Open Access

Discrepancies between cardiovascular magnetic resonance and Doppler echocardiography in the measurement of transvalvular gradient in aortic stenosis: the effect of flow vorticity

Journal of Cardiovascular Magnetic Resonance201315:84

DOI: 10.1186/1532-429X-15-84

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 Echo-Doppler 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 [1]. 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 [1] 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 [36]. 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, 710]. 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, 1114].

Based on a recent study on the inconsistent grading of AS severity assessed by TTE and cardiac catheterization [15] it has been proposed to use Gorlin equation to correct the MPG disagreement between TTE and CMR measurements [16] leading to reasonable results in the evaluated population. From a fluid dynamic point-of-view, when the blood flows through the aortic valve it is spatially accelerated from the left ventricular outflow tract (LVOT) to the location of the vena contracta and it is then decelerated and diverges within the ascending aorta (Figure 1). This flow generates turbulence when the aortic valve is severely stenotic and an irreversible heat dissipation process. Several flow-derived parameters (energy loss, vorticity, and Strouhal number) may provide an insight on the presence and intensity of turbulence generated downstream of a severe AS [17]. All these flow parameters may be useful for identifying potential sources of discordance between MPG measured by CMR and TTE.
Figure 1

Fluid mechanics of the aortic valve. Schematic representation of the system composed of left ventricle, aortic valve and ascending aorta with corresponding static pressure (P) and energy in terms of total pressure (P+4 V2). LVOT indicates left ventricular outflow tract, V indicates LVOT velocity, AOA indicates anatomic aortic area and VC indicates the vena contracta position, cross-sectional area of VC corresponds to the valve effective orifice area. Magnetic resonance velocity measurements at vena contracta (10 mm from the aortic valve) were used to compute dimensionless flow parameters and vorticity magnitude. AAo indicates ascending aorta.

Energy loss (EL) represents the energetic cost (in mmHg) between the LVOT and the ascending aorta after pressure recovery [1822]. Vorticity intensity (ω) can be used to estimate the dissipation effects within the flow [23]. Interestingly, a recent study demonstrated that vorticity jet shear layer can also be used to estimate EOA using CMR velocity measurements [5]. Strouhal number (St) represents the dimensionless oscillating flow through the aortic valve [24].

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.


Study population

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.

Transthoracic Doppler-echocardiography

TTE studies were performed and analyzed by two experienced echocardiographers according to the American Society of Echocardiography guidelines [25] and included:
  1. 1)

    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);

  2. 2)

    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 [5] 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 ( ω t = V t x V t y was computed using a compact-Richardson interpolation scheme [2729], 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 [2729]. 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.

Statistical analyses

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).


Sixty patients with mild to severe AS (65% men, age 64±15 years) and eight healthy subjects (75% men, age 34±8 years) were included in this study. The demographic, TTE and CMR data of the patients with AS and the healthy subjects are presented in Table 1. Valve morphology was bicuspid in 27% of AS patients. Age, MPG, EL, vorticity, and Strouhal number were significantly higher in AS patients compared with healthy control subjects. When comparing AS severity groups with healthy control subjects a significant difference was found for AS severity indices, EL, vorticity, and Strouhal number. There was a significant difference (p<0.05) between aortic valve phenotype (i.e. bicuspid vs. tricuspid aortic valves) for age, systolic arterial pressure, and systemic compliance.
Table 1

Comparison of clinical TTE and CMR data


Healthy subjects

AS patients

(n=8, mean±SD)

(n=60, mean±SD)

Patient demographics


Age (years)

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 (

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 *

*:p<0.001 with healthy.

Factors of the MPG underestimation by CMR

MPGCMR underestimated MPGTTE and this underestimation increased with AS severity (r = 0.73 [Figure 2A]; bias = −6.5 mmHg, limits of agreement from −18.3 to 5.2 mmHg, [Figure 2B], Table 1). Comparison between MPGCMR and MPGTTE was significantly different for all categories (p<0.001). When considering |∆MPG| groups, group A had 78% (n = 53) of subjects, group B had 21% (n = 14) of subjects and group Chad 1% (n = 1) of subjects. Vorticity (p = 0.003), EL (p = 0.006) and Strouhal number (p = 0.123) were significantly related to MPGerror (Table 2). In the multivariate analysis, after adjustment for EOACMR and age, EL, Strouhal number and vorticity were the factors independently associated with higher MPGerror (Table 2).
Figure 2

Comparison of mean transvalvular pressure gradients measured by TTE versus by CMR. Panel A shows the Pearson correlation plot for mean transvalvular pressure gradient measured by TTE (MPGTTE) and CMR (MPGCMR). Panel B shows the corresponding Bland-Altman plot. Panel C shows the Pearson correlation plot for mean transvalvular pressure gradient measured by TTE (MPGTTE) and predicted by Gorlin equation using CMR (MPGCMR-Gorlin). Panel D shows the corresponding Bland-Altman plot. Panel E shows the Pearson correlation plot for mean transvalvular pressure gradient measured by TTE (MPGTTE) and predicted model using vorticity and dimensionless stroke volume from CMR (MPGCMR-Predicted). Panel F shows the corresponding Bland-Altman plot.

