Source: http://www.google.com/patents/US20020143264?dq=6,243,373
Timestamp: 2016-07-25 20:44:18
Document Index: 664358978

Matched Legal Cases: ['art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100', 'art 100']

Patent US20020143264 - Identifying heart failure patients suitable for resynchronization therapy ... - Google PatentsSearch Images Maps Play YouTube News Gmail Drive More »Sign inPatentsMethods and systems are disclosed for determining whether a patient is a responder to cardiac resynchronization therapy. The beginning and ending of the intrinsic ventricular depolarization are determined through signals measured from one or more electrodes implanted in the patient's heart. An interval...http://www.google.com/patents/US20020143264?utm_source=gb-gplus-sharePatent US20020143264 - Identifying heart failure patients suitable for resynchronization therapy using QRS complex width from an intracardiac electrogramAdvanced Patent SearchPublication numberUS20020143264 A1Publication typeApplicationApplication numberUS 10/008,397Publication dateOct 3, 2002Filing dateDec 6, 2001Priority dateMar 30, 2001Also published asUS6993389, US7424324, US8280512, US8554321, US8849399, US20050216065, US20080306568, US20130013018, US20140031887Publication number008397, 10008397, US 2002/0143264 A1, US 2002/143264 A1, US 20020143264 A1, US 20020143264A1, US 2002143264 A1, US 2002143264A1, US-A1-20020143264, US-A1-2002143264, US2002/0143264A1, US2002/143264A1, US20020143264 A1, US20020143264A1, US2002143264 A1, US2002143264A1InventorsJiang Ding, Yinghong Yu, Julio SpinelliOriginal AssigneeCardiac Pacemakers, Inc.Export CitationBiBTeX, EndNote, RefManPatent Citations (7), Referenced by (102), Classifications (17), Legal Events (4) External Links: USPTO, USPTO Assignment, EspacenetIdentifying heart failure patients suitable for resynchronization therapy using QRS complex width from an intracardiac electrogram
DESCRIPTION OF THE DRAWINGS [0016] [0016]FIG. 1 is a diagram showing the various chambers of the heart. [0017] [0017]FIG. 2 is a diagram showing the various chambers and the electrical conduction system of the heart. [0018] [0018]FIG. 3 is a graph showing ventricular depolarization as a function of time. [0019] FIGS. 4-6 are diagrams illustrating a heart and the electrical conduction system advancing through a normal cardiac cycle. [0020] [0020]FIG. 7 is a graph illustrating mean percentage change in left ventricular pressure (LV+dp/dt) resulting from application of CRT plotted against the duration of intrinsic ventricular depolarization for responders and non-responders. [0021] [0021]FIG. 8 is a graph illustrating the accuracy, sensitivity, and specificity of the separation between responders and non-responders for various thresholds of ventricular depolarization duration used to make the distinction. [0022] [0022]FIG. 9 illustrates one possible embodiment of a system that can be used to detect whether a patient is a responder to CRT. [0023] [0023]FIG. 10 is an operational flow summarizing the logical operations employed by an exemplary system for detecting whether a patient is a responder to CRT.
