an exemplary embodiment of the device is illustrated with reference to the accompanying drawings as described below . aspects of the device may be applied to implantable devices such as the paradym family ( especially paradym rf sonr crt - d ) produced and marketed by sorin crm , clamart , france . these are programmable microprocessor devices including circuitry to receive , format and process electrical signals collected by implanted electrodes . these devices also deliver stimulation pulses to electrodes . it is possible , using telemetry software that is stored in memory and is executed , to implement some of the features of the device that are described below ( parameter optimization and monitoring of the patient &# 39 ; s status ). the adaptation of these devices for the implementation of the functions of some of the embodiments of the device is within the skill in the art and is not described in detail . the technique used in some embodiments of the device is based on the analysis of the endocardial acceleration ( hereinafter “ ea ”). ea is a parameter that reflects very precisely , and in real time , phenomena contributing to the mechanical operation of the myocardium . ea may be measured by an accelerometer coupled to the heart muscle . this technique is described , for example , in ep 0515319 a1 ( sorin biomedica cardio spa ). this document discloses the method to collect an ea signal through an endocardial lead with a stimulation distal electrode implanted in the atrium or in the ventricle . a microaccelerometer is included for measuring endocardial acceleration . such a sensor as a the one described in ep 0515319 a1 or another microaccelerometer may be arranged on an endocardial lead terminating at the apex of the ventricle . an acceleration sensor is provided at that location . the sensor may also be a lead provided with an acceleration sensor at its one end disposed against the wall of the right atrium . note that although the present description refers mainly to the analysis of an ea signal delivered by a sensor on an endocardial lead , some embodiments of the device may perform an analysis using an ea signal delivered by other types of implantable sensors . for example , these implantable sensors may include a motion sensor of a wall of the myocardium , an epicardial sensor , or an accelerometer in the housing of an implant . some embodiments of the device are also applicable of performing the analysis using an external ea signal obtained non - invasively . for example , a sensor may be attached to the patient &# 39 ; s chest at the sternum . fig1 illustrates the various signals characterizing the activity of the heart during a cardiac cycle . the profiles of intracardiac pressures p a , p vg and p og are shown . the p a profile shows the changes in the aortic pressure . the p vg profile shows changes in the left ventricular pressure . the p og profile shows changes in the left atrium pressure . these changes go through phases including : a contraction of the left atrium , closure of the mitral valve ( mc ), opening of the aortic valve ( ao ), closure of the aortic valve ( ac ), and opening of the mitral valve ( mo ). an ecg surface electrocardiogram plot is also shown corresponding to the same period of time . the ecg surface electrocardiogram plot includes the p wave corresponding to the depolarization of the atria , the qrs complex corresponding to the depolarization of the ventricles , and the t wave of ventricular repolarization . also shown are the changes in the collected ea endocardial acceleration signal . the ea endocarial acceleration signal forms two main components ea 1 and ea 2 during a given cardiac cycle . the two main components correspond to the two major heart sounds ( s 1 and s 2 sounds of the phonocardiogram ) that can be recognized in each cardiac cycle . in fig2 , changes in the ea signal during a cardiac cycle are more specifically illustrated . the ea 1 component begins after the qrs complex and is caused by a combination of the closing of the atrioventricular valves ( the mitral and the tricuspid valves ), the opening of semilunar valves ( the aortic and the pulmonary valves ), and the contraction of the left ventricle . the amplitude variations of this ea 1 component are closely related to changes in the pressure in the ventricle . the maximum peak - to - peak pea 1 is specifically correlated to the positive maximum of the pressure variation dp / dt in the left ventricle . the ea 2 component occurs during the isovolumetric ventricular relaxation phase . it supports the end of the ventricular systole and is mainly produced by the closure of the aortic and pulmonary valves . for the implementation of some embodiments of the device , the device may extract from the ea signal , specifically from the ea 1 component , a non - temporal parameter characteristic of the magnitude of this ea 1 component . this parameter can particularly be the pea 1 amplitude of the first peak of endocardial acceleration . pea 1 amplitude is