Table 2

Univariate and multivariate determinants of relative error in transvalvular mean pressure gradient

Mean transvalvular pressure gradient

Univariate analysis

Multivariate model

Relative error = MRI-TTE/TTE (%)

βeta coeff ± SE


βeta coeff ± SE


Age (years)

0.19 ± 0.19




Effective orifice area (cm2)*

−0.14 ± 4.66




Strouhal number*

−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


Legend: *Parameters computed from CMR. Multivariate model includes only variables that were significantly (p<0.15) associated with transvalvular mean pressure gradient relative error on univariate analysis. Βeta coeff ± SE were standardized regression coefficients ± standard error.

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.

Independent factors associated to MPGerror were included, avoiding redundancies, in a multivariate analysis for MPGTTE adjusted to MPGCMR; all the parameters included were significantly associated in the univariate analysis (p < 0.001, see Table 3).
Table 3

Univariate and multivariate determinants of Doppler-echocardiography mean transvalvular pressure gradient

Doppler-Echocardiography mean transvalvular mean pressure gradient (mmHg)

Univariate analysis

Multivariate model

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




Strouhal number*

−0.57 ± 224


−0.44 ± 202


Mean systolic vorticity*

0.48 ± 0.03


−0.21 ± 0.03


Legend: *Parameters measured by CMR. Multivariate model includes only variables that were significantly (p < 0.001) associated with echo-Doppler transvalvular mean pressure gradient on univariate analysis. Βeta coeff ± SE were standardized regression coefficients ± standard error.

In this multivariate analysis MPGCMR, Strouhal number and mean vorticity were independently associated to MPGTTE. We have introduced a new MPGCMR-Predicted model based in the previous multivariate analysis presented in Table 3:
MP G CMR Predicted = 24 0.05 × mean ω + 0.85 × MP G CMR 960 × St

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, 914, 31, 32]. However, as it was demonstrated with catheterization other hemodynamic parameters affect mean transvalvular pressure gradients measurements, mainly energy loss [21] and pressure recovery [1822, 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 [15] and preliminary reported results [16]. 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 [36]. 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 [37].

A new predictive model based on vorticity and dimensionless oscillating flow (Strouhal number) was evaluated and led to a better MPG estimation from CMR (Figure 2, panel C and D). The new MPGCMR-Predited model introduced in this study showed that MPG can be accurately estimated by CMR and allowed to support the use of CMR as corroboration imaging technique for AS severity [3, 4, 8]. It may be also useful in the management of inconsistent severity grading (Figure 3), a current scenario between TTE and cardiac catheterization [15], and as it is demonstrated in this study (Table 2, Figure 3A), between TTE and CMR. Inconsistencies on EOA and MPG measurements may lead to incorrect therapeutic/surgical decisions. It is important to avoid measurement inconsistencies as reported with cardiac catheterization and define consistent cut-offs (EOA and pressure gradients) valid on all imaging techniques used to assess AS severity.
Figure 3

Effective orifice area and mean transvalvular pressure gradients. Panel A shows the aortic valve effective orifice area and mean transvalvular pressure gradient (MPG) plot using measurements from TTE (MPGTTE) and CMR (MPGCMR). Panel B shows the same plot but using MPG predicted by Gorlin equation and CMR measurements (MPGCMR-Gorlin). Panel C shows the same plot but using MPG predicted using mean vorticity magnitude and dimensionless stroke volume from CMR measurements (MPGCMR-Predicted).

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 [22] 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, 3840].

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 [3], the introduction a novel EOA method with CMR used 57% [5], two closely related works exploring pressure gradient difference between TTE and CMR used 48% [16], and the same cohort [17]. Finally, the cohort presented in this work was included in a more recent study evaluating the valve EOA kinetic in patients with AS [6]. 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 [3]. However, 6 mm plane is unusual in clinical practice [4] 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 [23] 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.

Study limitations

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 [14]. 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.

