IMPLANTABLE LEADLESS PACEMAKER WITH ATRIAL-VENTRICULAR SYNCHRONIZED PACING

Abstract

An implantable leadless pacemaker (iLP) for a human or animal heart, wherein the iLP includes a housing, at least two electrode poles for picking up electrical potentials and/or delivering electrical stimulation, a stimulation control unit in connection with the electrode poles, a sensing unit that is in connection with at least one electrode pole, a signal processing unit in connection with the sensing unit, a signal evaluation unit in connection with the signal processing unit and/or the sensing unit, and an energy source. The sensing unit is configured to sense a first signal associated with an activity of the first heart chamber, and the stimulation control unit is configured to deliver electrical stimulation in the first heart chamber via the at least two electrode poles. wherein the sensing unit is configured to sense a second signal associated with an activity of a second heart chamber.

Claims

1. An implantable leadless pacemaker (iLP) for a human or animal heart, the iLP comprising: a housing; at least two electrode poles for picking up electrical potentials and/or delivering electrical stimulation; a stimulation control unit in connection with the electrode poles; a sensing unit, wherein the sensing unit is in connection with at least one electrode pole; a signal processing unit in connection with the sensing unit; a signal evaluation unit in connection with the signal processing unit and/or the sensing unit; and an energy source, wherein the iLP is configured to be anchored within a first heart chamber, and wherein the sensing unit is configured to sense electrical potentials via the at least two electrode poles, the sensing unit being configured to sense a first signal associated with an activity of the first heart chamber, wherein the stimulation control unit is configured to deliver electrical stimulation to the first heart chamber via the at least two electrode poles, and wherein the sensing unit is configured to sense a second signal associated with an activity of a second heart chamber, the second heart chamber being different from the first heart chamber.

2. The iLP according to claim 1, wherein the signal evaluation unit is configured to detect a first signal characteristic in the first signal, the first signal characteristic indicating a cardiac event of the first heart chamber, and/or wherein the signal evaluation unit is configured to detect a second signal characteristic in the second signal, the second signal characteristic indicating a cardiac event of the second heart chamber.

3. The iLP according to claim 2, wherein the cardiac event of the first heart chamber is an absence of an intrinsic contraction of the first heart chamber and wherein the cardiac event of the second heart chamber is an absence or occurrence of an intrinsic contraction of the second heart chamber.

4. The iLP according to claim 2, wherein the stimulation control unit is configured to deliver electrical stimulation in the first heart chamber in accordance with the cardiac event of the first heart chamber and/or in accordance with the cardiac event of the second heart chamber.

5. The iLP according to claim 2, wherein the stimulation unit is configured to deliver electrical stimulation when a time interval expires after the cardiac event of the second heart chamber has been detected.

6. The iLP according to claim 5, wherein the time interval corresponds to a physiological conduction time between the first heart chamber and the second heart chamber.

7. The iLP according to claim 1, wherein the second signal is an acoustic signal or a vibration signal representing a heart sound.

8. The iLP according to claim 1, wherein the second signal is an impedance signal representing contraction of a heart chamber.

9. The iLP according to claim 1, wherein the sensing unit comprises at least one sensor, the at least one sensor being an acoustic sensor, a vibration sensor, a mechanical sensor, an acceleration sensor, an electromechanical sensor, an impedance sensor, a CLS sensor, an ultrasound sensor, a temperature sensor, a pressure sensor, or a light sensor.

10. The iLP according to claim 1, wherein the first signal or the second signal is an electrical signal, a mechanical signal, an electromechanical signal, an ultrasound signal, an impedance signal, an acoustic signal, a vibration signal, a pressure signal, or a light signal.

11. The iLP according to claim 1, wherein the first signal and the second signal are comprised in one composite signal.

12. A method for operating an implantable leadless pacemaker (iLP), the iLP comprising: a housing; at least two electrode poles for picking up electrical potentials and/or delivering electrical stimulation; a stimulation control unit in connection with the electrode poles; a sensing unit, wherein the sensing unit is in connection with at least one electrode pole; a signal processing unit in connection with the sensing unit; a signal evaluation unit in connection with the signal processing unit and/or the sensing unit; and an energy source, the method comprising: sensing a first signal associated with an activity of the first heart chamber via the sensing unit; sensing a second signal associated with an activity of a second heart chamber via the sensing unit, the second heart chamber being different from the first heart chamber; and performing electrical stimulation in the first chamber of the heart via the at least two electrode poles via the stimulation control unit.

