DIAGNOSIS OF MITRAL REGURGITATION

Echo-Doppler is an extremely sensitive tool for the detection of MR. Indeed, trivial or mild MR can be seen in 20–40% of subjects with structurally normal hearts^3–5 and is of no clinical significance.

If significant MR is detected it is important not only to make an assessment of severity but also to make a judgement on the underlying cause. Careful inspection of the leaflet and subvalvar anatomy, along with the morphology and function of the left ventricle and papillary muscles, is required. From the list of conditions in table 1 it is evident that MR may be caused by either primary valvar pathology such as congenital heart disease, rheumatic heart disease or myxomatous degeneration, or secondary to miscellaneous pathologies such as mitral annular dilatation and/or left ventricular regional wall dysfunction (so-called “functional MR”). Defining the cause of the regurgitation is extremely important to guide further management of the patient. Primary valve pathologies will generally require valve repair or replacement when symptoms and/or haemodynamics dictate, whereas functional MR may respond to medical treatment of the underlying ventricular pathology, mitral annuloplasty or possibly revascularisation in the case of ischaemic left ventricular dysfunction.

Before discussing the pathologies affecting the mitral valve it is necessary to review the normal structure and function of the valve.

NORMAL MITRAL VALVE STRUCTURE AND FUNCTION

The normal mitral valve is a complex structure that relies on a precise interaction of all its components for normal function. The valve comprises the anterior and posterior leaflets, the subvalvar apparatus (chordae tendineae and papillary muscles), and the fibrous annulus. Failure of the normal function of any of these components may lead to regurgitation. Normal function of the regional walls of the left ventricle into which the papillary muscles insert is also required for valve competency. Figure 1 shows the structure of the mitral leaflets viewed from their superior aspect. The anterior mitral leaflet is a relatively long, semicircular structure. While the posterior leaflet is comparatively short in its leaflet edge to annulus dimension, it has a more extensive area of insertion to the annulus than the anterior leaflet. This fact is not readily appreciable on two dimensional echocardiographic imaging, where longitudinal cuts through the valve demonstrate leaflet width rather than area. For descriptive purposes discussed further below, both leaflets are subdivided into three components (fig 1).

The chordae tendineae arise from the tips of the anterolateral and posteromedial papillary muscles and run to the free edges and body of the valve leaflets. Chords from the posteromedial muscle supply the medial half of both anterior and posterior leaflets, while those from the anterolateral muscle supply their lateral halves. As the chords are fixed in length, it is vital that the correct relationship is maintained between the leaflet edges and the papillary muscles to ensure that normal coaptation occurs. Any pathology affecting the structure and function of the papillary muscles or indeed their adjacent left ventricular walls may therefore produce valve dysfunction.

PRIMARY MITRAL VALVE PATHOLOGY

Rheumatic valve disease

The echocardiographic features of rheumatic MR are generally easy to recognise. Thickening and calcification of the leaflet tissue and subvalvar apparatus with restricted leaflet motion are typical findings. Commissural fusion is commonly seen and there is usually a combination of mitral stenosis and regurgitation to varying degrees. A further clue may be involvement of other valves, most commonly the aortic.

Mitral valve leaflet prolapse

Mitral prolapse is most commonly caused by myxomatous degeneration of the valve leaflets and chordae tendineae. The leaflets become thickened and large amounts of redundant tissue may be present. Chordal elongation and rupture prevent normal apposition of the leaflet tips, and may produce valvar regurgitation of varying degrees. Less commonly, prolapse may result from direct damage to the papillary muscles or to the chordae through infarction or infection.

The echocardiographic diagnosis of mitral valve prolapse has historically been a contentious issue with a variety of definitions put forward. This lack of consensus has led to a wide range of reported prevalence of the condition (5–15%).^6,7 More recently, echocardiographic diagnostic criteria have been refined in the light of enhanced understanding of the three dimensional shape and motion of the mitral annulus.^8–10 This has led to the introduction of the concept of “classic” mitral valve prolapse. Classic prolapse is defined as a maximum superior displacement of one or both mitral leaflets of ≥ 2 mm relative to the line connecting the annular hinge points during systole, and a maximum leaflet thickness of ≥ 5 mm. In addition, “non-classic” prolapse is also described, with maximum displacement of ≥ 2 mm but a leaflet thickness < 5 mm. Subjects with classic prolapse are at higher risk of complications than those with the non-classic form.¹¹ Using these criteria, Freed and colleagues studied the transthoracic echocardiograms of 3500 subjects of the offspring cohort of the Framingham heart study. They showed a prevalence of 2.4% of mitral prolapse with approximately equal numbers of classic and non-classic forms.¹²

Of note is the fact that these criteria do not include an assessment of displacement of the coaptation point of the valve leaflets relative to the line connecting the annular hinge points. While previously proposed as an indicator of prolapse, posterior displacement of the coaptation point is not seen in the majority of subjects with classic and non-classic bileaflet prolapse.¹³ It is not therefore included in these most recent diagnostic criteria.