Authors’ Affiliations

Québec Heart and Lung Institute, Laval University
Laboratory of Cardiovascular Fluid Dynamics, Concordia University
Department of Radiology, Northwestern University
Department of Mechanical Engineering, McGill University


  1. Bonow RO, Carabello BA, Chatterjee K: 2008 Focused update incorporated into the ACC/AHA 2006 guidelines for the management of patients with valvular heart disease: a report of the American College of Cardiology/American Heart Association Task Force on Practice Guidelines. Circulation. 2008, 118: e523-661.View ArticlePubMed
  2. Vahanian A, Alfieri O, Andreotti F: Guidelines on the management of valvular heart disease. Eur Heart J. 2012, 33: 245-96.
  3. Garcia J, Kadem L, Larose E, Clavel M-A, Pibarot P: Comparison between cardiovascular magnetic resonance and transthoracic doppler echocardiography for the estimation of effective orifice area in aortic stenosis. J Cardiovasc Magn Reson. 2011, 13: 25-10.1186/1532-429X-13-25.PubMed CentralView ArticlePubMed
  4. Caruthers SD, Lin SJ, Brown P, Watkins MP, Williams TA, Lehr KA, Wickline SA: Practical value of cardiac magnetic resonance imaging for clinical quantification of aortic valve stenosis: comparison with echocardiography. Circulation. 2003, 108: 2236-43. 10.1161/01.CIR.0000095268.47282.A1.View ArticlePubMed
  5. Garcia J, Marrufo OR, Rodriguez AO, Larose E, Pibarot P, Kadem L: Cardiovascular magnetic resonance evaluation of aortic stenosis severity using single plane measurement of effective orifice area. J Cardiovasc Magn Reson. 2012, 14: 23-10.1186/1532-429X-14-23.PubMed CentralView ArticlePubMed
  6. Garcia J, Pibarot P, Capoulade R, Le Ven F, Kadem L, Larose E: Usefulness of cardiovascular magnetic resonance imaging for the evaluation of valve opening and closing kinetics in aortic stenosis. Eur Heart J CardiovascImaging. 2013, 14: 819-26.View Article
  7. Kilner P, Firmin D, Rees R: Valve and great vessel stenosis: assessment with MR jet velocity mapping. Radiology. 1991, 178: 229-35.View ArticlePubMed
  8. Cawley PJ, Maki JH, Otto CM: Cardiovascular magnetic resonance imaging for valvular heart disease: technique and validation. Circulation. 2009, 119: 468-78. 10.1161/CIRCULATIONAHA.107.742486.View ArticlePubMed
  9. Sondergaard L, Hildebrandt P, Lindvig K, Thomsen C, Ståhlberg F, Kassis E, Henriksen O: Valve area and cardiac output in aortic stenosis: quantification by magnetic resonance velocity mapping. Am Heart J. 1993, 126: 1156-64. 10.1016/0002-8703(93)90669-Z.View ArticlePubMed
  10. Eichenberger AC, Jenni R, Von Schulthess GK: Aortic valve pressure gradients in patients with aortic valve stenosis: quantification with velocity-encoded cine MR imaging. AJR Am J Roentgenol. 1993, 160: 971-77. 10.2214/ajr.160.5.8470612.View ArticlePubMed
  11. Gao JH, Gore JO: Turbulent flow effects on NMR imaging: measurement of turbulent intensity. Med Phys. 1991, 18: 1045-51. 10.1118/1.596645.View ArticlePubMed
  12. Kilner PJ, Manzara CC, Mohiaddin RH: Magnetic resonance jet velocity mapping in mitral and aortic valve stenosis. Circulation. 1993, 87: 1239-48. 10.1161/01.CIR.87.4.1239.View ArticlePubMed
  13. Kuethe DO, Gao JH: NMR signal loss from turbulence: models of time dependence compared with data. Phys RevE. 1995, 51: 3252-62.
  14. O’Brien KR, Cowan BR, Jain M, Stewart RAH, Kerr AJ, Young AA: MRI phase contrast velocity and flow errors in turbulent stenotic jets. J Magn Reson Imaging. 2008, 28: 210-18. 10.1002/jmri.21395.View ArticlePubMed
  15. Minners J, Allgeier M, Gohlke-Baerwolf C, Kienzle R-P, Neumann F-J, Jander N: Inconsistencies of echocardiographic criteria for the grading of aortic valve stenosis. Eur Heart J. 2008, 29: 1043-48. 10.1093/eurheartj/ehm543.View ArticlePubMed
