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Distinguishing premature contractions in a medical device

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20120277611 patent thumbnailZoom

Distinguishing premature contractions in a medical device

A method and device of distinguishing premature contractions that includes a sensor sensing cardiac signals, and a processor configured to determine a plurality of R-waves in response to the sensed cardiac signal, detect a premature contraction being associated with a first R-wave of the plurality of R-waves, determining a first area of the detected first R-wave, determine a second area of a second R-wave, determine a ratio of the first area and the second area, compare the ratio to a ratio threshold, and identify the detected premature contraction as one of a premature atrial contraction or a premature ventricular contraction in response to the comparing..
Related Terms: Contractions Premature Atrial Contraction Premature Contraction Premature Ventricular Contraction

Medtronic, Inc. - Browse recent Medtronic patents - ,
Inventors: Raphael Schneider, Raja N. Ghanem
USPTO Applicaton #: #20120277611 - Class: 600521 (USPTO) - 11/01/12 - Class 600 
Surgery > Diagnostic Testing >Cardiovascular >Heart >Detecting Heartbeat Electric Signal >Detecting R Portion Of Signal Waveform

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The Patent Description & Claims data below is from USPTO Patent Application 20120277611, Distinguishing premature contractions in a medical device.

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The present application claims priority and other benefits from U.S. Provisional Patent Application Ser. No. 61/480,044, filed Apr. 28, 2011, entitled “DISTINGUISHING PREMATURE CONTRACTIONS IN A MEDICAL DEVICE” (Attorney Docket P0041925.00), incorporated herein by reference in its entirety.


Cross-reference is hereby made to the commonly-assigned related U.S. application Ser. No. ______, (Attorney Docket Number P0041925.USU1), entitled “DISTINGUISHING PREMATURE CONTRACTIONS IN A MEDICAL DEVICE”, to Schneider et al., and application Ser. No. ______ (Attorney Docket Number P0041925.USU2), entitled “DISTINGUISHING PREMATURE CONTRACTIONS IN A MEDICAL DEVICE”, to Schneider et al. filed concurrently herewith and incorporated herein by reference in it\'s entirety.


The present disclosure relates generally to cardiac monitoring systems and, in particular, to a method and apparatus for distinguishing premature contractions in a medical device.


Patients suffering from heart failure can experience severe symptoms leading to hospitalization as their heart failure worsens. It is desirable to prevent hospitalization and worsening heart failure symptoms by managing medications and other heart failure therapies, such as cardiac resynchronization therapy (CRT). However, clinicians are challenged in detecting a worsening state of heart failure patient before the patient becomes overtly symptomatic and hospitalization is required. A need remains for medical devices and methods for ambulatory monitoring of heart failure patients that improves early detection of a worsening heart failure condition.


FIG. 1 is a schematic diagram of an implantable medical device (IMD) optionally coupled to a lead positioned within a heart in a patient\'s body.

FIG. 2 is a functional block diagram of one embodiment of the IMD shown in FIG. 1.

FIG. 3 is a flow chart of a method for monitoring HRT in a patient.

FIG. 4 is a flow chart of a method for monitoring HRT according to an alternative embodiment.

FIG. 5A is a representative R-wave showing amplitude metrics that may be determined for use in confirming a premature ventricular contraction (PVC).

FIG. 5B is a representative R-wave showing area metrics that may be determined for use in confirming a PVC.

FIG. 6 is a flow chart of a method for establishing morphology-related metrics and thresholds for positively identifying PVCs during HRT monitoring.

FIG. 7 is a flowchart of a method of distinguishing premature contractions as being one of a premature atrial contraction and a premature ventricular contraction, according to an embodiment of the disclosure.

FIG. 8 is a flowchart of a method of distinguishing premature contractions as being one of a premature atrial contraction and a premature ventricular contraction, according to an embodiment of the disclosure.

FIG. 9 is a flowchart of a method of distinguishing premature contractions as being one of a premature atrial contraction and a premature ventricular contraction, according to an embodiment of the disclosure.


In the following description, references are made to illustrative embodiments. It is understood that other embodiments may be utilized without departing from the scope of the disclosure. As used herein, the term “module” refers to an application specific integrated circuit (ASIC), an electronic circuit, a processor (shared, dedicated, or group) and memory that execute one or more software or firmware programs, a combinational logic circuit, or other suitable components that provide the described functionality.

