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- Abstract
- 1. Introduction
- 2. Methods
- 3. Analysis of Heart Beat Interval Dynamics
- 4. Analysis of Postural Changes
- 5. Conclusion
- References

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Biosystems. Author manuscript; available in PMC 2009 July 1.

Published in final edited form as:

Published online 2008 April 26. doi: 10.1016/j.biosystems.2008.03.011

PMCID: PMC2561955

NIHMSID: NIHMS63417

The publisher's final edited version of this article is available at Biosystems

The development of statistical models that accurately describe the stochastic structure of biological signals is a fast growing area in quantitative research. In developing a novel statistical paradigm based on Bayes’ theorem applied to point processes, we are focusing our recent research on characterizing the physiological mechanisms involved in cardiovascular control. Results from a Tilt Table study point at our statistical framework as a valid model for the heart beat, as generated from complex mechanisms underlying cardiovascular control. The point process analysis provides new quantitative indices that could have important implications for research studies of cardiovascular and autonomic regulation and for monitoring of heart rate and heart rate variability measures in clinical settings.

Heart rate (HR) and heart rate variability (HRV) are important dynamic measures of the state of the cardiovascular system and the autonomic nervous system (Stauss, 2003; Task Force, 1996). Heart rate is traditionally estimated as the average of the reciprocal of the *R* – *R* intervals within a specified time window, or as the number of *R* –wave events (heart beats) per unit time on the electrocardiogram (ECG). The *R* –wave events mark the electrical impulses from the heart’s conduction system that represent ventricular contractions. Hence, they are a sequence of discrete occurrences in continuous time, and as such, form a point process. Rather than modeling them to reflect the point process structure of the heart beats, most current methods either treat the heart beat *R* – *R* interval series as continuous-valued signals, or convert them into continuous-valued, evenly spaced measurements for analysis by interpolation of either the *R* – *R* intervals or their reciprocals. We have recently derived new definitions of HR and HRV based on an explicit point process Bayesian probability model for heart rate under the assumption that the stochastic properties of the R-R intervals are governed by an inverse Gaussian renewal model. We can estimate the time-varying inverse Gaussian parameters by either local maximum likelihood (Barbieri et al., 2005) or by adaptive point process estimation (Barbieri et al., 2006), and assess model goodness-of-fit by Kolmogorov-Smirnov tests based on the time-rescaling theorem. These models give a more physiologically sound representation of the stochastic structure in heart beat generation than those provided by current definitions and analysis methods. In particular, the adaptive filter algorithm can compute updates in an on-line fashion and at any desired temporal resolution, and it may be at the core of a new device to monitor heart beat dynamics in clinical setting such as the intensive care unit, the operating room and during labor and delivery (Fig. 1). We here show the application of our adaptive paradigm to data from ten healthy subjects during postural changes.

In this section, we present the heart beat interval and the heart rate probability models, the heart beat interval model parameters, the point process adaptive filtering algorithm to derive instantaneous estimates of heart rate and heart rate variability, and the goodness-of-fit test to evaluate how well these estimates describe the stochastic structure of the *R* – wave events extracted from an ECG.

Each *R* –wave event is initiated by a coordinated depolarization of the heart’s pacemaker cells that begins in the sino-atrial (SA) node and propagates throughout the cardiac muscle. Deterministic models of this integrate (rise of the transmembrane potential)-and-fire (depolarization) mechanism are used regularly to simulate heart beats or *R* –wave events (De Boer et al., 1985; Berger et al., 1986). An elementary, stochastic integrate-and-fire model is the Gaussian random walk model with drift, and the probability density of the first passage times for this random walk process, i.e., the times between threshold crossings (*R* – *R* intervals), is well-known to be the inverse Gaussian (Tuckwell, 1988; Chhikara and Folks, 1989). Therefore, we assume that given any *R* –wave event *u _{k}*, the waiting time until the next

$$f(t|{H}_{k},\theta )={\left[\frac{{\theta}_{p+1}}{2\pi {(t-{u}_{k})}^{3}}\right]}^{\frac{1}{2}}\text{exp}\phantom{\rule{thinmathspace}{0ex}}\{-\frac{1}{2}\frac{{\theta}_{p+1}{[t-{u}_{k}-\mu ({H}_{k},\theta )]}^{2}}{\mu {({H}_{k},\theta )}^{2}(t-{u}_{k})}\},$$

