- Open Access
Discrepancies between cardiovascular magnetic resonance and Doppler echocardiography in the measurement of transvalvular gradient in aortic stenosis: the effect of flow vorticity
© Garcia et al.; licensee BioMed Central Ltd. 2013
- Received: 6 May 2013
- Accepted: 3 September 2013
- Published: 20 September 2013
Valve effective orifice area EOA and transvalvular mean pressure gradient (MPG) are the most frequently used parameters to assess aortic stenosis (AS) severity. However, MPG measured by cardiovascular magnetic resonance (CMR) may differ from the one measured by transthoracic Doppler-echocardiography (TTE). The objectives of this study were: 1) to identify the factors responsible for the MPG measurement discrepancies by CMR versus TTE in AS patients; 2) to investigate the effect of flow vorticity on AS severity assessment by CMR; and 3) to evaluate two models reconciling MPG discrepancies between CMR/TTE measurements.
Eight healthy subjects and 60 patients with AS underwent TTE and CMR. Strouhal number (St), energy loss (EL), and vorticity were computed from CMR. Two correction models were evaluated: 1) based on the Gorlin equation (MPGCMR-Gorlin); 2) based on a multivariate regression model (MPGCMR-Predicted).
MPGCMR underestimated MPGTTE (bias = −6.5 mmHg, limits of agreement from −18.3 to 5.2 mmHg). On multivariate regression analysis, St (p = 0.002), EL (p = 0.001), and mean systolic vorticity (p < 0.001) were independently associated with larger MPG discrepancies between CMR and TTE. MPGCMR-Gorlin and MPGTTE correlation and agreement were r = 0.7; bias = −2.8 mmHg, limits of agreement from −18.4 to 12.9 mmHg. MPGCMR-Predicted model showed better correlation and agreement with MPGTTE (r = 0.82; bias = 0.5 mmHg, limits of agreement from −9.1 to 10.2 mmHg) than measured MPGCMR and MPGCMR-Gorlin.
Flow vorticity is one of the main factors responsible for MPG discrepancies between CMR and TTE.
- Aortic stenosis
- Cardiovascular magnetic resonance
- Mean pressure gradient
- Flow vorticity
Valve effective orifice area (EOA) and mean transvalvular pressure gradient (MPG) are the most frequently used parameters to assess aortic stenosis (AS) severity . Current ACC/AHA and ESC guidelines suggest an EOA < 1.0 cm2 and a MPG > 40 mmHg as main criteria to define a severe AS [1, 2]. Transthoracic Doppler-echocardiography (TTE) is the primary method utilized in clinical practice to assess and grade AS severity. Since TTE has some theoretical and technical limitations  cardiovascular magnetic resonance (CMR) has emerged as a non-invasive, radiation-free accurate alternative method to corroborate AS severity when uncertain or discordant results are obtained at TTE [3–6]. However, previous studies have showed that MPG measured by CMR may differ from the one obtained by TTE, mainly when transvalvular velocity is greater than 4 m/s [3, 4, 7–10]. It was hypothesized that this underestimation might be due to the following factors: flow turbulence generated downstream the severe AS, local signal loss, background noise and phase wrap [7, 11–14].
Energy loss (EL) represents the energetic cost (in mmHg) between the LVOT and the ascending aorta after pressure recovery [18–22]. Vorticity intensity (ω) can be used to estimate the dissipation effects within the flow . Interestingly, a recent study demonstrated that vorticity jet shear layer can also be used to estimate EOA using CMR velocity measurements . Strouhal number (St) represents the dimensionless oscillating flow through the aortic valve .
The objectives of this study were: 1- to identify the factors responsible for the discrepancies in the MPG measurement by CMR versus TTE in patients with AS, 2- to investigate the effect of vorticity on AS severity assessment by CMR and 3- to evaluate two models to reconciling MPG discrepancies between CMR/TTE measurements.