  16. Garcia J, Kadem L, Larose E, Pibarot P: Disagreement between Cardiovascular Magnetic Resonance and Echo-Doppler Transvalvular Pressure Gradients. Proceedings of the 19th Annual Meeting of ISMRM. 2011, Montreal, Canada, 1209
  17. Garcia J, Capoulade R, Kadem L, Larose E, Pibarot P: New insights in the disagreement of transvalvular mean pressure gradient measured by transthoracic echo-Doppler and cardiovascular magnetic resonance in patients with aortic stenosis. Proceedings of the 21th Annual Meeting of ISMRM. 2013, Salt Lake City, USA, 64
  18. Voelker W, Reul H, Stelzer T, Schmidt A, Karsch KR: Pressure recovery in aortic stenosis: an in vitro study in a pulsatile flow model. J Am Coll Cardiol. 1992, 20: 1585-93. 10.1016/0735-1097(92)90454-U.View ArticlePubMed
  19. Baumgartner H, Stefenelli T, Niederberger J, Schima H, Maurer G: “ Overestimation ” of catheter gradients by doppler ultrasound in patients with aortic stenosis: a predictable manifestation of pressure recovery. J Am Coll Cardiol. 1999, 33: 1655-61. 10.1016/S0735-1097(99)00066-2.View ArticlePubMed
  20. Niederberger J, Schima H, Maurer G, Baumgartner H: Importance of pressure recovery for the assessment of aortic stenosis by Doppler ultrasound. Role of aortic size, aortic valve area, and direction of the stenotic jet in vitro. Circulation. 1996, 94: 1934-40. 10.1161/01.CIR.94.8.1934.View ArticlePubMed
  21. Garcia D, Pibarot P, Dumesnil JG, Sakr F, Durand L-G: Assessment of aortic valve stenosis severity a new index based on the energy loss concept. Circulation. 2000, 101: 765-71. 10.1161/01.CIR.101.7.765.View ArticlePubMed
  22. Bahlmann E, Cramariuc D, Gerdts E: Impact of pressure recovery on echocardiographic assessment of asymptomatic aortic stenosis: a SEAS substudy. JACC Cardiovasc Imaging. 2010, 3: 555-62. 10.1016/j.jcmg.2009.11.019.View ArticlePubMed
  23. Kadem L, Rieu R, Dumesnil JG, Durand L-G, Pibarot P: Flow-dependent changes in Doppler-derived aortic valve effective orifice area are real and not due to artifact. J Am Coll Cardiol. 2006, 47: 131-37. 10.1016/j.jacc.2005.05.100.View ArticlePubMed
  24. Strouhal V: Ueber eine besondere Art der Tonerregung. Annalen der Physik und Chemie. 1878, 241: 216-51. 10.1002/andp.18782411005.View Article
  25. Baumgartner H, Hung J, Bermejo J: Echocardiographic assessment of valve stenosis: EAE/ASE recommendations for clinical practice. J Am Soc Echocardiogr. 2009, 22: 1-23. 10.1016/j.echo.2008.11.029.View ArticlePubMed
  26. Garcia J, Kadem L, Larose E, Pibarot P: In vivo velocity and flow errors quantification by phase-contrast magnetic resonance imaging. Conf Proc IEEE Eng Med Biol Soc. 2008, 2008: 1377-80.PubMed
  27. Etebari A, Vlachos PP: Improvements on the accuracy of derivative estimation from DPIV velocity measurements. Exp Fluids. 2005, 39: 1040-50. 10.1007/s00348-005-0037-1.View Article
  28. Garcia J, Larose É, Pibarot P, Kadem L: On the evaluation of vorticity using cardiovascular magnetic resonance velocity measurements. J Biomech Eng. 2013, doi: 10.1115/1.4025385
  29. Garcia J, Barker AJ, Schnell S, Entezari P, Mahadevia R, Pibarot P, Carr JC, Markl M: 4D flow jet shear layer detection method for the measurement of effective orifice area and assessment of aortic stenosis severity. J Cardiovasc Magn Reson. 2013, 15 (Suppl 1): P241-PubMed Central
  30. Gorlin R, Gorlin S: Hydraulic formula for calculation of the area of the stenotic mitral valve, other cardiac valves, and central circulatory shunts. Am Heart J. 1951, 41: 1-29. 10.1016/0002-8703(51)90002-6.View ArticlePubMed
  31. Kuethe DO: Measuring distributions of diffusivity in turbulent fluids with magnetic-resonance imaging. Phys Rev A. 1989, 40: 4542-51. 10.1103/PhysRevA.40.4542.View ArticlePubMed