(1)

where 0 < *u*_{1} < *u*_{2} <,…,< *u _{k}* <,…<

The mean and standard deviation of the *R* – *R* probability model in (1) are, respectively,

$${\mu}_{RR}=\mu ({H}_{k},\theta )$$

(2)

$${\sigma}_{RR}={[\mu {({H}_{k},\theta )}^{3}{\theta}_{p+1}^{-1}]}^{\frac{1}{2}}.$$

(3)

Heart rate is often defined as the reciprocal of the *R* – *R* intervals, thus we define *r* = *c*(*t* − *u _{k}*)

$${\mu}_{HR}={\mu}^{*}{({H}_{k},\theta )}^{-1}+{{\theta}_{p+1}^{*}}^{-1}$$

(4)

$${\sigma}_{HR}={\left[\frac{2{\mu}^{*}({H}_{k},\theta )+{\theta}_{p+1}^{*}}{{\mu}^{*}({H}_{k},\theta )\xb7{{\theta}_{p+1}^{*}}^{2}}\right]}^{\frac{1}{2}}.$$

(5)

where ${\mu}^{*}({H}_{k},\theta )={c}^{-1}\mu ({H}_{k},\theta ),{\theta}_{p+1}^{*}={c}^{-1}{\theta}_{p+1}$.

To track the non-stationary behavior in heart beat dynamics that occurs due to changes in state under both physiological and pathological conditions, we assume that the parameter θ is time-varying, and we model the time-varying behavior of θ using a state space model. To define the state model and the observation model, we choose *J* large, and divide (0, *T*] into *J* intervals of equal width Δ = *T* / *J*, so that there is at most one spike per interval. The adaptive parameter estimates will be updated at *j*Δ for *j* = 1,…, *J*.

From the heart beat probability model in (1) we define the associated conditional intensity function as

$$\lambda (j\mathrm{\Delta}|{H}_{j},{\theta}_{j\mathrm{\Delta}})=\frac{f(j\mathrm{\Delta}|{H}_{j},{\theta}_{j\mathrm{\Delta}})}{1-{\displaystyle {\int}_{{u}_{j}}^{j\mathrm{\Delta}}f(u|{H}_{j},{\theta}_{u})du}}.$$

(6)

The conditional intensity function provides a canonical characterization of a point process that gives a history-dependent generalization of the rate function of a Poisson process (Brown et al., 2003).

Once the state model and the observation process model are defined (Barbieri et al., 2006), it follows from (Barbieri et al., 2004; Eden et al., 2004) that the point process adaptive filter algorithm for this system is (*One-Step Prediction*)

$${\theta}_{j|j-1}={\theta}_{j-1|j-1}$$

(7)

(*One-Step Prediction Variance*)

$${W}_{j|j-1}={W}_{j-1|j-1}+{W}_{\epsilon}$$

(8)

(*Posterior Mode*)

$${\theta}_{j|j}={\theta}_{j|j-1}+{W}_{j|j-1}(\mathrm{\text{log}{\lambda}_{j})[{n}_{j}-{\lambda}_{j}\mathrm{\Delta}]}$$

(9)

(*Posterior Variance*)

$${W}_{j|j}={[{W}_{j|j-1}^{-1}-({\mathrm{2}}^{\text{log}}-1}^{}$$

(10)

where λ_{j} =λ (*j*Δ | *H _{j}*, θ

Given θ_{j|j}, the point process adaptive filter estimate of θ at time *j*Δ, it follows from (2), (3), (4) and (5), that the instantaneous estimates of mean *R* – *R*, *R* – *R* interval standard deviation, mean heart rate and heart rate standard deviation at time *j*Δ are respectively (*Mean R-R Interval*)

$${\mu}_{RR}(j\mathrm{\Delta})=\mu ({H}_{j},{\theta}_{j|j})$$

(11)

(*R-R Interval SD*)

$${\sigma}_{RR}(j\mathrm{\Delta})={[\mu {({H}_{j},{\theta}_{j|j})}^{3}{\theta}_{p+1,j|j}^{-1}]}^{\frac{1}{2}}.$$

(12)