An impaired autonomic nervous system (ANS) is associated with higher mortality and hospitalization risk in patients. Heart rate turbulence (HRT) is a physiological response of the sinus node to a premature ventricular contraction (PVC). HRT can be used as a measure of the health of the ANS. A PVC causes a brief disturbance of heart rate and arterial blood pressure. A PVC is a ventricular depolarization, also referred to as a ventricular ectopic beat, arising from the ventricular myocardium, rather than arising from the sinoatrial node and being conducted normally from the atria to the ventricles through the heart\'s natural conduction system.

When a PVC occurs, the heart typically does not have ample time to fill with blood prior to the premature beat, thus resulting in reduced arterial blood pressure and blood flow. In a healthy person, this change in blood pressure typically stimulates baroreceptors, which are nerve endings in the vasculature that are sensitive to changes in blood pressure. When the baroreceptors are stimulated, a neural reflex affects the heart and vasculature to increase heart rate and blood pressure in an attempt to restore the body to its normal state. Until the normal pressure can be restored, however, oscillations in the patient\'s heart rate is frequently observed due to the changes in cardiac output originating with the PVC beat. If the patient is in good health, the response to changes in cardiac output and arterial pressure is relatively large and the heart recovers relatively quickly. If the patient has an impaired ANS diminishing the arterial baroreflex, heart rate oscillations may be depressed. Accordingly, the duration and magnitude of heart rate turbulence (HRT) following a heart beat perturbation can be a good indicator of the health of the ANS of the patient. In particular, measuring HRT following a PVC is believed to be useful in identifying patients at risk for congestive heart failure (CHF), CHF decompensation, sudden cardiac death, and other forms of heart disease.

A PVC can be observed as a short ventricular cycle, i.e. the interval between two consecutive R-waves, with no intervening atrial beat. For HRT calculation it is important that only PVCs are used and not premature atrial contractions (PACs) because the response of the sinus rhythm after a PAC produces different results. The different response following a PAC, if measured and included with measurements associated with a true PVC, would confound HRT measurements. A PAC can be conducted to the ventricles and appear like a short ventricular cycle, potentially being detected as a PVC when PVC detection is based on intervals measured between R-waves. In a dual chamber device having both atrial and ventricular sensing electrodes or when using multi-lead ECG signals, PVCs can be readily identified by a shortened ventricular cycle length without an intervening atrial depolarization signal, i.e. a P-wave.

In a cardiac monitoring device that relies on a single ECG lead, subcutaneous electrodes, or a single chamber device having electrodes located only in a ventricular chamber, it can be difficult to differentiate PACs and PVCs based on the absence of a P-wave during a short ventricular cycle because the P-wave signal is of very low amplitude or absent. Furthermore, the available processing power in a small implantable device, such as an implantable ECG recorder or hemodynamic monitor, may be limited precluding highly complex signal analysis methods. Automatic and reliable identification of PVCs originating in the ventricles, i.e. ventricular ectopic beats, for HRT assessment that requires only a single ECG lead or EGM signal without requiring high processing burden is needed.

In addition to subcutaneous or external cardiac monitors, the relationship between HRT and cardiac health can be beneficially exploited in other implantable medical devices (IMDs) such as pacemakers, implantable cardioverter-defibrillators (ICDs), an automatic external defibrillator (AED) or heart monitor and the like. According to various embodiments, an implantable medical device (IMD) detects PVCs and monitors HRT resulting from a PVC to determine an indication of the patient\'s cardiac health. The perturbation may be naturally occurring in the patient. HRT measurements made by the IMD can be used for enhanced monitoring, diagnosis and/or therapeutic functions in response to the measured turbulence. For example, the IMD may store diagnostic data in a memory, activate an alarm to the patient if medical attention is potentially warranted, or the like. In further embodiments, the IMD administers or adjusts an appropriate therapy or other response when such treatment or adjustment to the treatment is needed. As used herein, the term “response” is intended to broadly encompass any type of medical response, alarm, report, telemetered data or the like (including storage of data within the IMD), as well as any of the various therapies that may be provided by the IMD to the patient. In a further embodiment, HRT may be used to determine optimal settings for a pacemaker, or for optimal delivery of a pharmaceutical or other therapy.

