Abstract
Aortic stenosis (AS) once was conceptualized as a mechanical problem with a fixed left ventricular (LV) afterload because of an obstructive valve. With time, there has been growing recognition that AS functions more like a series circuit, with important contributions from the ventricle through to the vasculature. Emerging evidence suggests that higher blood pressure and increased arterial stiffness, synonymous with vascular aging, increases global LV afterload in patients with AS. This in turn, has adverse consequences on quality-of-life measures and survival. Although traditional methods have emphasized measurement of the transvalvular pressure gradient, focusing on valvular hemodynamics alone may be inadequate. By definition, total vascular load of the human circulation includes both steady and pulsatile components. Steady load is best represented by the systemic vascular resistance whereas pulsatile load occurs because of wave reflections and vascular stiffness, and is often referred to as the valvulo-arterial impedance. In the following Review, we evaluate existing and upcoming methods to assess vascular load in patients with AS in order to better understand the effects of vascular aging on this insidious disease process.
Keywords
- applanation tonometry
- cardiac magnetic resonance imaging
- systemic vascular impedance
- transthoracic echocardiography
- valvulo-arterial impedance
- valvulo-arterial load
1. Introduction
Aortic valve stenosis (AS) is a progressive disease in which the end-stage is characterized by an increase in global left ventricular (LV) load, resulting in inadequate cardiac output, decreased exercise capacity, congestive cardiac failure and death [1]. Without correction, the rate of death is more than 50% at 2-years for patients with severe AS and symptomatic disease [2]. Patients with AS are frequently elderly, with concomitant hypertension and increased arterial stiffness. Higher global LV load – as reflected in blood pressure, resistive (i.e. systemic vascular resistance) and pulsatile (i.e. vascular impedance) load – is known to be associated with poorer quality-of-life measures and survival outcomes. As such, AS is no longer regarded as an isolated valvular disease, but rather a pathological process involving the left ventricle, aortic valve and large conducting arteries (Figure 1) [3].
The past decade has seen a rapid uptake of device technologies to treat patients with AS. Despite the obvious effects of vascular aging, uncoupling intrinsic properties of the left ventricle and arterial tree from the degree of valvular stenosis remains challenging. This is particularly true of patients with severe AS with low-flow/low-gradient (LF-LG) (aortic valve area [AVA] ≤1 cm2; ejection fraction [EF] ≤30–45%; and mean transvalvular gradient ≤30–40 mmHg) or paradoxical LF-LG severe AS (LVEF ≥50%; indexed stroke volume [SVi] ≤35 mL/m2; and mean gradient ≤40 mmHg). This is important, however, as acute interventions on either compartment may cause reciprocal changes in the other. Patients with severe LF-LG or paradoxical LF-LG AS, for example, are at considerably higher risk of ongoing exertional intolerance, even after relief of valvular obstruction, due to presumed mismatch between ventricular filling, valvular stenosis, and vascular stiffness.
Pulsatile pressure-flow relationships to describe vascular impedance (the relationship of pressure to flow) of the human circulation were first reported over half-a-century ago in (then) pioneering invasive studies [4, 5]. The clinical use of this technique for determination of vascular impedance has remained limited however, as high-fidelity catheters are considered cumbersome, expensive and may fail to appreciate the eccentricities of pressure and flow dynamics in the ascending aorta. Over the intervening years, measurements of steady-state load (such as systolic arterial pressure, systemic arterial compliance, pulse pressure and systemic vascular resistance [SVR]) have erroneously been taken to represent the vascular impedance. The advent of transcatheter aortic valve implantation (TAVI) has re-ignited this conversation.