13. The method according to claim 12, wherein the step of sensing a first signal comprises detecting a first signal characteristic in the first signal via the signal evaluation unit, the first signal characteristic indicating a cardiac event of the first heart chamber, the cardiac event of the first heart chamber being an absence of an intrinsic contraction of the first heart chamber; and wherein the step of sensing a second signal comprises detecting a second signal characteristic in the second signal via the signal evaluation unit, the second signal characteristic indicating a cardiac event of the second heart chamber, and the cardiac event of the second heart chamber being an absence or an occurrence of an intrinsic contraction of the second heart chamber, and wherein the step of performing electrical stimulation comprises starting a timer after the cardiac event of the second heart chamber has been detected and delivering the electrical stimulation in the first heart chamber after expiration of a time interval, the time interval corresponding to a physiological conduction time between two chambers of the heart.

14. The method according to claim 12, wherein the second signal is an acoustic or a vibration signal representing a heart sound.

15. The method according to claim 12, wherein the first signal or the second signal is an electrical signal, a mechanical signal, an electromechanical signal, an ultrasound signal, an impedance signal, a pressure signal, or a light signal.

16. The method according to claim 12, wherein the first signal and the second signal are comprised in one composite signal.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0033] The present invention will become more fully understood from the detailed description given hereinbelow and the accompanying drawings which are given by way of illustration only, and thus, are not limitive of the present invention, and wherein:

[0034] FIG. 1 shows a simplified block diagram of a proposed iLP;

[0035] FIG. 2 shows an exemplary set of acoustic sensor data captured in the ventricle showing atrial contraction events;

[0036] FIG. 3 shows an exemplary set of acoustic sensor data captured in the ventricle with markers indicating cardiac activity;

[0037] FIG. 4 shows an exemplary set of accelerometer sensor data captured in the ventricle with markers indicating cardiac activity;

[0038] FIG. 5 shows exemplary experimental accelerometer data captured in the ventricle showing atrial contraction events in the ventricular wall acceleration;

[0039] FIG. 6 shows an exemplary set of intracardiac electrogram (IEGM) data and impedance sensor data captured in the ventricle; and

[0040] FIG. 7 shows exemplary experimental impedance data captured in the ventricle with markers indicating cardiac activity

DETAILED DESCRIPTION

[0041] Referring to FIG. 1, an exemplary embodiment of the disclosed iLP 10 according to the invention is depicted schematically. iLP 10 comprises a sensing unit 20, signal processing unit and signal evaluation unit 30, stimulation control unit 40, electrode 50 and housing 51. Sensing unit 20 may include a sensor for detecting a signal which represents atrial activity 21, as for instance an acoustic transducer. Alternatively, sensor 21 may be a vibration sensor, a mechanical sensor, an acceleration sensor, an electromechanical sensor, an impedance sensor, a CLS sensor, an ultrasound sensor, a temperature sensor, a pressure sensor, a light sensor, etc. Signal sensing unit 20 further comprises at least a sensor 22 for measuring an electrogram, for instance a ventricular electrogram. The electrogram may be sensed via electrode 50. The signal processing unit and signal evaluation unit 30 comprise for instance an atrial event detector 31 and a detector for sensed ventricular events 32, wherein the atrial event detector 31 is configured to detect atrial events in the signal sensed by 21, and the detector for sensed ventricular events 32 is configured to detect ventricular events in the signal sensed by sensor 22. Moreover, signal evaluation unit 30 is configured to relate the detected atrial and ventricular events, such that the atrial event detector 31 processes acoustic signals from the transducer and applies ventricular state timing signals. The atrial event detector 31 is able to detect atrio-ventricular filling events from within the ventricle by observing acoustic signals imparted on the device as a result of atrial contraction and blood ejection into the ventricle. The proposed iLP 10 is capable to detect atrial contraction (‘kick’) filling events from within the ventricle in which the iLP is implanted. The atrial kick is the ventricular pre-load induced by blood filling the ventricle as the atrium contracts. The action of pre-load causes an acoustic vibration to be induced in the ventricle as the tricuspid valve opens and the ventricle accommodates the incoming blood. This acoustic signal is sensed via an acoustic transducer in the ventricular iLP. The acoustic transducer may be a microphone or any vibrational sensor suitable for the task. The sensed acoustic signal is then processed by the atrial event detector 31 from the signal processing unit 30 which detects atrial events during the quiescent period of ventricular expansion (after the ventricle has contracted, and the tricuspid valve has opened). The atrial event detection circuit monitors this period for sudden atrial-induced acoustic signals which exhibit an acoustic energy beyond a threshold for detection. When an atrial-induced acoustic event is detected, the acoustic signal is processed for atrial events according to ventricular state as provided by ventricular event timing signals (e.g. sense and pace event markers, blanking) to the atrial event detector 31. The atrial event detector 31 may utilize bandpass pre-filtering tuned to the atrial event frequency components, as well as threshold crossing detection on this filtered signal to evaluate the incoming acoustic vibration signal stream for atrial events. Stimulation control unit 40 comprises a pacing control unit 41 which receives information on detected atrial and/or ventricular events from the atrial event detector 31 and the detector for sensed ventricular events 32 and controls electrical stimulation according to the information via electrode 50. Moreover, the information concerning coordination of electrical stimulation can be passed from pacing control unit 41 back to the signal processing unit and the detector for sensed ventricular events 32, and the atrial event detector 31, respectively.