FIG. 1 is a schematic diagram of an IMD 10 optionally coupled to a lead 14 positioned within a heart 8 in a patient\'s body 6. IMD 10 may correspond to a variety of implantable medical devices including an ECG monitor, cardiac pacemaker, implantable cardioverter defibrillator (ICD), implantable hemodynamic monitor, a drug pump, a neurostimulator or the like. IMD 10 may or may not be provided with therapy delivery capabilities. When provided with therapy delivery capabilities, IMD 10 may be coupled to additional leads and/or catheters operatively positioned relative to the patient\'s heart 8 or other body tissues for deploying stimulating/sensing electrodes, physiological sensors, and/or drug delivery ports. While lead 14 is shown carrying sense/pace electrodes 16 and 18 positioned within the right ventricle of the patient\'s heart in the illustrative embodiment, it is recognized that lead 14 may be configured to extend transvenously into other heart chambers or blood vessels or subcutaneously away from IMD 10 to other body locations for positioning any number of electrodes and/or physiological sensors in a desired location.

In one embodiment, IMD 10 corresponds to an implantable cardiac signal monitor capable of at least sensing an ECG or intracardiac EGM signal using an intracardiac lead 14 and/or subcutaneous electrodes 42 and 44 incorporated in the housing 12 of IMD 10. Subcutaneous electrodes may additionally or alternatively be carried by a lead. IMD 10 receives the ECG and/or EGM signals, collectively referred to herein as “cardiac electrical signals” or simply “cardiac signals”.

Housing 12 encloses circuitry (not shown in FIG. 1) included in IMD 10 for controlling and performing device functions and processing sensed signals as described herein. Cardiac signals may be stored and/or analyzed by IMD 10 for diagnostic or prognostic purposes. Cardiac arrhythmias, heart rate, premature contractions, and other events may be detected and corresponding data may be stored by IMD 10.

In particular and as further described herein, IMD 10 will detect PVCs and evaluate cardiac signals subsequent to the disturbance associated with a PVC for computing metrics of HRT. HRT metrics are then available to a clinician for diagnosis and prognosis of various heart-related conditions.

IMD 10 is capable of bidirectional communication with an external device 26 via bidirectional telemetry link 28. Device 26 may be embodied as a programmer, typically located in a hospital or clinic, used to program the operating mode and various operational variables of IMD 10 and interrogate IMD 10 to retrieve data acquired and stored by IMD 10. Device 26 may alternatively be embodied as a home monitor used for remote patient monitoring for retrieving data from the IMD 10. Data stored and retrieved from IMD 10 may include data related to IMD function determined through automated self-diagnostic tests as well as physiological data acquired by IMD 10 including HRT data.

External device 26 is further shown in communication with a central database 24 via communication link 30, which may be a wireless or hardwired link. Programming data and interrogation data may be transmitted via link 30. Central database 24 may be a centralized computer, Internet-based or other networked database used by a clinician for remote monitoring and management of patient 6. An example of a remote patient management system in which tissue oxygenation monitoring may be incorporated for monitoring heart failure patients is generally described in commonly-assigned U.S. Pat. No. 6,599,250 (Webb, et al.), hereby incorporated herein by reference in its entirety. It is recognized that other external devices, such as other physiological monitoring devices or other types of programming devices, may be used in conjunction with IMD 10 and incorporate portions of the methods described herein.

The methods described herein for analyzing cardiac signals to determine HRT metrics may be implemented in IMD 10 and the results of data analysis transmitted to external device 26 upon an interrogation request and optionally on to central database 24. IMD receives a cardiac signal, detects PVCs, computes HRT metrics and stores the metrics for transmission to external device 26. Alternatively, raw cardiac signal data may be transmitted from IMD 10 to external device 26 with the data analysis performed by external device 26 and/or central database 24. In still other embodiments, the signal analysis may be performed in a distributed manner across the IMD 10, external device 26, and/or central database 24. For example, IMD 10 may detect PVCs and transmit only cardiac signal segments containing a valid PVC for HRT analysis by external device 26 or central database 24.

FIG. 2 is a functional block diagram of one embodiment of IMD 10. IMD 10 generally includes timing and control circuitry 52 and an operating system that may employ microprocessor 54 or a digital state machine for timing sensing and therapy delivery functions (when present) in accordance with a programmed operating mode. Microprocessor 54 and associated memory 56 are coupled to the various components of IMD 10 via a data/address bus 55.

IMD 10 may include therapy delivery module 50 for delivering a therapy under the control of microprocessor 54 in response to determining a need for therapy, e.g., based on sensed physiological signals. Therapy delivery module 50 may provide drug delivery therapies or electrical stimulation therapies, including neurostimulation or cardiac pacing, cardiac resynchronization therapy, or anti-arrhythmia therapies. Therapies are delivered by module 50 under the control of timing and control circuitry 52.