As discussed further below, simultaneous high-fidelity pressure and flow catheters have recently been used to describe the acute changes that occur following TAVI [6]. The valvulo-arterial impedance (ZVA) index obtained by Doppler echocardiography (TTE) is one of the most widely adopted non-invasive methods to assess vascular impedance in patients with AS [7]. Valvulo-arterial impedance is assessed using brachial systolic pressure, mean aortic pressure gradient and indexed stroke volume within the LV outflow tract. It has been found to be useful in patients with AS because it incorporates stenosis severity, volume flow rate, body size, SVR and vascular impedance. More recent studies have utilized non-invasive pressure (from carotid or radial applanation tonometry [AT]) and flow velocity (from the LV outflow tract on cardiac magnetic resonance [CMR]) to estimate vascular impedance in the time or frequency domain [8, 9].
Determination of both the steady-state and pulsatile components of the vascular tree are expected to play an increasingly important role in the clinical evaluation of patients with severe LF-LG or paradoxical LF-LG AS states moving forward, as well as in the prognostication of adverse clinical outcomes following TAVI. The following Review provides an overview of key concepts, as well as invasive and non-invasive methods to measure global LV load in individuals with AS.
2. Defining hydraulic load of the human circulation
Hydraulic load of the systemic circulation includes both steady-state and pulsatile components. Steady-state load is best represented by the SVR, although systolic arterial pressure, systemic arterial compliance, and pulse pressure are frequently used. Systemic vascular resistance is calculated as:
where
Pulsatile load occurs because of wave reflections and vascular stiffness and is best described using the term vascular impedance (Z), or the relationship of pressure to flow. When the general term ‘impedance’ is applied to a vascular bed, it is usually referring to “input impedance” (Zin), this being the relationship between pulsatile pressure and pulsatile flow recorded in an artery feeding a particular vascular bed. Zin can be estimated with the following complex equation:
where
3. Effects of vascular aging in patients with aortic stenosis
With aging, the central elastic aorta progressively dilates, elongates and becomes tortuous with stiffened, thickened walls [13]. Characteristic age-related changes in aortic flow velocity, pressure waveform and vascular impedance now well described [11, 14]. Stiffer, older vessels lead to a faster velocity of pressure pulse and earlier timing of reflected pulse wave from the periphery, augmenting central aortic systolic pressure and yielding a greater afterload on the heart [10, 11]. Systemic vascular resistance is higher, while the systemic impedance phase typically shows similar values for the first harmonic at all ages, then increases for all age groups, crossing zero to positive values later in elderly patients and also those with AS (around 3–4 Hz). Harmonic refers to the analysis of signals with respect to frequency (Hz) rather than time. Put simply, a frequency-domain graph shows how much of the signal lies within each given frequency band over a range of frequencies. The effect of age-related alterations to vascular impedance is to cause further mismatch between energy expenditure of LV ejection, and an increase in pulsatile energy lost in the circulation. The result is a direct increase in LV afterload and left ventricular mass. Additionally, mean aortic systolic pressure is increased, thereby increasing LV oxygen requirements and LV afterload, while mean aortic diastolic pressure is decreased, reducing coronary blood flow [15].
4. Effects of transcatheter aortic valve implantation on vascular impedance
Limited studies have explored the effect of aortic valve replacement on vascular impedance in elderly patients with AS. Residual LV afterload is more often than not assumed by assessing transvalvular pressure gradient, effective orifice area or the degree of valve patient-prosthesis mis-match [16]. However, focusing on valvular hemodynamics alone is clearly inadequate. In one study,
5. Invasive methods to determine vascular impedance
As mentioned earlier, vascular impedance (Z-INV) of the human circulation was first determined in pioneering catheter studies during the 1960’s and 1970’s [13, 18, 19, 20, 21]. From this early work, a typical Z-INV pattern in the ascending aorta was demonstrated to have a relatively high modulus at zero frequency – which is the peripheral/systemic resistance or steady-state load – then experience a fall of modulus with increasing frequency to a minimal value around 3–4 Hz, before rising to a maximal value around twice the minimal frequency and continuing to fluctuate around its characteristic impedance at higher frequencies [5, 22]. The phase (or difference in angle) value was found to be negative at low frequencies – indicating arterial flow leading pressure – then crossed zero around the same frequency where modulus was at a minimum and became positive at higher frequencies [5, 22]. These impedance patterns are mainly influenced by ascending aorta distensibility and arterial pulse wave velocity [4], both of which are significantly altered in the presence of vascular aging and cardiovascular disease.