Prolapse may involve the entire leaflet or only a portion thereof. It is important to accurately define the extent of the leaflet involved in the prolapse, as this has implications for subsequent surgical management. While it may be possible to estimate the extent of involvement by transthoracic imaging, it is generally accepted that transoesophageal echocardiography is superior for this purpose¹⁴ (fig 1).

FUNCTIONAL MITRAL REGURGITATION

Mitral regurgitation may occur secondary to pathology outwith the mitral leaflets.^15,16 Dilatation of the left ventricle will lead to a stretch of the mitral valve annulus. If the annulus dilates to the point where complete leaflet coaptation is not possible, a leak will result usually producing a central jet of MR. A wall motion abnormality affecting the anterolateral or posteromedial left ventricular walls with or without direct papillary muscle involvement may also have an effect on mitral valve competency. Normal functioning of the valve relies on normal contraction of both the papillary muscles and the myocardium at their areas of insertion. Many authors describe the entity of papillary muscle dysfunction, but it is extremely unusual to see chronic, isolated dysfunction of these structures without involvement of the neighbouring myocardium. Normal myocardial contraction reduces the dimensions of both the short and long axes of the left ventricle and ensures that the correct relation between papillary muscles and leaflets is maintained during systole. An abnormality of systolic function of the regional left ventricular wall adjacent to a papillary muscle caused by ischaemia or infarction will impede this motion. The tip of the leaflet supplied by the papillary muscle will not be able to move back to its correct coaptation point and regurgitation will occur in an eccentric fashion behind the restricted leaflet. Dilatation of the left ventricle will produce displacement and restriction of motion of both papillary muscles which will add to the effects of annular dilatation in producing valvar regurgitation.

In some patients with functional MR secondary to ischaemic heart disease, the degree of regurgitation may increase during exercise since the resulting ischaemia will produce further deterioration in regional or global ventricular function. This “dynamic” regurgitation must be considered when assessing such patients.

QUANTIFICATION OF MITRAL REGURGITATION

Grading of severity

As indicated above, in the majority of cases of MR a semi-quantitative estimate of the severity is sufficient for clinical purposes. It is customary to grade the lesion on a spectrum between mild and severe. A grading of severe indicates a large regurgitant volume, implying that the lesion is of major haemodynamic significance and may require surgical correction. A pragmatist might even argue that the only question to be answered is whether the regurgitation is severe or non-severe, since recommendations for surgical intervention are limited to the former group. Generally, however, an experienced sonographer will use several parameters to make an assessment of mild, moderate or severe regurgitation. Since this is a subjective assessment there will be a degree of variability between individual observers and institutions. Interobserver variability can, however, be minimised within individual institutions by the development of clear grading guidelines using the principles outlined below. It is advisable to keep the grading system as simple as possible, and there is little to be gained by broadening the range to include “mild to moderate” or “moderately severe”.

Colour Doppler regurgitant jet dimensions

Colour Doppler regurgitant jet length and/or area has been used by a number of investigators to provide a semi-quantitative measure of MR severity. To do so requires an assumption that the size of the jet is proportional to the regurgitant volume passing through the valve. It should be remembered, however, that the colour jet is a velocity map whose extent reflects the velocity of regurgitant flow at any moment rather than the absolute regurgitant volume at that point in time. It cannot therefore be regarded as the direct ultrasonic equivalent of a radiographic contrast angiogram. Despite this observation, the relation between colour jet dimensions and regurgitation severity has been demonstrated in several studies,^17–19 but it must be pointed out that those studies demonstrating the best correlations related to “free” or unconstrained flows under strictly controlled flow conditions. Clinical studies indicate that the area of a free regurgitant jet averaged from multiple planes correlates well with angiographic grade of severity, and appears to be more robust than jet length alone.¹⁸ Correction of jet area for atrial area has also been studied and may improve accuracy. Helmcke¹⁸ demonstrated that jet areas of < 20%, 20–40%, and > 40% of left atrial area predicted mild, moderate, and severe angiographic regurgitation, respectively. Such figures must be treated with caution, however, since atrial size is inherently linked to atrial pressure and compliance, both of which may themselves affect jet area (see below).

The relation between jet area and regurgitant volume becomes more tenuous when the effects of flow constraint by the atrial walls come into play. In the case of an eccentric jet of regurgitation, the jet will tend to travel across the floor and wall of the atrium rather than expanding freely into the centre of the chamber. Projected against the wall in this way, the eccentric jet cannot expand like a free jet and preferentially spreads outwards across the wall with a thin dimension perpendicular to the wall (the so-called Coanda effect). A number of studies have shown that these “wall jets” have smaller jet areas by colour flow mapping in conventional echocardiographic views than do free or unconstrained jets of the same regurgitant volume.^20–22 This observation must be taken into account when using colour Doppler jet size to grade the severity of eccentric MR.

The size of the colour jet may also be influenced by any factor which affects the measured or displayed velocity of regurgitant flow (table 2). Such factors include instrument settings, transducer position, left atrial pressure and compliance, and left ventricular pressure and systolic function.²³ Any or all of these may conspire to lead the unwary to the wrong conclusion regarding lesion severity. For example, high left ventricular pressures (caused by hypertension or co-existing aortic stenosis, for example) will produce high energy and hence high velocity jets of MR. Such jets will occupy a larger area than might be expected for any given degree of regurgitation, and this must be considered when reporting the severity of the lesion. A patient with acute, severe MR may display a relatively small area jet on colour flow mapping since in this situation left atrial pressures are high because of limited compliance of the receiving chamber.