Therapy delivery module 50 may be coupled to two or more electrodes 68 via an optional switch matrix 58 for delivering an electrical stimulation therapy such as cardiac pacing or neurostimulation. Electrodes 68 may correspond to any of the electrodes 16, 18, 42 and 44 shown in FIG. 1.

Electrodes 68 are also used for receiving cardiac electrical signals through any unipolar or bipolar sensing configuration. Cardiac electrical signals are monitored for diagnostic or prognostic purposes, managing a patient condition, and may be used for determining when an automatically-delivered therapy is needed and controlling the timing and delivery of the therapy. Signal processor 60 receives cardiac signals and includes sense amplifiers and may include other signal conditioning circuitry and an analog-to-digital converter. Cardiac electrical signals received from electrodes 68, which may be intracardiac EGM signals, far field EGM signals, or subcutaneous ECG signals, are used for detecting PVCs and determining HRT metrics.

IMD 10 may be coupled to one or more sensors 70 of physiological signals other than cardiac electrical signals. Physiological sensors may include a pressure sensor, activity sensor, oxygen sensor or the like. Sensor signals are received by sensor interface 62, which may provide initial amplification, filtering, rectification, or other signal conditioning. Sensor signals are used by signal processor 60 and/or microprocessor 54 for detecting physiological events or conditions.

The operating system includes associated memory 56 for storing operating algorithms and control parameter values that are used by microprocessor 54. The memory 56 may also be used for storing data compiled from sensed cardiac signals and/or relating to device operating history for telemetry out on receipt of a retrieval or interrogation instruction. Microprocessor 54 may respond to cardiac signals by altering a therapy, triggering data analysis and storage, or triggering alert 74 to generate an alert signal to the patient or a clinician that a condition has been detected that may require medical intervention. Data relating to physiological signal processing may be stored in memory 56 for later retrieval. For example, PVC detection may trigger a HRT analysis and data storage. When PVC detections, a HRT metric or trend thereof reaches a predetermined threshold, an alert signal may be generated by alert module 74 in the form of an audible sound, vibration, transmittable message or other notification.

FIG. 3 is a flow chart 100 of a method for monitoring HRT in a patient. Flow chart 100 and other flow charts presented herein are intended to illustrate the functional operation of the device, and should not be construed as reflective of a specific form of software or hardware necessary to practice the methods described. It is believed that the particular form of software will be determined primarily by the particular system architecture employed in the device and by the particular detection and therapy delivery methodologies employed by the device. Providing software to accomplish the described functionality in the context of any modern IMD, given the disclosure herein, is within the abilities of one of skill in the art.

Methods described in conjunction with flow charts presented herein may be implemented in a computer-readable medium that includes instructions for causing a programmable processor to carry out the methods described. A “computer-readable medium” includes but is not limited to any volatile or non-volatile media, such as a RAM, ROM, CD-ROM, NVRAM, EEPROM, flash memory, and the like. The instructions may be implemented as one or more software modules, which may be executed by themselves or in combination with other software.

At block 102, cardiac signal sensing is performed using one or more selected electrode pairs. At block 104, R-waves are sensed from the cardiac signal. R-wave sensing may be performed according to any method implemented in the IMD. Typically, an automatically adjusting threshold is applied to the cardiac signal for sensing R-waves as generally described in U.S. Pat. No. 5,117,824 (Keimel, et al.), hereby incorporated herein by reference in its entirety. At block 105, intervals between consecutively sensed R-waves, i.e. RR intervals, are analyzed to determine if an RR interval corresponding to a PVC coupling interval is detected as determined at decision block 106. Criteria for detecting a PVC coupling interval may vary between embodiments. One method for detecting a PVC coupling interval is described in greater detail in conjunction with FIG. 4. Generally, a PVC coupling interval is detected as an interval that is shorter than at least one or more preceding RR intervals. Additionally or alternatively, one or more subsequent RR intervals may be compared to a given RR interval for detecting a PVC coupling interval.

If a PVC coupling interval is detected, as determined at decision block 106, the process advances to block 108 to identify an R-wave fiducial point for each of the PVC QRS complex and a selected number N preceding sensed R-waves. As long as a PVC coupling interval is not detected, the process continues to sense R-waves (block 104) and analyze RR intervals (block 105). The fiducial point identified at block 108 may correspond to the R-wave amplitude at the time of R-wave detection, a maximum peak R-wave amplitude (of a rectified or non-rectified signal), a minimum R-wave peak, a maximum slope, or other selected point along the QRS complex.