Studies of Z-INV have not been actively pursued beyond the 1970s until recently, partly because of the requirement of invasive technique and costly sensors to register arterial pressure and/or flow waveform accurately. In a study by
6. Echocardiographic methods to determine vascular impedance
Pulse pressure (PP), systemic arterial compliance (SAC), the systemic vascular resistance index (SVRi), and valvulo-arterial impedance (ZVA) are the most widely applied echocardiographic methods to determine vascular impedance in patients with AS. Steady-state load is best represented by the SVRi, which is calculated as:
where
where
where
Since ZVA was first described in patients with AS, elevated values have been associated with poorer outcomes, a greater degree of myocardial dysfunction and reduced overall survival [24, 25]. Poorer outcomes are thought to be related to comorbidities which elevate vascular impedance – namely advanced age, hypertension, and obesity [26]. For patients with asymptomatic severe AS, who have a 3% mortality rate a 5-years if left untreated, a ZVA index >5 mmHg/mL/m2 is associated with a 2.5-fold increase in overall mortality, regardless of treatment type [24]. Paradoxical low-flow, low-gradient AS is known to account for one-third of patients with severe AS and preserved EF. Patients with paradoxical LF-LG AS and a ZVA index >5.5 mmHg/mL/m2 also have increased mortality [24]. Interestingly, in patients with LF-LG AS, elevated ZVA has not yet been found to be associated with operative or long-term mortality [27]. The prognostic impact of ZVA is not well studied in patients with symptomatic moderate AS.
Despite the accessibility of ZVA and its widespread use, the technique has limitations including: (i) the potential for underestimation of flow velocity due to misalignment of the Doppler signal with flow direction; (ii) the risk of underestimation of LV outflow tract diameter due to inadequate quality and/or positioning of the imaging plane; (iii) measurement variability related to manual tracing of flow velocity contours, and; (iv) the calculation of mean pressure from brachial cuff pressure rather than direct measurement of central aortic pressure [12]. Furthermore, ZVA is measured as the ratio of pressure to indexed volume (rather than pressure to flow) and may therefore be more accurately described as a resistance index rather than a true measure of vascular impedance (Figure 2).
7. Cardiac magnetic resonance methods to determine vascular impedance
With the introduction of CMR into routine clinical practise, several parameters of aortic stiffness in patients with AS have now been described - aortic compliance, distensibility, capacitance, elasticity, stiffness index and valvulo-arterial impedance. Two methods to assess vascular impedance in patients with AS have been described – valvulo-arterial impedance instantaneous (ZVA-INS) and valvulo-arterial load (VAL).
where
where
VAL differs from ZVA-INS as it permits (i) simultaneous acquisition of aortic pressure and flow; (ii) measures the combined LV afterload; (iii) samples the multiple flow profiles seen in patients with AS [28], and; (iv) estimates systemic impedance in the frequency domain [29]. As left ventricular hypertrophy, aortic valve stenosis and vascular stiffness represent elevated impedances in series, simple summation of these resistances (as in the case of ZVA-INS) may lead to an overestimation of global LV load [9, 30]. Studies of CMR vascular impedance estimation in patients undergoing transcatheter aortic valve implantation (TAVI) are currently underway (Figure 3).
8. Other methods
Although vascular impedance measures the pulsatile properties of the human circulation, aortic pulse wave velocity (PWV) is considered the ‘gold-standard’ measurement of arterial stiffness and an important tool to evaluate both arterial system damage, vascular adaptation, and therapeutic efficiency. Pulse wave velocity can be measured using non-invasive, reproducible, and relatively inexpensive techniques. The effect of elevated PWV has been studied in AS patients undergoing both surgical and transcatheter replacement, and found to be associated with poorer quality-of-life measures [31] and mortality [32] irrespective of stenosis severity. Waveform analysis post TAVI typically shows an acute increase in the forward compression wave, backward compression wave and forward expansion energies [33]. The duration that these changes persist post correction of AS remain unclear (Figure 2).