Eight (8) healthy control subjects and 60 patients with mild to severe AS (0.60 cm2 ≤ EOATTE ≤ 1.79 cm2) underwent comprehensive research TTE and CMR exams in the context of this study. All subjects were prospectively recruited based on standard clinical TTE exams. Both tricuspid and bicuspid AS patients were included. Exclusion criteria were: age < 21 years old, LV ejection fraction < 50%, more than mild mitral disease or aortic regurgitation, poor TTE imaging quality and standard contra-indications to magnetic resonance imaging. The study was approved by the Ethical Review Board (Comité d’Éthique de la Recherche, Institut Universitaire de Cardiologie et de Pneumologie de Québec) and all patients provided written informed consent for their participation in this study.
Valve hemodynamics: transvalvular pressure gradients were determined by simplified Bernoulli formula: MPGTTE = 4 × Vmean 2, where V is the mean systolic aortic transvalvular velocity; and valve EOA was calculated by continuity equation: EOATTE = SVLVOT/ VTIAo = (VTILVOT × ALVOT) / VTIAo , where SVLVOT is the stroke volume measured in the LVOT, ALVOT is the cross-sectional area of the LVOT and VTILVOT and VTIAo are the velocity-time integrals at the LVOT and the vena contracta, respectively. AS severity was classified on the basis of TTE-derived EOA: Mild to moderate (EOA> 1.0 cm2) and severe (EOA ≤ 1.0 cm2);
Parameters of arterial hemodynamics: Systemic arterial compliance (SAC) was computed using the following formula: SAC = SVi/PP, where SVi is the stroke volume indexed to the body surface area and PP is the pulse arterial pressure. Systemic vascular resistance (SVR) was also estimated from the following formula: SVR = 80MAP/80 × MAP /CO, where MAP is the mean arterial pressure and CO is the cardiac output.
Cardiovascular magnetic resonance
CMR studies were performed 2 to 4 weeks after TTE with patients in comparable hemodynamic state (SVTTE = 80±14 vs. SVCMR = 77±17, p=NS; heart rate TTE = 63±10 bpm vs. heart rate CMR = 65±11 bpm, p = NS). Imaging was performed with a 1.5 Tesla Philips Achieva scanner operating release 2.6 level 3 and dedicated phased-array cardiac coil during successive end-expiratory breath-holds (Philips Healthcare, Best, The Netherlands) as described in previous studies [3, 5, 6]. Typical parameters included TR/TE of 3.4/1.2 ms, flip angle 40°, NEX of 1, yielding in-plane spatial resolution of 1.6×2 mm. Through-plane phase-contrast imaging was performed during breath-hold in the LVOT at 12 mm upstream from the aortic valve annulus (reference: 0 mm), in the ascending aorta (Ao) at 10 mm downstream of the aortic annulus, both planes parallel to the aortic valve annulus plane. Flow imaging parameters consisted of: TR/TE = 4.60-4.92/2.76-3.05 ms, flip angle = 15°, 24 phases, pixel spacing = 1.32–2.07 mm, slice thickness = 10 mm and acquisition matrix = 256 × 208, scan time = 10–25 s without SENSE. For each patient, peak aortic jet velocity measured by TTE was used to define CMR encoding velocity (CMR encoding velocity = (1.25 to 1.5) × peak jet velocity, range from 1.5 to 5.5 m/s) to optimally define resolution and avoid signal wrap.
CMR images acquisitions and analyses were performed by investigators blinded to clinical and TTE results. A custom-made research application was developed using Matlab software (Mathworks, Natick, Ma, USA) to process and analyze velocity-encoded images [5, 26] and the image stack was processed to filter background noise. Regions of interest (ROIs) were defined on each of the 24 phases of anatomical magnitude images to include the lumen of the LVOT and of the aorta. The following measurements were performed within each ROI on matched phase images at LVOT and Ao positions.
The peak and average flow velocities within the ROI were used to determine the changes in instantaneous peak and average velocity (Vaverage) in the LVOT during the cardiac cycle. The instantaneous LVOT flow rate was calculated by multiplying the instantaneous Vaverage by the LVOT cross-sectional area.
The maximum through-plane flow velocity within the ROI was used to determine the instantaneous peak aortic velocity at Ao position. The mean transvalvular velocity was computed using instantaneous peak velocity values during systole (i.e. ejection period).