At block 110, at least one time interval is established beginning or ending at the fiducial point and extending a predetermined time from the fiducial point for each of the PVC and N preceding beats. The area under the R-wave during the established time interval is computed at block 112 for the PVC and the N preceding beats. The predetermined time may be in the range of approximately 25 ms to approximately 100 ms or more an may vary between embodiments. The time interval may generally be defined to maintain the time interval within an expected QRS complex width. Alternatively, the time interval may be defined to extend beyond an expected normal QRS complex width (i.e. beyond a beginning or end of a normal QRS width), to allow a wider QRS width associated with a PVC to be detected based on a change in area under the R-wave signal during the established time interval.

The computed area under the R-wave during the established time interval for the suspected PVC detected based on the detected PVC coupling interval is compared to the area(s) computed for the N preceding beats at block 114. A representative area for the N preceding beats may be determined for comparison to the area computed for the suspected PVC. For example an average, median, nth maximum area or other statistical measure may be determined for the N preceding beats. A difference or ratio of the suspected PVC area may then be computed and compared to a predefined PVC detection threshold. Alternatively, a difference or ratio of the suspected PVC area and each of the N preceding beats may be computed and the computed differences or ratios combined in a summation, average, or other representative number are compared to a PVC detection threshold. It is understood that many specific implementations may be conceived for detecting a clinically significant difference between an area computed for a suspected PVC and an area computed for one or more preceding beats.

If the PVC area is not different (negative result at decision block 114), the suspected PVC is rejected at block 116. In other words the suspected PVC based on a detected PVC coupling interval is rejected as not being a PVC. The PVC coupling interval detected at block 106 may be associated with a PAC, oversensing of a T-wave or other non-cardiac related signal noise. If the PVC detection is rejected at block 116, the process returns to block 104 to continue sensing R-waves and analyzing RR intervals for detecting a PVC coupling interval. HRT metrics are not computed.

If the PVC detection threshold criteria applied to the computed areas is satisfied at decision block 114, a PVC detection is confirmed at block 118. PVC detection triggers an analysis of RR intervals preceding and subsequent to the detected PVC and computation of HRT metrics at block 120. It is noted that HRT metrics such as Turbulence Onset and Turbulence Slope are usually computed using RR intervals measured in response to multiple PVCs, not just one PVC detection. If a HRT metric reaches an alert threshold at block 122, an alert is generated at block 124 to notify the patient and/or clinician of the detected condition and allow the clinician to assess the patient\'s condition and take any appropriate intervention. If an alert threshold is not reached, patient monitoring continues by returning to block 104.

It is recognized that in addition to or alternatively to generating an alert at block 124 the IMD may be configured to provide other responses to the HRT analysis. An IMD capable of delivering a cardiac therapy may be triggered to adjust the therapy based on the HRT metric. Furthermore, whenever HRT metrics are computed at block 120, it is understood that if the metrics are being computed by a processor incorporated in the IMD, the HRT metrics are stored for transmission to an external device as described in conjunction with FIG. 1. The digitized cardiac signal or data associated with the PVC detection, preceding beats, and/or subsequent beats may be stored along with HRT metrics for review by a clinician. In an another embodiment, confirmed detection of the PVC at block 118 causes storage of a cardiac signal strip including preceding and subsequent beats needed for HRT analysis to be performed by an external device after transmission of the cardiac signal strip to the external device.

FIG. 4 is a flow chart 200 of a method for monitoring HRT according to an alternative embodiment. At block 202, cardiac signal sensing is initiated. R-waves are sensed at block 204 according to an R-wave detection method implemented in the IMD. At block 206, a reference RR interval is computed. The reference RR interval is computed to provide a baseline RR interval used in identifying an unexpectedly short RR interval associated with a possible PVC coupling interval. A reference RR interval may be computed as a running average or a median of a most recent number of RR intervals. For example, in one embodiment, the reference RR interval is computed as the median of the most recent 11 RR intervals.

At block 208, a current RR interval is compared to a prematurity threshold for determining whether a PVC coupling interval is detected. The prematurity threshold is defined as a percentage of the reference RR interval. In one embodiment, a prematurity of 80%, i.e. an RR interval that is less than 80% of the reference RR interval, is detected as potential PVC coupling interval.

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Application #
US 20120277611 A1
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International Class

Premature Atrial Contraction
Premature Contraction
Premature Ventricular Contraction

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