the maximum peak - to - peak value between the positive and negative extremes of the ea 1 component of the acceleration signal . this pea 1 parameter is used in the following description as a significant non - temporal parameter . in some embodiments , other parameters representative of the magnitude of ea 1 component may be used . in particular , it is possible to use as a significant non - temporal parameter the energy of the ea signal contained in all or part of the ea 1 component . this energy is given by the root mean square ( rms ) value of a series of samples considered for a predetermined time window of the ea 1 component . this energy parameter is illustrated in fig2 by the envelope e of the signal . the analysis of the ea signal is preferably determined with averaging over several cycles , typically three to five cycles , using a technique such as that disclosed in ep 2092885 a1 ( ela medical ). this technique is useful for eliminating the cycle to cycle variations by a timing shift of the successive components before averaging . essentially , this technique is to pre - process the continuously collected ea signal . the ea signal is cut into sub - signals each corresponding to the duration of a cardiac cycle and identified by cycle start markers ( time origin ) for performing this cutting cycle . the cycle start temporal markers can be provided by the implanted device . the device also , according to the operating mode , stores the moments of v stimulation or the moments of r wave detection . each of these sub - signals is segmented so as to individualize the ea 1 component in a given temporal window . for the current ea 1 component thus isolated on a cycle , an inter - correlation peak relative to the ea 1 components of the other collected cycles is determined . a corresponding temporal shift is computed . the calculated temporal shift is applied to the current ea 1 component so as to align it with respect to the others . the analysis processing of the ea signal can then be executed on successive ea 1 components , eliminating cycle to cycle variability bias through this pre - processing . in some embodiments of the device , atrioventricular delay ( avd ) is modulated . the changes to the non - temporal characteristic parameter of the ea signal , in this example the pea 1 amplitude , are produced by this modulation of the avd . the variation of the pea 1 amplitude with the avd is normally associated with a sigmoid shape characteristic s , shown in fig3 a . in this figure and the following ones , the thin line circles indicate the different readings in successive cardiac cycles for the same applied avd value . the thick line circles correspond to the value of these different measures averaged for a same avd . the pea 1 amplitude decreases when the avd increases , and the sigmoid characteristic can be modeled in a simplified form ms with two plateaus p 1 , p 2 respectively corresponding to the short avd and to the long avd , these plateaus being separated by a central transition portion with a negative slope . some embodiments of the device are based on the idea that changes in the ea 1 characteristic versus the avd , such as changes in the pea 1 amplitude , are due , among other factors , to the different contribution of the atrium for the filling of the ventricle . a short avd maximizes the filling of the ventricle , leading to a very marked ea peak signal . a long avd reduces the amplitude and the energy of the ea 1 component . when the atrial mechanical activity is absent , typically after an episode of atrial fibrillation ( af ), the atrium may fail to contribute in any way to fill the ventricle . a variation of the avd produces no significant change in the ea 1 component . this situation is illustrated in fig3 b . the level of the pea 1 amplitude is essentially the same regardless of the applied , short or long , avd . in the case of a present but deficient atrial contraction ( atrial atony ), the pea 1 amplitude varies slightly with the avd ( shown fig3 c status ). the variation of the pea 1 amplitude with respect to avd is much less than in the case of a full atrial contraction ( fig3 a ). different techniques can be used to analyze the pea 1 / avd characteristic and discriminate between normal atrial activity and absent or deficient atrial activity . some embodiments may include a first technique , alone or in conjunction with other techniques . the first technique is illustrated with reference to fig4 a and 4 b . a number n of short test avd values are applied . separately , a number n of long test avd values are applied . the pea 1 amplitude is measured for each of these applied avd values . the test avd are selected from a bounded range of values . for example , some embodiments may use minimum values dav min = 32 ms for the shortest value and maximum dav max = pr - 50 ms for the longest avd . pr is the interval between the atrial and ventricular depolarizations and 50 ms corresponds to a predetermined safety margin in this example . in