DETAILED DESCRIPTION [0024] Various embodiments of the present invention will be described in detail with reference to the drawings, wherein like reference numerals represent like parts and assemblies throughout the several views. Reference to various embodiments does not limit the scope of the present invention, which is limited only by the scope of the claims attached hereto. [0025] The following discussion is intended to provide a brief, general description of a suitable method for predicting whether a patient will positively respond to cardiac resynchronization therapy (“CRT”). As will be described in greater detail below, the method of the present disclosure predicts a patient's response to CRT by measuring and comparing an intrinsic ventricular depolarization period against a threshold. As will become apparent from the discussion below in connection with the various drawings, the ventricular depolarization period may be measured by finding a beginning and ending of the depolarization through processing of an intracardiac signal to find a beginning value Q* and an ending value S*. However, those of ordinary skill in the art will readily appreciate that the method of the present disclosure can be implemented using any suitable beginning and ending value, which may or may not be found by employing various methods for measuring Q* and S*. [0026] In a preferred embodiment, the method of the present disclosure predicts whether a patient will respond to CRT by evaluating the period of depolarization of the right or left ventricles 108, 112 (FIG. 1). The period of depolarization of the ventricles 108, 112 can be evaluated using an intracardiac electrogram. An intracardiac electrogram is generally a graphical depiction of the electrical depolarization or excitement of the heart 100 (FIG. 1) that is measured by one or more electrodes placed on or within the heart 100, such as within the right or left ventricles. [0027] An exemplary electrogram for an intrinsic systolic cycle is shown in FIG. 3. Each portion of the electrogram is typically given an alphabetic designation corresponding to a predetermined period of electrical depolarization or excitement. For example, the portion of the electrogram that represents atrial depolarization is commonly referred to as the P-wave (not shown). Similarly, the portion of the electrogram that represents ventricular depolarization is commonly referred to as the QRS complex comprising a Q-wave, an R-wave, and an S-wave. Moreover, the portion of the electrogram that represents ventricular recovery or repolarization is commonly referred to as the T-wave (not shown). [0028] As shown in FIG. 3, the QRS complex has a beginning and an ending. To determine the beginning and ending, the intracardiac electrogram may be analyzed, as discussed below, to find various representative values. The representative beginning value Q* and ending value S* are shown in FIG. 3. Other values representative of the beginning and ending of the QRS complex may be used in place of the Q* and S* values that are defined by the calculations discussed below. [0029] Each period of electrical depolarization or excitement represented on the electrogram corresponds to a period of muscular activation within the heart 100 (FIG. 1). FIGS. 4-6 are schematic illustrations depicting the various periods of muscular activation within the heart 100. As shown in FIGS. 4-6, the electrogram data can be monitored using any suitable electrocardiographic device 150, such as an implantable heart stimulation device (i.e. CRT device), that is connected to leads located on or within the heart 100. [0030] [0030]FIG. 4 is a schematic illustration showing the period of atrial activation in response to electrical impulses initiated at the sinoatrial node 120 (corresponding to the P-wave portion as discussed above). After electrical impulses spread from the sinoatrial node 120, the muscle tissues of the right and left atriums 106, 110 contract to pump blood into the right and left ventricles 108, 112, respectively. [0031] [0031]FIG. 5 is a schematic illustration showing the period of a ventricular depolarization in response to electrical impulses initiated at the atrioventricular node 122 that spread through the ventricles 108, 112 (corresponding to the QRS portion as discussed above). After electrical impulses spread from the atrioventricular node 122, the muscle tissues of the right and left ventricles 108, 112 contract to pump blood to the lungs and throughout the body, respectively. [0032] [0032]FIG. 6 is a schematic illustration showing ventricular recovery or repolarization (corresponding to the T-wave portion as discussed above). During ventricular repolarization, the membrane potential of the muscle cells reverse polarity and return to their resting state, thereby, causing the ventricles to relax. [0033] An electrogram of a patient's heart can be used to assess cardiac performance by validating the existence of cardiac abnormalities, such as, arrhythmias evinced by an abnormally fast heart rate (e.g., tachycardia), an abnormally slow heart rate (e.g., bradycardia), or a normal rate but the depolarization is abnormally propagated (e.g., ectopic, or conduction system defect). The existence of an arrhythmia typically indicates that the heart's