9. Future directions
Beyond techniques to determine vascular impedance in patients with AS, the question remains – what can be done to ameliorate the insidious effects of arterial stiffness in patients with AS before and after intervention? Indeed, arterial stiffness involves both arteriosclerosis and atherosclerosis and is influenced by structural and biochemical changes within vessel walls, involving changes in elastin/collagen ratio, elastin cross-linking, vascular calcification, vascular smooth muscle cell stiffness, endothelial dysfunction, and inflammation [34, 35]. Lifestyle modification may have a considerable impact. A diet rich in fruits and vegetables, polyunsaturated fatty acids, coca flavonoids, tea catechins and dairy products with a limited intake of salt and red meat have all been demonstrated to reduce arterial stiffness [36]. Anti-hypertensive treatment, anti-diabetic drugs and lipid lowering agents have also been shown to reverse vascular aging in middle aged individuals, and to a lesser degree, in older patients [37]. The effect of diet, lifestyle, and pharmaceutical interventions in elderly patients with AS remains to be determined.
10. Conclusions
The natural history of AS is dictated by a progressive decoupling of the aortic valve from the left ventricle and vascular system over time. Vascular function is conditioned by the upstream valvular obstruction, which in turn dampens forward and backward compression waves in the arterial tree. Abrupt correction of valvular stenosis may have unforeseen effects on the left ventricle and vasculature not adequately accounted for using traditional TTE imaging techniques. Simultaneous CMR and AT techniques are uniquely placed as they better account for steady-state and pulsatile components of flow. Incorporation of techniques to assess vascular impedance in patients with AS is expected to play a greater role in patient selection of severe AS sub-types and prognosis with time.
Funding
All other authors have reported that they have no funding disclosures relevant to the contents of this paper to disclose.
Disclosures
All authors have reported that they have no relationships relevant to the contents of this paper to disclose.
Abbreviations
AA | ascending aorta |
AS | aortic valve stenosis |
AT | applanation tonometry |
CMR | cardiac magnetic resonance |
FFT | fast Fourier transformation |
LV | left ventricular |
MPA | main pulmonary artery |
PA | pulmonary artery |
Pn | derived central aortic pressure |
PH | pulmonary hypertension |
PWV | pulse wave velocity |
Qn | aortic flow velocity product |
RHC | right heart catheterisation |
RV | right ventricular |
TAVI | transcatheter aortic valve implantation |
VAL | valvulo-arterial load |
VTF | velocity transfer function |
ZC | characteristic impedance |
Zin | input impedance |
ZVA-INS | valvulo-arterial impedance-instantaneous. |
References
- 1.
Otto CM, Prendergast B. Aortic-valve stenosis--from patients at risk to severe valve obstruction. The New England Journal of Medicine. 2014; 371 (8):744-756 - 2.
Makkar RR, Fontana GP, Jilaihawi H, Kapadia S, Pichard AD, Douglas PS, et al. Transcatheter aortic-valve replacement for inoperable severe aortic stenosis. The New England Journal of Medicine. 2012; 366 (18):1696-1704 - 3.
Briand M, Dumesnil JG, Kadem L, Tongue AG, Rieu R, Garcia D, et al. Reduced systemic arterial compliance impacts significantly on left ventricular afterload and function in aortic stenosis: Implications for diagnosis and treatment. Journal of the American College of Cardiology. 2005; 46 (2):291-298 - 4.
O'Rourke MF, Taylor MG. Input impedance of the systemic circulation. Circulation Research. 1967; 20 (4):365-380 - 5.