some embodiments , the number n , which defines the number of long and short avd to test , can be for example between 3 and 20 . the different tested avd are performed with a fixed pitch , for example 15 ms between two consecutive avd . for each tested avd , the pea 1 amplitude is measured and averaged over a number of cycles . for example , some embodiments may take measurements for six or more cardiac cycles . to determine the level of atrial activity , a difference is calculated between the average values of pea 1 measured for the n short avd , and the average values of pea 1 measured for the n long avd . if this absolute difference is less than a programmable threshold , there is an absence of normal mechanical atrial activity ( as in fig4 b ). in other words , there is absent or deficient atrial activity . if the absolute difference is greater than the programmable threshold , there is normal mechanical atrial activity . in some embodiments , the value of the calculated difference is preferably stored in memory . the stored values may constitute a history that may be used to monitor the long - term atrial mechanical activity . this is explained below with reference to fig7 and 8 . some embodiments may use a second technique , alone or in conjunction with other techniques , to analyze the pea 1 / avd characteristic and discriminate between normal atrial activity and absent or deficient atrial activity . this second technique is illustrated with reference to fig5 a and 5 b . the avd is regularly modulated with a scan between the dav min and dav max values . this can be done to obtain a number n of successive measurements of equidistant avd values . in some embodiments , n may typically be between 4 and 20 . for each tested avd , the pea 1 amplitude is measured and averaged over several cycles . in some embodiments , the pea 1 amplitude is measured for typically at least six cardiac cycles . the standard deviation sd pea1 is then calculated from all the averaged values of pea 1 . if the standard deviation is below a given threshold , then there is no normal mechanical atrial activity ( as in fig5 b ). there is absent or deficient atrial activity . if the standard deviation sd pea1 is greater than the given threshold , there is normal mechanical atrial activity . in some embodiments , the value of the calculated standard deviation may be stored in memory to monitor the long - term atrial mechanical activity of the patient . some embodiments may use a third technique , alone or in conjunction with other techniques , to analyze the pea 1 / avd characteristic and discriminate between normal atrial activity and absent or deficient atrial activity . the third technique is illustrated with reference to fig6 a and 6 b . the third technique is a variant of the second technique described above . this technique operates by creating a ms model of the pea 1 characteristic obtained after scanning the range of possible avd between dav min and dav max . as noted above , the modeled characteristic has two plateaus , p 1 for the lowest avd values and p 2 for the highest avd values . this is typical of a sigmoid shape . the atrial activity is estimated by calculating the absolute difference δp between the two plateaus p 1 and p 2 of the sigmoid approximation . if this difference is less than a given threshold , then there is an absence of normal atrial mechanical activity ( as in fig6 b ). in other words , there is absent or deficient atrial activity . if the difference is greater than the given threshold , there is normal mechanical atrial activity . fig7 and 8 and the flow chart of fig9 illustrate the possibility of using the atrial mechanical activity test techniques described above to monitor the patient &# 39 ; s long - term clinical status . in some embodiments , a test can be triggered periodically . for example , the test may occur weekly or more frequently to determine the status of the atrial activity . this test may be run for both spontaneous and stimulated atrial depolarization . in the case of stimulated atrial activity , the test may occur in conditions in which atrial capture is likely . to facilitate atrial capture , stimulation amplitude is adjusted at a high level during the test . in some embodiments , stimulation amplitude is previously checked for the presence of an actual atrial capture . for testing , the avd is modulated in order to evaluate a degree of variation of the ea 1 characteristic versus the avd according to one of the techniques described above . for example , the difference δ pea1 calculated between the pea 1 amplitude collected for the short avd and those collected for the long avd may be stored . this corresponds with the first technique for discriminating between normal atrial activity and absent or deficient atrial activity described above . some embodiments may use a different combination of one or more of the techniques described . if this δ pea1 value is greater than a given threshold s , atrial activity is present and normal . if