rhythm initiation and/or conduction system is functioning abnormally. CRT can be used, among other applications, to treat abnormal electrical conduction. In particular, CRT can be used to deliver electrical stimulation to portions of the heart 100 (FIG. 1) to resynchronize the heart's activation, thereby, improving the efficiency of atrial and ventricular contractions necessary to circulate blood throughout the body. The amount of benefit derived from CRT, however, typically varies depending upon the severity of the abnormality of the heart's conduction system. Therefore, prior to treating a patient using CRT, it is preferable to evaluate whether the heart's 100 (FIG. 1) conduction system is normal or abnormal. [0034] The heart's ventricular conduction system can be assessed through analysis of the duration of ventricular depolarization. Identification of patients who may have a positive response to CRT can be performed using the duration of ventricular depolarization (e.g., the width of the QRS complex as shown in FIG. 3) measured from an intracardiac electrogram. For example, if the duration of ventricular depolarization is greater than a given threshold, then the patient may be considered a responder to CRT, and the CRT device for that patient may be configured appropriately. Patients are referred to as responders because they have an abnormal conduction system that can benefit from CRT. [0035] Once the patient has been deemed a responder or non-responder, the CRT device can be configured to stimulate the heart to produce an atrioventricular delay of a duration appropriate for the patient type as is discussed below. For responders, the atrioventricular delay is generally set to about one-half of the intrinsic, or naturally occurring atrioventricular delay. For non-responders, the atrioventricular delay is set to approximately the intrinsic atrioventricular delay, such as the intrinsic atrioventricular delay minus a relatively small delay factor of about 30 milliseconds. One with ordinary skill in the art will recognize that other atrioventricular delay settings for responders and non-responders are possible as well. The atrioventricular delay is generally considered to be the length of time between an atrial sensed (or stimulated) event and the delivery of a ventricular output pulse. [0036] [0036]FIG. 7 shows a graph of the mean percent change in peak left ventricle pressure “LV dp/dt” after application of CRT over three atrioventricular delays for a group consisting of both responders and non-responders. Responders may be defined as those who receive an increase in peak left ventricle pressure when CRT is applied. From the graph, one can see that a relationship exists between the intrinsic Q*S* depolarization interval and the increase in peak left ventricle pressure due to CRT. For those having a relatively long intrinsic ventricular depolarization, CRT caused a relatively large increase in peak left ventricle pressure. For those having a relatively short intrinsic ventricular depolarization, CRT caused a relatively small increase or in some instances a decrease in peak left ventricle pressure. [0037] A linear regression of the test cases shows that the correlation of percent change in peak left ventricle pressure to Q*S* is defined by the equation y=0.3462x −51.807, with a coefficient of determination R2=0.3974. The vertical line of FIG. 7 indicates that an appropriate Q*S* threshold for distinguishing responders from non-responders is approximately 175 milliseconds for humans. The determination of 175 milliseconds as an appropriate threshold is further supported by the plot in FIG. 8. [0038] [0038]FIG. 8 shows the values for the accuracy which represents the probability of correct classification of either a responder or non-responder, sensitivity which represents the probability of correct classification of patients as responders, and specificity which is the probability of correct classification of patients as non-responders plotted against Q*S* thresholds for humans. From this plot, it can be seen that the optimal threshold is about 175 milliseconds for humans because at this point the accuracy and sensitivity are above 0.95 and the specificity is above 0.88. [0039] One possible embodiment of a CRT system 300 that can be used to implement the methods for determining whether a patient is a responder is illustrated in FIG. 9. As shown in FIG. 9, the CRT system 300 generally comprises a programming device 301 that can be used to regulate stimulation pulses that are delivered to the heart 100. In one possible embodiment, the heart 100 is connected to various leads 320 having electrodes (not shown) and terminal pins (not shown) that can connect the heart 100 to the CRT system 300. The various leads 320 connecting the heart 100 to the CRT system 300 will be described in greater detail below. [0040] The programmer 301 can regulate the stimulation pulses delivered to the heart 100 using, for example, a telemetry module 302. In one possible embodiment, the telemetry module 302 is unidirectional (e.g., capable of allowing the programmer 301 to receive data). However, in an alternative embodiment, the telemetry module 302 is bi-directional (e.g., capable of allowing the programmer 301 to receive and/or send data). The