(*Mean Heart Rate*)

$${\mu}_{HR}(j\mathrm{\Delta})={\mu}^{*}{({H}_{j},{\theta}_{j|j})}^{-1}+{{\theta}_{p+1,j|j}^{*}}^{-1}$$

(13)

(*Heart Rate SD*)

$${\sigma}_{HR}(j\mathrm{\Delta})={\left[\frac{2{\mu}^{*}({H}_{j},{\theta}_{j|j})+{\theta}_{p+1,j|j}^{*}}{{\mu}^{*}({H}_{j},{\theta}_{j|j})\xb7{{\theta}_{p+1,j|j}^{*}}^{2}}\right]}^{\frac{1}{2}}$$

(14)

Equation (13) provides a new algorithm for computing an instantaneous estimate of heart rate whereas (12) and (14) are new indices of heart rate variability.

To evaluate goodness-of-fit for the heart beat probability model-point process adaptive filter algorithm, i.e., determine how well this model describes the sequence of ECG *R* -wave events, we use the Kolmogorov-Smirnov test based on the time-rescaling theorem for point processes (Brown et al., 2002, Barbieri et al., 2005; Barbieri et al., 2006). Close agreement between the uniform transformation of the ordered observations (empirical quantiles) and the ordered observations from a uniform probability density (model quantiles) is true if and only if there is close agreement between the point process probability model and the series of R-R intervals. Graphically, the better the model describes the data, the more the KS plot lies along the 45° line and inside the 95% confidence bounds.

To assess the correlation structure and hence, possible dependence that may be present beyond first order, we also perform a normal transformation of the observations and compute the serial correlation function for 60 lags (~ 1 min). Small values of the serial correlation function at all lags would suggest that the series of the normal transformation of the observations are independent. Approximate independence suggests that the original model is highly consistent with the R-R interval series.

To illustrate the application of our point process adaptive filter algorithm to actual data, we have analyzed heart beat series from ten healthy subjects performing a tilt table study.

The protocol begins with subjects lying supine for approximately 10 minutes, after which, each subject undergoes 3 types of up-down tilt pairs. The tilt pairs are: rapid up (down) tilt in which the tilt table moved from horizontal (vertical) to vertical (horizontal) in less than 3 s; slow up (down) tilt in which the tilt table moved from horizontal (vertical) to vertical (horizontal) in approximately 1 min; and stand-up (supine) in which the subject stood up immediately supporting his or her own weight and then lied supine immediately from having been standing supporting his own weight (Heldt et al, 2002, 2003).

The wide range of changes in heart rate that can be induced in either short or long time periods make the tilt table protocol and excellent paradigm for testing the ability of our new algorithm to track *R* – *R* interval and heart rate dynamics. Because the subject's legs are not supported, weight bearing from standing and muscle tone in the legs, which normally help return blood to the heart, are diminished. As a consequence, to maintain perfusion, there are compensatory changes in cardiovascular and autonomic activity reflected as changes in heart rate and blood pressure. Similarly, by tilting the subject back from the vertical to the horizontal, a different set of compensatory changes in cardiovascular and autonomic activity can be induced. The degree of compensatory cardiovascular and autonomic activity can be affected by changing the rates at which the postural changes are induced and/or the length of time the subject is maintained in the supine or upright posture.

Following a preliminary partial autocorrelation analysis of the *R* – *R* interval series, we implemented the point process adaptive filter algorithm assuming an AR(8) HDIG model to analyze these data. The initial parameter values were computed by local maximum likelihood analysis (Barbieri et al, 2005) using the first 60 s. We chose the state covariance matrix *W*_{ε} to be the diagonal matrix with values of 6×10^{−2} for θ_{0}, 3×10^{−1} for ${\sigma}_{s}^{2}$, and 1×10^{−6}for the autoregressive parameters by applying the same preliminary local maximum likelihood analysis.

Figure 2 shows results from one subject. In this recording session two rapid tilts were initiated at around 1000 s and 2900 s, slow tilts at 350 s and 2450 s, whereas the subjects stood up at around 1560 s and 2010 s. Our analysis provides time-varying estimates of mean *R* – *R* (Fig. 2A), heart rate (Fig. 2B), *R* – *R* standard deviation (Fig. 2C) and heart rate standard deviation (Fig. 2D) computed using (11–14). While the mean estimates show dynamics consistent with the original beat series, and with the hemodynamic changes elicited by changes in posture, the variability instantaneous indices show very fine fluctuations not directly correlated with posture changes, particularly with significantly faster dynamics than the respective log likelihood instantaneous indices previously estimated (Barbieri et al, 2005). Most importantly, the *R* – *R* and heart rate standard deviations show that time-varying estimates of mean *R* – *R* and heart rate alone do not capture all the dynamic features of heart beat interval.