CMR valve hemodynamic parameters
Mean transvalvular pressure gradient (MGPCMR) was determined by simplified Bernoulli formula and valve EOA was calculated using jet shear layer detection method  from velocity field at Ao plane (i.e. 10 mm downstream of the aortic annulus). The same plane was used to compute energy loss (EL = Vpeak2 × [1 − EOACMR/AAo]2), where Vpeak2 is the systolic transvalvular aortic peak jet velocity and AAo is cross-sectional area of the ascending aorta. Systolic mean vorticity () was computed using a compact-Richardson interpolation scheme [27–29], absolute value was used to consider both clockwise and anti-clockwise effects. Briefly, compact-Richardson interpolation scheme estimates the partial velocity derivatives needed for the vorticity computation with reduced partial volume effects and local noise alterations using an iterative-weighted process. This vorticity method works with through-plane (single velocity component) and full volume (three velocity components, i.e. full vector) velocity data, and it has been previously validated in silico, in vitro and in vivo [27–29]. Furthermore Strouhal number (non-dimensional oscillating flow) was given by St = (Daverage//2) × (f/[/ [Vpeak − Vaverage]), where Daverage is the averaged systolic diameter of LVOT and f is the heart rate.
To assess the discordance between MPG obtained by CMR and MPG obtained by TTE, the MPG relative error (in %) was computed as follows: MPGerror = ([MPGTTE − MPGCMR]/] /MPGTTE) × 100. Absolute error differences (|∆MPG|) were classified in three groups: group A (|∆MPG| ≤ 10 mmHg), group B (10 mmHg < |∆MPG| < 20 mmHg) and group C (|∆MPG| ≥ 20 mmHg). Predicted MPGCMR-Gorlin was computed using Gorlin equation as follows: MPGCMR − Gorlin = (CO/[/ [HR × SEP × 44.3 × EOACMR])2[15, 16, 30], where CO is the cardiac output, HR is the heart rate and SEP is the systolic ejection period.
Results are expressed as mean ± SD. Comparisons between groups (healthy control subjects vs. moderate vs. severe AS or tricuspid vs. bicuspid valve) were performed with the use of Student t-tests or One-way ANOVA when appropriate. Association and agreement between variables were assessed by Pearson’s correlations and Bland-Altman methods, respectively. Multivariate linear regression analysis was performed to identify the factors independently associated with MPGerror and MPGTTE. We included in multivariate models age and AS severity defined by CMR (i.e. EOACMR or MPGCMR) and all variables with p-value<0.15 in univariate analysis. Standardized regression coefficients were presented as mean ± standard error (βeta coeff ± SE). Statistical analysis was performed with SPSS 17 (SPSS, Chicago, IL).
Comparison of clinical TTE and CMR data
34 ± 8
64 ± 15 *
Gender (men %)
Body surface area (m2)
1.93 ± 0.26
1.82 ± 0.19
Systolic arterial pressure (mmHg)
116 ± 10
132 ± 23
Diastolic arterial pressure (mmHg)
77 ± 5
72 ± 12
Doppler echocardiography data
Valve phenotype (bicuspid, %)
Aortic valve hemodynamics
Stroke volume (mL)
80 ± 20
80 ± 13
Mean transvalvular gradient (mmHg)
5 ± 1
20 ± 10 *
Valve effective orifice area (cm2)
2.67 ± 0.47
1.19 ± 0.28 *
Systemic arterial hemodynamics
Systemic arterial compliance (mL.m-2.mmHg-1)
1.06 ± 0.21
0.91 ± 0.32
Systemic vascular resistance (dyne.s.cm-5)
1448 ± 319
1515 ± 338
Cardiovascular magnetic resonance data
Aortic valve hemodynamics
Stroke volume (mL)
84 ± 14
76 ± 17
Mean transvalvular gradient (mmHg)
3 ± 1
12 ± 7 *
Valve effective orifice area (cm2)
3.08 ± 0.8
1.4 ± 0.41 *
Energy loss (mmHg)
3.33 ± 1.11
13.81 ± 7.99 *
Mean systolic vorticity (1/s)
88 ± 13
125 ± 35 *
0.0174 ± 0.0034
0.0087 ± 0.0029 *
Factors of the MPG underestimation by CMR
Univariate and multivariate determinants of relative error in transvalvular mean pressure gradient
Mean transvalvular pressure gradient
Relative error = MRI-TTE/TTE (%)
βeta coeff ± SE
βeta coeff ± SE
0.19 ± 0.19
Effective orifice area (cm2)*
−0.14 ± 4.66
−0.19 ± 809
−0.46 ± 934
Energy loss (mmHg)*
−0.33 ± 0.37
−0.41 ± 0.36
Mean systolic vorticity (1/s)*
−0.36 ± 0.09
−0.53 ± 0.08
TTE and CMR transvalvular mean pressure gradient prediction models
MPGCMR-Gorlin and MPGTTE measurements showed a good correlation and agreement, a reduced underestimation with higher limits of agreement than measured MPGCMR (r = 0.7 [Figure 2C]; bias = −2.8 mmHg, limits of agreement from −18.4 to 12.9 mmHg, [Figure 2D]). When considering |∆MPG| groups, group A had 76% (n = 52) of subjects, group B had 21% (n = 14) of subjects and group C had 3% (n = 2) of subjects.