command input module 304 is configured to interpret the data received from the programmer 301 such that the stimulation pulses can be accurately distributed according to predetermined criteria, such as, the specific requirements of the patient being treated. [0041] A controller 306 can be used to control the specific instructions regarding the stimulation pulses delivered to the heart 100. In one possible embodiment, the controller 306 can be controlled manually. In an alternative embodiment, however, the controller 306 can be controlled automatically using, for example, feedback received from an intrinsic signal analyzer 338. Moreover, one having ordinary skill in the art will readily appreciate that the controller 306 and the programmer 301 can be combined into a single unit. The instructions from the controller 306 are received by an electrode switching and output circuitry module 308 that delivers the stimulation pulses to the appropriate lead 320 within the heart 100. [0042] As discussed above, the heart 100 is connected to the CRT system 300 using various leads 320. The various leads 320 are preferably configured to carry the CRT stimuli from the CRT device to the heart 100. Moreover, the various leads 320 can likewise operate in a demand mode, thereby, relaying intrinsic cardiac signals from the heart's 100 electrical conduction system back to one or more sense amplifiers 310, 312, 314, 316. In one possible embodiment, the various leads 320 comprise separate and distinct leads connecting the CRT system 300 to different portions of the heart 100. In particular, the various leads 320 can comprise a lead 322 connected to the right-side portion or pump 102 (FIG. 1) of the heart 100, including, for example, a right atrium lead 324 configured to operate with a right atrium amplifier 310 and a right ventricle lead 326 configured to operate with a right ventricle amplifier 312. Similarly, the various leads 320 can comprise a lead 327 connected to the left-side portion or pump 104 (FIG. 1) of the heart 100, including, for example, a first left ventricle lead 328 configured to operate with a first left ventricle amplifier 314 and a second left ventricle lead 330 configured to operate with a second left ventricle amplifier 316. [0043] As discussed above, the various leads 320 connected to the heart 100 can relay intrinsic cardiac signals from the heart's 100 electrical conduction system back to the one or more sense amplifiers 310, 312, 314, 316. The intrinsic cardiac signals amplified by the sense amplifiers 310, 312, 314, 316 can then be processed by an intrinsic signal analyzer 338 incorporated in whole or in part by an implantable heart stimulation device (i.e., CRT device) or a device programmer. The intrinsic signal analyzer 338 generally can comprise a detection module 340 that is configured to analyze the intracardiac electrogram information to detect the beginning and ending of ventricular depolarization, such as the Q* and S* values discussed above with reference to FIG. 3. [0044] Calculating Q* and S* from the intracardiac electrogram signal may be done in various ways. See for example, the calculation of Q* from U.S. Pat. No. 6,144,880, which is commonly assigned to Cardiac Pacemakers, Inc. and is incorporated herein by reference. In one embodiment, calculating Q* and S* may proceed as follows. For Q*, a waveform V(n) including the QRS complex must be acquired and analyzed, such as by the detection module 340 of the CRT device or CRT device programmer. The acquisition involves digitizing the waveform V(n) including the activity beginning at the time of an atrial reference marker indicating the end of atrial activity and extending beyond the QRS complex received by the electrode in the left or right ventricle and storing it in memory of the CRT device or CRT device programmer. Then, Q* is found by the following process. [0045] First, the detection module 340 smooths the waveform V(n). This may be done by smoothing the waveform V(n) seven times using a 5 point rectangular moving window (for a sampling frequency of 500 Hz) whereby the 5 samples for each window are averaged and the average is assigned to the middle sample of the five. A derivative dV(n)/dt of the smoothed waveform is taken, and the absolute value of the derivative dV(n)/dt is normalized to range from 0 to 1. [0046] The time samples n from the atrial reference marker time Tp to the time TR of the peak of the R wave of the QRS complex are analyzed. This analysis involves calculating the mean and standard deviation of both the smoothed waveform V(n) and the normalized absolute value of its derivative dV(n)/dt for each time sample within a 50 ms moving window. The baseline window with the minimum mean (i.e., baseline mean) plus a baseline standard deviation for |dv(n)/dt| is found and its values are used in the following steps. [0047] For each sample n between Tp and TR if the baseline mean is less than |dV(n)/dt|, but more than or equal to |dV(n)/dt|, then the number of data points N in another 50 ms window is found. N is the accumulation of each data point /nw where |dv(nw)/dt| is greater than the baseline mean plus the baseline standard deviation. The window sample nw of this other window ranges from n to n plus the total number of data points in the