  32. Oshinski JN, Ku DN, Pettigrew RI: Turbulent fluctuation velocity: the most significant determinant of signal loss in stenotic vessels. Magn Reson Med. 1995, 33: 193-99. 10.1002/mrm.1910330208.View ArticlePubMed
  33. Garcia D, Dumesnil JG, Durand L-G, Kadem L, Pibarot P: Discrepancies between catheter and Doppler estimates of valve effective orifice area can be predicted from the pressure recovery phenomenon. J Am Coll Cardiol. 2003, 41: 435-42.View ArticlePubMed
  34. Adams JC, Jiamsripong P, Belohlavek M: Potential role of Reynolds number in resolving Doppler- and catheter-based transvalvular gradient discrepancies in aortic stenosis. J Heart Valve Dis. 2011, 20: 159-64.PubMed
  35. Cape EG, Jones M, Yamada I, VanAuker MD, Valdes-Cruz LM: Turbulent/viscous interactions control Doppler/catheter pressure discrepancies in aortic stenosis. The role of the Reynolds number. Circulation. 1996, 94: 2975-81. 10.1161/01.CIR.94.11.2975.View ArticlePubMed
  36. Dumesnil J, Yoganathan AP: Theoretical and practical differences between the Gorlin formula and the continuity equation for calculating aortic and mitral valve areas. Am JCardiol. 1991, 67: 1268-72. 10.1016/0002-9149(91)90939-I.View Article
  37. Pibarot P, Larose E: What our eyes see is not necessarily what our heart feels. Cardiology. 2008, 109: 122-25. 10.1159/000105553.View ArticlePubMed
  38. Dyverfeldt P, Hope MD, Tseng EE, Saloner D: Magnetic resonance measurement of turbulent kinetic energy for the estimation of irreversible pressure loss in aortic stenosis. JACC. Cardiovasc imaging. 2013, 6: 64-71. 10.1016/j.jcmg.2012.07.017.PubMed CentralView ArticlePubMed
  39. Barker AJ, van Ooij P, Bandi K, Garcia J, Mccarthy P, Carr J, Malaisrie C, Markl M: Viscous energy loss in aortic valve disease patients. Proceedings of the ASME Summer Bioengineering Conference. 2013, Sunriver, USA, 14142-
  40. Garcia J, Markl M, Schnell S, Entezari P, Mahadevia R, Wu C, Malaisrie SC, Pibarot P, Carr J, Barker AJ: A novel method for the assessment of valve effective orifice area using 4D flow shear layer detection method in patients with aortic stenosis. Proceedings of the 21th Annual Meeting of ISMRM. 2013, Salt Lake City, USA, 1329-
  41. Barker AJ, Markl M, Bürk J, Lorenz R, Bock J, Bauer S, Schulz-Menger J, von Knobelsdorff-Brenkenhoff F: Bicuspid aortic valve is associated with altered wall shear stress in the ascending aorta. Circulation cardiovasc imaging. 2012, 5: 457-66. 10.1161/CIRCIMAGING.112.973370.View Article
  42. Bissell MM, Hess AT, Biasiolli L: Aortic dilation in bicuspid aortic valve disease: flow pattern is a major contributor and differs with valve fusion type. Circulation cardiovasc imaging. 2013, 6: 499-507. 10.1161/CIRCIMAGING.113.000528.View Article
  43. Garcia J, Kadem L, Larose É, Pibarot P: Assessment of Transvalvular Flow Jet Eccentricity in Aortic Stenosis. Proceedings of 20th Annual Meeting of ISMRM. 2012, Melbourne, Australia, 1186-
  44. Frydrychowicz A, Harloff A, Jung B: Time-resolved, 3-dimensional magnetic resonance flow analysis at 3 T: visualization of normal and pathological aortic vascular hemodynamics. J Comput Assist Tomogr. 2007, 31: 9-15. 10.1097/01.rct.0000232918.45158.c9.View ArticlePubMed
  45. Sengupta PP, Pedrizzetti G, Kilner PJ, Kheradvar A, Ebbers T, Tonti G, Fraser AG, Narula J: Emerging trends in CV flow visualization. JACC Cardiovasc Imaging. 2012, 5: 305-16. 10.1016/j.jcmg.2012.01.003.View ArticlePubMed


© Garcia et al.; licensee BioMed Central Ltd. 2013

This article is published under license to BioMed Central Ltd. This is an Open Access article distributed under the terms of the Creative Commons Attribution License (http://​creativecommons.​org/​licenses/​by/​2.​0), which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.