Univariate and multivariate determinants of Doppler-echocardiography mean transvalvular pressure gradient
Doppler-Echocardiography mean transvalvular mean pressure gradient (mmHg)
βeta coeff ± SE
βeta coeff ± SE
Mean transvalvular pressure gradient (mmHg)*
0.73 ± 0.1
0.72 ± 0.19
Energy loss (mmHg)*
0.68 ± 0.09
−0.57 ± 224
−0.44 ± 202
Mean systolic vorticity*
0.48 ± 0.03
−0.21 ± 0.03
Where ω is the vorticity magnitude and St is the Strouhal number. MPGCMR-Predicted model showed better correlation with MPGTTE and a low overestimation with lower limits of agreement (r = 0.82 [Figure 2E]; bias = 0.5 mmHg, limits of agreement from −9.1 to 10.2 mmHg, [Figure 2F]) than measured MPGCMR and MPGCMR-Gorlin. When considering |∆MPG| groups, group A had 99% (n = 67) of subjects and group B had 1% (n = 1) of subjects.
The main findings of this study are: 1) Mean systolic vorticity and EL were the factors associated with the discrepancies between CMR and TTE for the measurement of MPG. 2) Flow vorticity may be used as a quantitative parameter of AS hemodynamic severity; 3) The introduction of a new MPGCMR-Predicted model based on mean vorticity and oscillating flow(Strouhal number) allowing a better correlation and agreement than MPGCMR-Gorlin.
MPGTTE underestimation by CMR is typically related to local signal loss, background noise, phase wrap and turbulence [7, 9–14, 31, 32]. However, as it was demonstrated with catheterization other hemodynamic parameters affect mean transvalvular pressure gradients measurements, mainly energy loss  and pressure recovery [18–22, 33]. Those explanations should also apply to CMR given the theoretical background of the measurements. Some previous studies used those similarities to estimate EOA with CMR [9, 10]. Reynolds number (ratio of the inertial/viscous forces) has been shown to be a dimensionless parameter contributing to the explanation of pressure gradient differences between TTE and catheterization in AS [34, 35]. However, it is mainly valid in steady flow conditions evaluating flow regimes (laminar or turbulent).
In this study, a predictive MPG model using Gorlin equation [15, 16, 30] and CMR measurements was used. MPGCMR-Gorlin reduced CMR-TTE bias differences but it showed important differences with AS severity increase (i.e. higher MPG) (Figure 2, panel C and D). It is important to notice that we used the Gorlin equation based on Minners et al. study  and preliminary reported results . However, it was been demonstrated that Gorlin equation have two small errors: 1) the use of mean flow instead of root-mean-square flow and 2) the use of the coefficient 44.3 instead of 50.5 . The original intent of Gorlin equation was to give an estimate of anatomic valve area (AVA) instead of EOA. Of interest, EOA represent better the aortic valve hemodynamic than AVA and similar AVA geometries could lead to different EOA, i.e. different AS severities .