The goodness-of-fit analysis resulted in the KS plot in Fig. 2E, and the autocorrelation plot in Fig. 2F. The KS plot for the model fit does not lie entirely within the 95% confidence bounds. Nevertheless, the curve does not significantly deviate from the diagonal, keeping all values relatively close to the confidence bounds. Looking at the autocorrelation function of the transformed times, only three lags (lag 1, 2, and 9) have autocorrelation estimates that fall significantly outside the 95% confidence bounds, suggesting that its transformed times are nearly independent. In summary, the goodness-of-fit analysis suggests that the AR(8) HDIG model with time-varying parameters describes well the stochastic structure in this subject’s heart beat series, but also invites for exploration of more refined algorithms and more complex models that could explain more exhaustively the mechanisms behind heart beat dynamics.

Figure 3 better illustrates the different pattern changes of our four measures of heart rate dynamics as elicited by each postural change. Here we show, from top to bottom respectively, the instantaneous estimates of mean *R* – *R*, heart rate, *R* – *R* standard deviation and heart rate standard deviation from subjects 1, 4, and 5 during approximately 200 s before and after a rapid tilt (Fig. 3A), a slow tilt (Fig. 3B), and an upright position (Fig. 3C). Of relevance in this new adaptive analysis is the increase in both *R* – *R* and heart rate standard deviations immediately after the rapid tilt and after standing up. The relatively constant level of heart rate standard deviation after the slow tilt, when compared to the sharp increase immediately after rapid tilt and standing up, suggests new patterns of faster dynamics which may be useful to distinguish physiological differences in these states.

The results in Fig. 3 suggest that our heart rate variability indices help provide a more detailed description of heart beat interval dynamics for an individual in each of the three types of postural change. To illustrate how our measures can be used to help characterize heart rate variability for the population, we analyzed for all 10 subjects one of the periods in the study where the most dynamics in the heart beat intervals would be expected. That is the period prior to the postural change while the subject was in the supine position to the period immediately after the subject assumed an upright posture by a rapid tilt, slow tilt or standing up. For each type of postural change, we define this period of maximal dynamics as beginning 60 seconds before onset of the postural change and extending to 180 s after the onset (Fig. 4). For each subject, we compute each of our four indices during this dynamic period and summarize the results as the average and standard deviation. We term the time interval 60 s after the onset of the postural change as the transient period. We report the four series of *R* – *R*, heart rate, *R* – *R* interval standard deviation and heart rate standard deviation respectively as Δ*RR*, Δ*HR*, Δ*RRV* and Δ*HRV* because we subtract from each series its mean level during the 60s prior to the postural change.

Because we subtract the respective mean levels, all four estimates fluctuate during this period about zero (Fig. 4). At the initiation of the rapid tilt (Fig. 4A and 4B, top graph), Δ*RR* (Δ*HR*) decreases (increases) abruptly and remains at an almost stationary level for the balance of the tilt. In the vertical position there is a wider range of fluctuations, reflected in the standard deviation range (gray curves), in both Δ*RR* and Δ*HR* compared to rest. Both Δ*RRV* and Δ*HRV* (Fig. 4C and 4D, top graph) show initial abrupt increases with the onset of the rapid tilt. As the subject stabilizes in the vertical position at around 200 s, Δ*RRV* fluctuations also stabilize below rest levels, whereas the Δ*HRV* mean level goes back to rest level. Of note, both of these indices show large fluctuations about their mean levels, both in the transient period and in the period immediately following the transient period.

