across the atrioventricular septum
US10583303B2 (en) 2016-01-19 2020-03-10 Cardiac Pacemakers, Inc. Devices and methods for wirelessly recharging a rechargeable battery of an implantable medical device
US10350423B2 (en) 2016-02-04 2019-07-16 Cardiac Pacemakers, Inc. Delivery system with force sensor for leadless cardiac device
US11116988B2 (en) 2016-03-31 2021-09-14 Cardiac Pacemakers, Inc. Implantable medical device with rechargeable battery
US10328272B2 (en) 2016-05-10 2019-06-25 Cardiac Pacemakers, Inc. Retrievability for implantable medical devices
US10668294B2 (en) 2016-05-10 2020-06-02 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker configured for over the wire delivery
US11497921B2 (en) 2016-06-27 2022-11-15 Cardiac Pacemakers, Inc. Cardiac therapy system using subcutaneously sensed p-waves for resynchronization pacing management
US10512784B2 (en) 2016-06-27 2019-12-24 Cardiac Pacemakers, Inc. Cardiac therapy system using subcutaneously sensed P-waves for resynchronization pacing management
US11207527B2 (en) 2016-07-06 2021-12-28 Cardiac Pacemakers, Inc. Method and system for determining an atrial contraction timing fiducial in a leadless cardiac pacemaker system
US10426962B2 (en) 2016-07-07 2019-10-01 Cardiac Pacemakers, Inc. Leadless pacemaker using pressure measurements for pacing capture verification
US10688304B2 (en) 2016-07-20 2020-06-23 Cardiac Pacemakers, Inc. Method and system for utilizing an atrial contraction timing fiducial in a leadless cardiac pacemaker system
US10391319B2 (en) 2016-08-19 2019-08-27 Cardiac Pacemakers, Inc. Trans septal implantable medical device
US11464982B2 (en) 2016-08-24 2022-10-11 Cardiac Pacemakers, Inc. Integrated multi-device cardiac resynchronization therapy using p-wave to pace timing
US10870008B2 (en) 2016-08-24 2020-12-22 Cardiac Pacemakers, Inc. Cardiac resynchronization using fusion promotion for timing management
US10780278B2 (en) 2016-08-24 2020-09-22 Cardiac Pacemakers, Inc. Integrated multi-device cardiac resynchronization therapy using P-wave to pace timing
US10905889B2 (en) 2016-09-21 2021-02-02 Cardiac Pacemakers, Inc. Leadless stimulation device with a housing that houses internal components of the leadless stimulation device and functions as the battery case and a terminal of an internal battery
US10994145B2 (en) 2016-09-21 2021-05-04 Cardiac Pacemakers, Inc. Implantable cardiac monitor
US10758737B2 (en) 2016-09-21 2020-09-01 Cardiac Pacemakers, Inc. Using sensor data from an intracardially implanted medical device to influence operation of an extracardially implantable cardioverter
US10758724B2 (en) 2016-10-27 2020-09-01 Cardiac Pacemakers, Inc. Implantable medical device delivery system with integrated sensor
US10413733B2 (en) 2016-10-27 2019-09-17 Cardiac Pacemakers, Inc. Implantable medical device with gyroscope
US11305125B2 (en) 2016-10-27 2022-04-19 Cardiac Pacemakers, Inc. Implantable medical device with gyroscope
US10463305B2 (en) 2016-10-27 2019-11-05 Cardiac Pacemakers, Inc. Multi-device cardiac resynchronization therapy with timing enhancements
US10561330B2 (en) 2016-10-27 2020-02-18 Cardiac Pacemakers, Inc. Implantable medical device having a sense channel with performance adjustment
US10765871B2 (en) 2016-10-27 2020-09-08 Cardiac Pacemakers, Inc. Implantable medical device with pressure sensor
US10434314B2 (en) 2016-10-27 2019-10-08 Cardiac Pacemakers, Inc. Use of a separate device in managing the pace pulse energy of a cardiac pacemaker
US10434317B2 (en) 2016-10-31 2019-10-08 Cardiac Pacemakers, Inc. Systems and methods for activity level pacing
US10617874B2 (en) 2016-10-31 2020-04-14 Cardiac Pacemakers, Inc. Systems and methods for activity level pacing
US10583301B2 (en) 2016-11-08 2020-03-10 Cardiac Pacemakers, Inc. Implantable medical device for atrial deployment
US10632313B2 (en) 2016-11-09 2020-04-28 Cardiac Pacemakers, Inc. Systems, devices, and methods for setting cardiac pacing pulse parameters for a cardiac pacing device
US10639486B2 (en) 2016-11-21 2020-05-05 Cardiac Pacemakers, Inc. Implantable medical device with recharge coil
US10881863B2 (en) 2016-11-21 2021-01-05 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker with multimode communication
US10894163B2 (en) 2016-11-21 2021-01-19 Cardiac Pacemakers, Inc. LCP based predictive timing for cardiac resynchronization
US10881869B2 (en) 2016-11-21 2021-01-05 Cardiac Pacemakers, Inc. Wireless re-charge of an implantable medical device
US11147979B2 (en) 2016-11-21 2021-10-19 Cardiac Pacemakers, Inc. Implantable medical device with a magnetically permeable housing and an inductive coil disposed about the housing
US11207532B2 (en) 2017-01-04 2021-12-28 Cardiac Pacemakers, Inc. Dynamic sensing updates using postural input in a multiple device cardiac rhythm management system
US10029107B1 (en) 2017-01-26 2018-07-24 Cardiac Pacemakers, Inc. Leadless device with overmolded components
US10737102B2 (en) 2017-01-26 2020-08-11 Cardiac Pacemakers, Inc. Leadless implantable device with detachable fixation
US10835753B2 (en) 2017-01-26 2020-11-17 Cardiac Pacemakers, Inc. Intra-body device communication with redundant message transmission
US11590353B2 (en) 2017-01-26 2023-02-28 Cardiac Pacemakers, Inc. Intra-body device communication with redundant message transmission
US10821288B2 (en) 2017-04-03 2020-11-03 Cardiac Pacemakers, Inc. Cardiac pacemaker with pacing pulse energy adjustment based on sensed heart rate
US10905872B2 (en) 2017-04-03 2021-02-02 Cardiac Pacemakers, Inc. Implantable medical device with a movable electrode biased toward an extended position
US11065459B2 (en) 2017-08-18 2021-07-20 Cardiac Pacemakers, Inc. Implantable medical device with pressure sensor
US10918875B2 (en) 2017-08-18 2021-02-16 Cardiac Pacemakers, Inc. Implantable medical device with a flux concentrator and a receiving coil disposed about the flux concentrator
US11235163B2 (en) 2017-09-20 2022-02-01 Cardiac Pacemakers, Inc. Implantable medical device with multiple modes of operation
US11185703B2 (en) 2017-11-07 2021-11-30 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker for bundle of his pacing
US11260216B2 (en) 2017-12-01 2022-03-01 Cardiac Pacemakers, Inc. Methods and systems for detecting atrial contraction timing fiducials during ventricular filling from a ventricularly implanted leadless cardiac pacemaker
US11071870B2 (en) 2017-12-01 2021-07-27 Cardiac Pacemakers, Inc. Methods and systems for detecting atrial contraction timing fiducials and determining a cardiac interval from a ventricularly implanted leadless cardiac pacemaker
US11052258B2 (en) 2017-12-01 2021-07-06 Cardiac Pacemakers, Inc. Methods and systems for detecting atrial contraction timing fiducials within a search window from a ventricularly implanted leadless cardiac pacemaker
US11813463B2 (en) 2017-12-01 2023-11-14 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker with reversionary behavior
US11529523B2 (en) 2018-01-04 2022-12-20 Cardiac Pacemakers, Inc. Handheld bridge device for providing a communication bridge between an implanted medical device and a smartphone
US10874861B2 (en) 2018-01-04 2020-12-29 Cardiac Pacemakers, Inc. Dual chamber pacing without beat-to-beat communication