Furthermore, energy loss was evaluated using CMR and was strongly associated to MPGerror, mean vorticity intensity and dimensionless oscillating flow. A recent substudy of SEAS cohort  showed the potential usefulness of energy loss, pressure recovery and energy loss coefficient ([EOA×AAo] / [AAo-EOA]) for AS severity assessment, highlighting the importance of this parameter unexplored in CMR. A more accurate evaluation of energy loss and vorticity may be computed using CMR 4D flow velocity measurements [29, 38–40].
The cohort and results presented in this study make part of an ongoing prospective study at our institution. Some of our previous works included a part or the integrity of the actual cohort exploring different topics. Briefly, our work comparing continuity equation EOA using TTE and CMR used 48% of the actual data , the introduction a novel EOA method with CMR used 57% , two closely related works exploring pressure gradient difference between TTE and CMR used 48% , and the same cohort . Finally, the cohort presented in this work was included in a more recent study evaluating the valve EOA kinetic in patients with AS . Patients with bicuspid valve showed a ratio close to 30% of the ongoing population.
In terms of methodology it is important to observe that the initial imaging work flow included measurements at 6 mm and 10 mm downstream from the aortic valve. Measurements at 6 mm showed to be slightly higher than those at 10 mm . However, 6 mm plane is unusual in clinical practice  and it was found none statistical difference between both velocity planes. So our work flow was modified in consequence. Parallel plane position to the aortic valve annulus may crucial for the adequate measurement of velocity gradients at vena contracta position, avoiding potential sources of velocity underestimation [4, 5, 8]. In particular the presence of high eccentric flow jets, often observed in patients with bicuspid aortic valves and aortic dilation, may contribute to pressure gradient underestimation [41, 42]. However, AS severity does not seem to be the only factor affecting flow jet eccentricity, complex rotatory flow patterns and velocity-related measurements [42, 43]. In this study non-statistical difference was found when comparing bicuspid vs. tricuspid MPG.
Vortex formation is currently visually evaluated for identifying abnormal flow patterns [41, 42, 44, 45]. However vorticity intensity provides a quantitative approach of vorticity and vortex formation. In this study MPG, EOA, energy loss, and Strouhal number (dimensionless oscillating flow) were significantly associated with mean vorticity. Vorticity was also used to compute EOA using vorticity jet shear layer detection method [5, 17, 29], this method may be more accurate than continuity equation and may be useful for differentiating pseudo-severe AS to truly-severe AS severity at rest or during dobutamine perfusion  given its high-accurate fluid mechanics approach, non-circular LVOT shape assumptions and/or stroke volume computation need. Vorticity intensity may provide useful additional information of aortic valve hemodynamics and AS severity.
Accurate estimation of valve vorticity magnitude is dependent on the temporal and spatial resolution (typically 30–40 ms per phase and 1–2 mm, respectively) which is essentially determined by patient’s heart rate, sequence design and echo time. In this study we use a vendor product flow sequence which automatically estimates the shorter TE, however TE was maybe not enough shorter to accurately measure peak velocities . New promising fast acquisition flow sequences and hardware (i.e. SENSE, image mapping, ultra-short echo time, and parallel imaging) could help overcoming these limitations. It is important to notice that vorticity was calculated using standard through-plane velocity measurements (i.e. a single velocity component). As presented in the discussion full velocity vector acquisition may provide a more accurate estimation of vorticity. The number of patients with AS and adverse events was too small (7 valve replacement surgeries) to determine the association between valve vorticity intensity with clinical outcomes.
In conclusion, this study showed that flow vorticity is one of the main factors responsible for the MPG discrepancies between CMR and TTE. It is possible to account for this factor and correct the MPG measured by CMR. Larger studies are needed to confirm the potential usefulness of CMR-derived vorticity and flow-derived parameters in cardiovascular diseases and valve function.
This work was supported by research grants of Natural Sciences and Engineering Research Council of Canada, Ottawa, Ontario, Canada (grant # 343165–07) and of the Canadian Institutes of Health Research (CIHR), Ottawa, Ontario, Canada (grant # 126072 and 114997). Dr. Pibarot holds the Canada Research Chair in Valvular Heart Diseases, CIHR. J. Garcia is supported by CONACYT (Mexico City, Mexico, grant 203355). Dr. Larose is a Clinical research scholar of the Fonds de la recherché en santé du Québec.
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