Murgo JP, Westerhof N, Giolma JP, Altobelli SA. Aortic input impedance in normal man: Relationship to pressure wave forms. Circulation. 1980; 62 (1):105-116 - 6.
Yotti R, Bermejo J, Gutierrez-Ibanes E, Perez del Villar C, Mombiela T, Elizaga J, et al. Systemic vascular load in calcific degenerative aortic valve stenosis: Insight from percutaneous valve replacement. Journal of the American College of Cardiology. 2015; 65 (5):423-433 - 7.
Hachicha Z, Dumesnil JG, Pibarot P. Usefulness of the valvuloarterial impedance to predict adverse outcome in asymptomatic aortic stenosis. Journal of the American College of Cardiology. 2009; 54 (11):1003-1011 - 8.
Soulat G, Kachenoura N, Bollache E, Perdrix L, Diebold B, Zhygalina V, et al. New estimate of valvuloarterial impedance in aortic valve stenosis: A cardiac magnetic resonance study. Journal of magnetic resonance imaging : JMRI. 2017; 45 (3):795-803 - 9.
Hungerford SL, Adji AI, Bart NK, Lin L, Namasivayam MJ, Schnegg B, et al. A novel method to assess valvulo-arterial load in patients with aortic valve stenosis. Journal of hypertension. 2020 - 10.
O'Rourke MF. Vascular impedance in studies of arterial and cardiac function. Physiological Reviews. 1982; 62 (2):570-623 - 11.
Hungerford SL, Adji AI, Bart NK, Lin L, Song N, Jabbour A, et al. Ageing, hypertension and aortic valve stenosis - understanding the series circuit using cardiac magnetic resonance and applanation tonometry. International Journal of Cardiology Hypertension. 2021; 9 :100087 - 12.
Hungerford SL, Adji AI, Hayward CS, Muller DWM. Ageing, hypertension and aortic valve stenosis: A conscious uncoupling. Heart, Lung & Circulation. 2021 - 13.
Nichols WWR, Hartley MF, McDonalds C. Blood Flow in Arteries: Theoretical, Experimental and Clinical Principles. Arnold and Oxford University Press Inc.; 1997 - 14.
Ohyama Y, Redheuil A, Kachenoura N, Ambale Venkatesh B, Lima JAC. Imaging insights on the aorta in aging. Circulation Cardiovascular imaging. 2018; 11 (4):e005617 - 15.
Westerhof N, O'Rourke MF. Haemodynamic basis for the development of left ventricular failure in systolic hypertension and for its logical therapy. Journal of hypertension. 1995; 13 (9):943-952 - 16.
Pibarot P, Dumesnil JG. New concepts in valvular hemodynamics: Implications for diagnosis and treatment of aortic stenosis. The Canadian Journal of Cardiology. 2007; 23 (Suppl. B):40b-47b - 17.
Lindman BR, Otto CM, Douglas PS, Hahn RT, Elmariah S, Weissman NJ, et al. Blood pressure and arterial load after Transcatheter aortic valve replacement for aortic stenosis. Circulation Cardiovascular Imaging. 2017; 10 (7) - 18.
Mcdonald DA. Taylor MG, editors. The Hydrodynamics of the Arterial Circulation. 1959 - 19.
Womersley JR. Method for the calculation of velocity, rate of flow and viscous drag in arteries when the pressure gradient is known. The Journal of Physiology. 1955; 127 (3):553-563 - 20.
Milnor WR. Arterial impedance as ventricular afterload. Circulation Research. 1975; 36 (5):565-570 - 21.
Nichols WW, Conti CR, Walker WE, Milnor WR. Input impedance of the systemic circulation in man. Circulation Research. 1977; 40 (5):451-458 - 22.
O'Rourke MF, Avolio AP. Pulsatile flow and pressure in human systemic arteries. Studies in man and in a multibranched model of the human systemic arterial tree. Circulation Research. 1980; 46 (3):363-372 - 23.