[0042] FIG. 2 shows an example of an acoustic data stream 60 as captured in the ventricle. The atrial contraction events (indicated with arrows 61) immediately prior to ventricular events 62, which are electrically-detected QRS markers sensed in the intracardiac electrogram (IEGM). The information on the ventricular events 62 can be obtained for instance via sensor 22 in combination with sensed ventricular event detector 32, wherein the atrial contraction events 61 can be obtained via sensor 21 in combination with atrial event detector 31. Later heart sounds are induced by systolic phase valve operation, in synchrony with and following the electrical QRS signal.

[0043] FIG. 3 shows an exemplary set of acoustic sensor data captured in the ventricle with markers indicating cardiac activity and an example of the inventive method for detecting atrial activity according to an exemplary acoustic data stream 60 as captured in the ventricle electrically-detected QRS markers 62. Following a QRS detection 62, the atrial event detector 31 begins a ventricular systole activity timer 70 during which no atrial activity should be detected. Arrow 90 points to end of a systole as the pulmonary artery valve closes. At the end of ventricular systole phase, the atrial event detector 31 enters a detection phase 80 where the circuit expects an atrial event 61 to trigger its atrial detection marker when the acoustic vibration exceeds a threshold 100. This then counts as an atrial event, which is passed to the iLP signal evaluation unit 30, which may comprise VDD (pacemaker operation mode where electrical stimulation is performed in the ventricle according to atrial activity, involving AV conduction monitoring) timing. For example, in patients exhibiting A-V block arrythmias, atrial event timing as disclosed is used to drive a VDD pacing mode for the iLP. In such an implantable leadless pacemaker, VDD functionality is achieved by use of atrial marker events, which start a ventricular event timer, the expiration of which will cause a ventricular pace if no intrinsic ventricular QRS has been sensed during timer countdown. The benefits of VDD mode vs VVI mode are well known in the cardiac therapeutics field.

[0044] FIG. 4 shows an exemplary set of accelerometer data 112 from measurements at the ventricular wall, wherein atrial contraction events 111 can be identified according to the ventricular wall acceleration immediately prior to ventricular IEGM sense events 110. Acceleration later than the ventricular IEGM sense events 110 is due to ventricular contraction and expansion.

[0045] In FIG. 5, experimental accelerometer data is illustrated which data calculated from the accelerometer signal measured in the right ventricle wall. 120 is the marker channel corresponding to the right atrium, 121 is the acceleration in m/s.sup.2, 122 is the velocity in mm/s, 123 is the displacement in mm. The S in 120 indicates a sensed event in the right atrium, which is an atrial contraction event.

[0046] FIG. 6 illustrates an experimental IEGM data 130 and the according impedance stream data 132 showing atrial contraction event 131 immediately prior to ventricular IEGM QRS event 133.

[0047] FIG. 7 illustrates experimental data from FIG. 6 showing electrical activity markers in the IEGM data 130, and impedance stream data 132 indicating the atrial-induced ventricular impedance deflection. Following a QRS detection 133, the atrial event detector 31 begins a ventricular systole activity timer 134 during which no atrial activity should be detected. At the end of the ventricular systole phase, the atrial event detector 31 enters a detection phase 135 where the circuit expects an atrial event 131 to trigger its atrial detection marker when the impedance exceeds a threshold 136. This then counts as an atrial event, which is passed to the iLP signal evaluation unit 30, which may comprise pacemaker VDD timing and logic circuit.

[0048] It will be apparent to those skilled in the art that numerous modifications and variations of the described examples and embodiments are possible in light of the above teaching. The disclosed examples and embodiments are presented for purposes of illustration only. Other alternate embodiments may include some or all of the features disclosed herein. Therefore, it is the intent to cover all such modifications and alternate embodiments as may come within the true scope of this invention.