During the slow tilt there is a gradual decrease (increase) in Δ*RR* (Δ*HR*) and the fluctuations around the estimates are consistent with the fact that the stress of the postural change is slowly increasing (Fig. 4A and 4B, middle graph). The Δ*RR* (Δ*HR*) decreases (increases) slowly through the transient period, is well below (above) the baseline of zero by the end of the transient period and stays well below (above) zero for the balance of this postural change. The Δ*RRV* and the Δ*HRV* (Fig. 4C and 4D, middle graph) show a gradual increase through the first part of the slow tilt with an increased level of fluctuations about the time course of each mean. At approximately thirty seconds into the transient period, both show an increase in level and fluctuations about this level. Compared with the preceding rest period, Δ*RRV* stabilizes to levels markedly below rest levels, whereas Δ*HRV* goes back to initial levels, with both measures showing greater fluctuations than during the rest period.

For the stand up postural change Δ*RR* (Δ*HR*) shows an abrupt change in the transient period of more than 300 s for the *R* – *R* interval (20 beats per minute for heart rate) within fifteen seconds (Fig. 4A and 4B, bottom graph). Both indices return almost to baseline by thirty seconds, but then slowly decrease (increase) again for the balance of this postural maneuver. As observed for the rapid and slow tilt series, the variability about this level is increased both during the transient period and following the transient period. The Δ*RRV* increases in the transient period, then declining below rest level prior to the postural change (Fig. 4C, bottom graph). The fluctuations about this level, both during and after the transient period, are substantially greater than when the subjects were at rest. The Δ*HRV* change in the transient period mirrors the change reported for Δ*HR* (Fig. 4D, bottom graph). It shows a very abrupt increase reaching a maximum at around fifteen to twenty seconds into the transient period and declines to a level that is still above baseline by the end of the transient period. Also here, as observed for the other two maneuvers, Δ*RRV* stabilizes to levels markedly below rest level, whereas Δ*HRV* goes back to the initial level. This trend, common to all posture changes, confirms on one side Δ*RRV* as an index of autonomic activation as defined by standard HRV analysis (Task Force, 1996), and points at Δ*HRV* as a new measure proportional to the transient hemodynamic variations.

In summary, our results show that together our instantaneous HR and HRV estimates provide a different signature for the transient period for each of the three types of postural change (Fig. 4). First, the time courses of the mean R–R intervals and the heart rate series follow the well documented patterns of cardiovascular response to orthostatic stress (Borst et al., 1982; Ewing et al., 1980; Heldt et al., 2002, 2003; Sprangers et al., 2003; Tanaka et al., 1995). In contrast, our heart rate variability series revealed a new pattern of temporal dynamics. In particular, the sharp increase in heart rate standard deviation immediately after standing up, that persisted for at least 20 seconds before returning to baseline (Fig. 4D), may be associated not only with autonomic changes (Stauss, 2003), but also with heart rate modulation due to an increase in venous return as leg muscles contract when the upright posture is assumed (Heldt et al., 2002; Sprangers et al., 2003; Tanaka et al., 1995). Hence, our heart rate standard deviation index may offer a potentially non-invasive correlate of changes in cardiac output and/or total peripheral resistance (Sprangers et al., 2003; Taylor et al., 1995).

We have presented a point process algorithm to study heart beat dynamics as applied to recordings from healthy subjects during a Tilt table protocol. The algorithm is based on the inverse Gaussian probability model because this model can be derived as a stochastic version of the widely-applied deterministic integrate-and-fire models used to simulate heart beats. We have used an autoregressive model to define the mean of the inverse Gaussian and to represent the dependence of the *R* – *R* interval length on the recent state of the autonomic inputs to the SA node. The point process adaptive filter was used to estimate the time-varying nature of the inputs to the SA node. Because the point process heart beat model is defined in continuous time, the algorithm computes estimates of mean *R* – *R*, *R* – *R* standard deviation, mean heart rate and heart rate standard deviation that can be updated at any desired temporal resolution. With changes in autonomic state, our analysis shows different behaviors between HR and HRV dynamics, as well as distinctive signatures reflecting the different hemodynamic changes elicited by three kinds of posture variation.

Future work will focus on more complex representations of the probability function, incorporating the point process framework into linear and nonlinear models of cardiovascular control and autonomic regulation, with inclusion of other cardiovascular variables such as arterial blood pressure, central venous pressure and respiration.

We are grateful to Roger G. Mark and Thomas Heldt, Harvard-Massachusetts Institute of Technology Division of Health Sciences and Technology, for kindly providing the tilt-table data analyzed in this study. This work was supported by NIH Grants R01-HL084502, R01-DA015644 and DP1-OD003646.

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