the δ pea1 value is less than a given threshold , atrial activity is absent or deficient ( atrial atony ). in some embodiments , the device compares the respective values of the δ pea1 stored value in the presence of a spontaneous atrial event and in the presence of an atrial paced event . the device may generate an alert in the case of a discrepancy between the compared values . fig7 shows an example in which the δ pea1 value is evaluated at weekly intervals ( w 1 , w 2 , w 3 , . . . ). the δ pea1 value corresponding to each week is stored . these stored values may be used to form a long - term history of global atrial mechanical activity of the patient . fig7 illustrates a normal atrial mechanical activity history . s is a threshold value against which the δ pea1 value for each week is compared . each week shows normal atrial mechanical activity as the δ pea1 value is above the threshold value s . in a case where the δ pea1 value is below the threshold value s , atrial activity is absent or deficient ( atrial atony ). fig8 shows an example of an episode of atrial fibrillation af leaving deficient mechanical atrial activity for several weeks . the end of this episode ( between periods w 4 and w 8 ) can be detected by a return of sinus rhythm . the test for mechanical atrial activity is then performed using one of or a combination of the techniques described above . in the example illustrated by fig8 , the test indicates that during the periods w 9 to w 12 there was deficient atrial activity . the degree of pea 1 / avd variation is less than the threshold s . the patient has regained normal atrial activity when δ pea1 rises above this threshold . for example , the threshold may be s ′= 80 % of the δ value recorded by the δ pea1 variation parameter prior to the af episode . fig9 illustrates a schematic of the successive steps of an algorithm to discriminate between the various possible states of atrial mechanical activity after an episode of atrial fibrillation . for a patient with atrial fibrillation ( block 10 ), the device waits for the end of this episode ( block 12 ). the end of the episode is detected by the return to a normal and stable sinus rhythm . the return to a normal and stable sinus rhythm may be determined by the analysis of the electrical activity of the depolarization signals detected at the atrium . the device may then perform a test to assess the degree of variation of the pea 1 amplitude versus the avd ( block 14 ). the resulting test data is collected and stored . if test results were obtained and stored before the af episode ( block 16 ), then the algorithm compares the new data to the old data ( block 20 ). if the data values are comparable ( for example , if the δ pea1 variation parameter is at least 80 % of the value it had before the episode of af ), the atrial activity returned to normal . if the test data values are not comparable to the values stored before the af episode , the atrial activity is insufficient or absent . if there is no data prior to the af episode , the algorithm simply compares the test data to a threshold ( block 18 ). if the test data values are greater than the threshold , there is normal mechanical atrial activity . if the test data values are less than the threshold , there is reduced or absent atrial activity . in some embodiments , the algorithm may use a combination of one or more of the techniques for discriminating between normal and absent or deficient atrial activity described above . in some embodiments , the analysis of the atrial mechanical activity may also be used to selectively enable or disable various algorithms . these algorithms may include atrial overdriving , automatic optimization of the avd , etc ., depending on the test result . for example , if atrial fibrillation is detected , using the analysis previously described herein , then the avd algorithm may be disabled . continued use of the avd algorithm during atrial fibrillation may have deleterious effects . these effects may be prevented by the disabling of the avd algorithm during episodes of atrial fibrillation detected by the device . in some embodiments , an atrial overdriving algorithm , designed to overdrive the atrium to prevent atrial fibrillation through a higher pacing rhythm , may be activated or enabled by the device . the device may enable this algorithm upon the detection of atrial fibrillation using the analysis previously described herein . in some embodiments , these algorithms may be disabled , enable , and / or modified depending on the detection of normal or deficient or absent atrial mechanical activity according to the analysis described herein . furthermore , in some embodiments the device and / or analysis may automatically optimize the avd using the techniques described herein ( e . g . upon detection of absent or deficient atrial mechanical activity ). in some embodiments , the device may produce an alert ( e . g . signal , notification , data point , sound , visible signal , etc .) in certain cases . for example , the device may produce an alert when an algorithm is enabled , disabled , and / or modified . continuing the example , the device may produce an alert upon the detection , using the analysis described herein , of absent or deficient atrial mechanical activity . the device may adjust a variable of an avd algorithm . for example , the device may adjust one or more of the length of time of the avd , the length of the time intervals between atrial sensing , the length of the time intervals between pacing , the number of cycles for which an extended or reduced avd is applies , the value of and avd extension , the value of an avd reduction , the value of the avd corresponding to different heart rates , the magnitude of the ventricular pacing stimulus , the rate adjustment value for exercise and other activities , the base pacing rate , etc . the avd may be adjusted taking into account the optimal or desired interatrial conduction time , left - atrial electromechanical action , left - ventricular latency period , etc . the device may also adjust a variable of an atrial overdriving algorithm . for example the device may adjust one or more of rate of pacing , the frequency of stimulation , the magnitude of stimulation , the atrial rate , the rate adjustment value for exercise and other activities , the base pacing rate in one embodiment of the device , the device is not a pacing device . the device may be a monitor , server computer , personal computer , mobile device , clinic computer , or other device configured to apply the analysis techniques described . the device may also be configured to discriminate between normal and absent or deficient atrial mechanical activity and / or to determine if a patient is experiencing af using the analysis techniques described above . in some embodiments , the device may be incorporated into another apparatus such as a patient bed , heart rate monitor , etc . having received data such as the ea signal for a patient over time or a set of non - temporal ea ventricular parameter values over time ( e . g . pea 1 amplitude or energy of the ea 1 component of the ea signal ), the device may perform the analysis techniques set forth above . the results of the analysis may be a determination of normal atrial mechanical activity or absent or deficient atrial mechanical activity . this determination may be over a period of time and / or live as data is received . for example , the device may display a graph such as the one illustrated in fig7 or fig8 . the device may display a graph of the change of the non - temporal ea ventricular parameter values for different avd values over time . the device may also label periods of normal atrial mechanical activity . the device may label periods of absent or deficient atrial mechanical activity . the device may also provide a current determination of whether a patient is experiencing af . this determination may be based on the most recently available data . this determination may be presented to a user of the device through an alert . for example , the alert may be a visual warning ( e . g . graphics or words which designate that the patient is experiencing af ), an auditory warning ( e . g . an alarm when the patient is experiencing af ), or a warning otherwise delivered . in the case that the patient is not experiencing af , a status indicator may be displayed to the user of the device . the analysis , analysis results , and / or warnings generated by the device may be displayed and / or delivered to a user . for example , the analysis and / or alerts may be displayed on a local monitor , remote monitor , emailed to a user , sent to a mobile device , pushed to an application on a mobile device , compiled into a report and printed , sent as a text message , sent as a page , broadcast over a public address system ( e . g . in the case of an af alert ), displayed on a computer and / or monitor at a nurses station , stored locally , stored in a cloud based architecture , transferred to another computing device etc . in some embodiments , the device may compare analyzed data to a data in a stored index for a particular patient . this comparison and / or the resulting analysis may displayed in a manner described above .
a device includes a lead configured to for use in applying an atrioventricular delay , an acceleration sensor adapted to output an endocardial acceleration signal , and circuitry configured to receive and process said endocardial acceleration signal to provide ventricular pacing by varying , in a controlled manner , the avd in a range having a plurality of avd values . the circuitry derives from said endocardial acceleration signal a value of a parameter representative of an component of the endocardial acceleration signal corresponding to the first endocardial acceleration peak associated with an isovolumetric ventricular contraction , and evaluates a degree of variation of said parameter values as a function of said plurality of avd values to detect atrial and ventricular events .