Abstract

Cardiovascular diseases are the leading cause of death worldwide. Pulse wave analysis (PWA) technique, which reconstructs and analyses aortic pressure waveform based on non-invasive peripheral pressure recording, became an important bioassay for cardiovascular assessment in a general population. The aim of our study was to establish a pulse wave propagation modeling framework capable of matching clinical PWA data from healthy individuals on a per-subject basis. Radial pressure profiles from 20 healthy individuals (10 males, 10 females), with mean age of 42 ± 10 years, were recorded using applanation tonometry (SphygmoCor, AtCor Medical, Australia) and used to estimate subject-specific parameters of mathematical model of blood flow in the system of fifty-five arteries. The model was able to describe recorded pressure profiles with high accuracy (mean absolute percentage error of 1.87 ± 0.75%) when estimating only 6 parameters for each subject. Cardiac output (CO) and stroke volume (SV) have been correctly identified by the model as lower in females than males (CO of 3.57 ± 0.54 vs. 4.18 ± 0.72 L/min with p-value < 0.05; SV of 49.5 ± 10.1 vs. 64.2 ± 16.8 ml with p-value = 0.076). Moreover, the model identified age related changes in the heart function, i.e. that the cardiac output at rest is maintained with age (r = 0.23; p-value = 0.32) despite the decreasing heart rate (r = −0.49; p-value < 0.05), because of the increase in stroke volume (r = 0.46; p-value < 0.05). Central PWA indices derived from recorded waveforms strongly correlated with those obtained using corresponding model-predicted radial waves (r > 0.99 and r > 0.97 for systolic (SP) and diastolic (DP) pressures, respectively; r > 0.77 for augmentation index (AI); all p—values < 0.01). Model-predicted central waveforms, however, had higher SP than those reconstructed by PWA using recorded radial waves (5.6 ± 3.3 mmHg on average). From all estimated subject-specific parameters only the time to the peak of heart ejection profile correlated with clinically measured AI. Our study suggests that the proposed model may serve as a tool to computationally investigate virtual patient scenarios mimicking different cardiovascular abnormalities. Such a framework can augment our understanding and help with the interpretation of PWA results.

Highlights

  • Over the last several decades pulse wave analysis (PWA) and pulse wave velocity (PWV) techniques became a well-recognized non-invasive tools to assess cardiovascular state, with PWV being the gold-standard for the measurement of arterial stiffness [1, 2]

  • The predictions of a physiology-based mathematical model of pulse wave propagation in the arterial tree were compared to a pulse wave analysis results performed using commercially available device on a group of 20 healthy volunteers

  • The first and the most crucial part of the study focused on fitting the model-predicted radial pressure waveforms to those recorded non-invasively using applanation tonometry

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Summary

Introduction

Over the last several decades pulse wave analysis (PWA) and pulse wave velocity (PWV) techniques became a well-recognized non-invasive tools to assess cardiovascular state, with PWV being the gold-standard for the measurement of arterial stiffness [1, 2]. The clinical benefits of using PWA to assess the cardiovascular risk and the impact of pharmacological intervention on the central blood pressure have been clearly shown in clinical trials [3, 4] Those two techniques, are not interchangeable and they are limited by the scarce data of reference values for a healthy population [5]. The quality of central pressure waveform reconstruction is especially important for the phase of the PWA during which some indices characterizing the wave, in addition to systolic and diastolic pressures, are being looked for [5] One of such indices, which is associated with aging and cardiovascular risk [16,17,18,19], is augmentation index (AI) that represents the augmentation of central pressure height that is being introduced by the reflected waves [20], compare Fig 1

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