Also Published As

Publication number Publication date
US5814089A (en) 1998-09-29
AU5526798A (en) 1998-07-15

Similar Documents

Publication Publication Date Title
US5814089A (en) Leadless multisite implantable stimulus and diagnostic system
US6141588A (en) Cardiac simulation system having multiple stimulators for anti-arrhythmia therapy
US9956401B2 (en) Cardiac stimulation using intravascularly-deliverable electrode assemblies
US4543955A (en) System for controlling body implantable action device
US11660455B2 (en) Tissue conduction communication using ramped drive signal
US4987897A (en) Body bus medical device communication system
EP0362611B1 (en) Body bus medical device communication system
US6654638B1 (en) Ultrasonically activated electrodes
EP2636426B1 (en) RF-powered communication for implantable device
US20090143836A1 (en) Method and apparatus of acoustic communication for implantable medical device
EP3717065B1 (en) Device and method to reduce artifact from tissue conduction communication transmission
US11110279B2 (en) Signal transmission optimization for tissue conduction communication
EP3723848B1 (en) Device and method with adaptive timing for tissue conduction communication transmission
US10549105B2 (en) Apparatuses and methods that improve conductive communication between external programmers and implantable medical devices
US11235162B2 (en) Tissue conduction communication between devices
US11925811B2 (en) Remote follow-up methods, systems, and devices for leadless pacemaker systems
US20220212019A1 (en) Devices, systems and methods for improving conductive communication between external devices and implantable medical devices
WO2005089868A1 (en) Device for stimulating muscle
WO2024015775A1 (en) Apparatus for cardiac event signal sensing

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AU CA JP

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): AT BE CH DE DK ES FI FR GB GR IE IT LU MC NL PT SE

DFPE Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)
121 Ep: the epo has been informed by wipo that ep was designated in this application
122 Ep: pct application non-entry in european phase