window. [0048] If N divided by the total number of data points in the window is greater than 0.96 and Tq=0, then set Tq equal to n0−1, where Tq is the current result of sample time for Q* and n0 is the time sample of the first data point that contributes to N. If the total number of data points in the window minus N is greater than or equal to 2, then Tq is reset to zero. After this is completed for all values of n between Tp and TR, then the final value of Tq is used as Q*. This process may be repeated to obtain a value of Q* for several beats, such as 16, and the median of these Q* values may be used in the computation of the ventricular depolarization interval. It may be desirable to include Q* values in the median determination for beats where the interval from R wave peak to R wave peak between beats has a variation within 10%. [0049] For S*, the same process may be repeated but the time samples n ranging from the time Tp+1 which occurs after sensing atrial activity in the next cycle until the time TR of the peak of the R wave of the QRS complex of the current cycle are analyzed rather than the samples occurring prior to the R wave peak. Once the process discussed above has been completed for all values starting at Tp+1 and continuing to TR (i.e., working backwards through the samples with respect to time), the final value of Tq is used as S*. As with Q*, this process for S* may be repeated to obtain a value of S* for several beats, such as 16, and the median of these S* values may be used in the computation of the ventricular depolarization interval. [0050] After analysis of the electrogram information to find the beginning and ending of ventricular depolarization such as Q* and S*, a processing module 342 may compute the duration of depolarization and compare it to a threshold value, such as 175 milliseconds, in accordance with the method described below with reference to FIG. 10 to validate the patient as a responder or non-responder. A configuration module 344 can be used to make adjustments to the CRT system 300 based upon whether the processing module 342 determines the patient to be a responder or non-responder. The adjustments may include setting the atrioventricular delay of the CRT device to about one-half of the intrinsic value for responders or to approximately the intrinsic value for non-responders. For embodiments where the device programmer includes all or part of the intrinsic signal analyzer 338, the device programmer may send an instruction through telemetry 302 to the implanted heart stimulation device to set the atrioventricular delay. [0051] The method of the present disclosure can be implemented using a CRT system as shown in FIG. 9 comprising various devices and/or programmers, including implantable or external CRT devices and/or programmers such as a CRT tachy or brady system. Accordingly, the method of the present disclosure can be implemented as logical operations controlling a suitable CRT device and/or programmer. The logical operations of the present disclosure can be implemented: (1) as a sequence of computer implemented steps running on the CRT device and/or programmer; and (2) as interconnected machine modules within the CRT device and/or programmer. [0052] The implementation is a matter of choice dependant on the performance requirements of the CRT device and/or programmer implementing the method of the present disclosure and the components selected by or utilized by the users of the method. Accordingly, the logical operations making up the embodiments of the method of the present disclosure described herein can be referred to variously as operations, steps, or modules. It will be recognized by one of ordinary skill in the art that the operations, steps, and modules may be implemented in software, in firmware, in special purpose digital logic, analog circuits, and any combination thereof without deviating from the spirit and scope of the present invention as recited within the claims attached hereto. [0053] [0053]FIG. 10 shows an exemplary embodiment 346 of the logical operations of the processing module 342. The process begins by the processing module 342 receiving the Q* and S* values from the signals measured by detection module 340 at receive operation 348. At interval operation 350, the processing module 342 computes the time interval between the Q* and S* values. At query operation 352, the processing module 342 compares the Q*S* interval to the threshold, such as 175 milliseconds. [0054] If the processing module 342 determines that Q*S* is greater than the threshold, then the processing module 342 selects an atrioventricular delay that is about one-half of the intrinsic atrioventricular delay at delay operation 354. If the processing module 342 determines that Q*S* is less than or equal to the threshold, then the processing module 342 selects an atrioventricular delay that is approximately equal to the intrinsic atrioventricular delay at delay operation 356. 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2009FPAYFee paymentYear of fee payment: 4Mar 13, 2013FPAYFee paymentYear of fee payment: 8RotateOriginal ImageGoogle Home - Sitemap - USPTO Bulk Downloads - Privacy Policy - Terms of Service - About Google Patents - Send FeedbackData provided by IFI CLAIMS Patent Services