Chemla D, Hébert JL, Coirault C, Zamani K, Suard I, Colin P, et al. Total arterial compliance estimated by stroke volume-to-aortic pulse pressure ratio in humans. The American Journal of Physiology. 1998; 274 (2):H500-H505 - 24.
Cramariuc D, Cioffi G, Rieck AE, Devereux RB, Staal EM, Ray S, et al. Low-flow aortic stenosis in asymptomatic patients: Valvular-arterial impedance and systolic function from the SEAS substudy. JACC Cardiovascular Imaging. 2009; 2 (4):390-399 - 25.
Hachicha Z, Dumesnil JG, Bogaty P, Pibarot P. Paradoxical low-flow, low-gradient severe aortic stenosis despite preserved ejection fraction is associated with higher afterload and reduced survival. Circulation. 2007; 115 (22):2856-2864 - 26.
Kruszelnicka O, Chmiela M, Bobrowska B, Świerszcz J, Bhagavatula S, Bednarek J, et al. Depressed systemic arterial compliance is associated with the severity of heart failure symptoms in moderate-to-severe aortic stenosis: A cross-sectional retrospective study. International Journal of Medical Sciences. 2015; 12 (7):552-558 - 27.
Levy F, Laurent M, Monin JL, Maillet JM, Pasquet A, Le Tourneau T, et al. Aortic valve replacement for low-flow/low-gradient aortic stenosis operative risk stratification and long-term outcome: A European multicenter study. Journal of the American College of Cardiology. 2008; 51 (15):1466-1472 - 28.
Woldendorp K, Bannon PG, Grieve SM. Evaluation of aortic stenosis using cardiovascular magnetic resonance: A systematic review & meta-analysis. Journal of cardiovascular magnetic resonance: official journal of the Society for Cardiovascular Magnetic Resonance. 2020; 22 (1):45 - 29.
Qureshi MU, Colebank MJ, Schreier DA, Tabima DM, Haider MA, Chesler NC, et al. Characteristic impedance: Frequency or time domain approach? Physiological Measurement. 2018; 39 (1):014004 - 30.
Laskey WK, Kussmaul WG 3rd. Hypertension, aortic valve stenosis, and the aorta: More lessons from TAVR. Journal of the American College of Cardiology. 2015; 65 (5):434-436 - 31.
Kidher E, Harling L, Nihoyannopoulos P, Shenker N, Ashrafian H, Francis DP, et al. High aortic pulse wave velocity is associated with poor quality of life in surgical aortic valve stenosis patients. Interactive Cardiovascular and Thoracic Surgery. 2014; 19 (2):189-197 - 32.
Broyd CJ, Patel K, Pugliese F, Chehab O, Mathur A, Baumbach A, et al. Pulse wave velocity can be accurately measured during transcatheter aortic valve implantation and used for post-procedure risk stratification. Journal of Hypertension. 2019; 37 (9):1845-1852 - 33.
Michail M, Hughes AD, Comella A, Cameron JN, Gooley RP, McCormick LM, et al. Acute effects of Transcatheter aortic valve replacement on central aortic hemodynamics in patients with severe aortic stenosis. Hypertension. 2020; 75 (6):1557-1564 - 34.
Nilsson PM, Boutouyrie P, Laurent S. Vascular aging: A tale of EVA and ADAM in cardiovascular risk assessment and prevention. Hypertension. 2009; 54 (1):3-10 - 35.
Regnault V, Challande P, Pinet F, Li Z, Lacolley P. Cell senescence: Basic mechanisms and the need for computational networks in vascular ageing. Cardiovascular Research. 2021; 117 (8):1841-1858 - 36.
Mozos I, Jianu D, Stoian D, Mozos C, Gug C, Pricop M, et al. The relationship between dietary choices and health and premature vascular ageing. Heart, Lung & Circulation. 2021; 30 (11):1647-1657 - 37.
Laurent S, Boutouyrie P. Vascular ageing - state of play, gaps and key issues. Heart, Lung & Circulation. 2021; 30 (11):1591-1594