Clearly therefore the use of colour jet dimensions to quantify MR must be undertaken with caution. In certain situations there is no doubt about the severity grade—a broad jet extending all the way back to the rear of the atrium is strongly suggestive of a severe leak. In other cases, especially in the case of eccentric jets, the situation may be less clear and several other parameters may be used to help determine severity. Most experienced sonographers will make an “eyeball” assessment of the size and extent of the regurgitant jet in a number of views. Formal measurement of jet area is generally not required. They will then give an indication of severity taking into account the above caveats. If doubt regarding severity remains, certain other qualitative parameters are available as adjuncts to aid in the assessment.

Spectral Doppler

The continuous wave Doppler envelope of the MR signal can provide clues to lesion severity.²⁴ As the intensity of the Doppler signal is proportionate to the number of scatterers (that is, red blood cells) in the beam, severe lesions with large regurgitant volumes will generally produce high intensity Doppler envelopes. Conversely, the envelope in mild regurgitation will be fainter. Clearly, adequate beam alignment with the regurgitant flow is vital to make such observations valid.

Pulmonary vein flow

Examination of pulmonary vein flow by pulsed wave Doppler can be useful in the assessment of MR severity.^25,26 Rising left atrial pressure caused by significant regurgitation can cause a decrease in the normal forward flow through the pulmonary veins in late systole. Complete reversal of systolic flow may occur in severe MR, and is a useful indicator of its presence. Depending on the direction of the regurgitant jet, flow reversal may be seen in a single pulmonary vein, in the two left or the two right sided veins, or in all four veins.

While pulmonary vein flow may be imaged by transthoracic echocardiography, transoesophageal imaging allows consistent measurement of flow velocities in all four pulmonary veins and is the imaging modality of choice for this purpose.

Formal quantitative assessment

On occasion there may still be uncertainty regarding lesion severity. In these situations a formal quantitative assessment may be useful. Three entities may be quantified—regurgitant volume, regurgitant fraction, and effective regurgitant orifice area (EROA). Table 3 lists the definitions and method of quantification of all three. Any or all of these parameters may be quantified, but we recommend the use of EROA as the concept of orifice area is one which is familiar to cardiac sonographers. Regurgitant volume may be a useful measure for serial follow up in an individual patient, but the absolute volume per se is unlikely to be a reliable guide to severity as it is dependent on haemodynamic variables and chamber size. Expressing the regurgitant volume as a ratio of total mitral inflow volume is a more standardised measure. Table 4 indicates the range of regurgitant fraction and EROA corresponding to conventional angiographic grades of regurgitation. Quantification of these parameters may be performed in two ways.

Quantitative Doppler

This technique allows calculation of volumetric flow at various points within the heart. For example, table 3 indicates that if mitral inflow and left ventricular outflow volumes can be calculated, then mitral regurgitant volume and fraction may be computed. If the velocity time integral of the regurgitant flow is also measured, EROA may be calculated. This is analogous to calculation of aortic valve area by the continuity equation which is itself an implementation of quantitative Doppler.

A detailed description of quantitative Doppler methodology has recently been published by the American Society of Echocardiography.²⁷ The technique is based on the principle that volume flow rate is equal to the product of the cross sectional surface area available for flow at any point in a flow system and the velocity of flow at that surface. Depending on the parameters measured, instantaneous volume flow rate or stroke volume (that is, the volume passing through the selected surface in one cardiac cycle) can be calculated as shown in fig 2.

This principle may be applied to the mitral annulus and the left ventricular outflow tract (LVOT) to calculate mitral valve diastolic inflow and LVOT systolic outflow, respectively, and hence mitral regurgitant volume and EROA (fig 3). Mitral annular area is calculated by measuring the diameter of the mitral annulus in the apical 4 chamber view during diastole and assuming circular cross section. Although the mitral annulus is not perfectly circular, it has been shown that an assumption of circular geometry yields satisfactory results in this context. Mitral annular velocity time integral (VTI) is measured by placing the PW Doppler sample volume at the level of the annulus as shown. Clearly it must be assumed that the velocity data measured at that point reflect the velocities across the entire annular plane (that is, that the flow profile is flat), but it also appears that this assumption yields satisfactory accuracy. The area of the LVOT is calculated by measuring its diameter in the parasternal long axis view and assuming circular geometry. VTI data are collected in the apical five chamber view with the PW sample volume placed at the same level in the LVOT as the previous diameter measurement. Finally, the VTI of the mitral regurgitant signal itself must also be recorded by CW Doppler from the apical 4 chamber view.

Quantitative Doppler calculations are therefore time consuming and require skill and expertise for their implementation. Incorrect diameter measurements will produce large errors since the value must be squared to generate the cross sectional area. Several measurements of each parameter (B mode and Doppler) should be made and averaged to minimise error. In addition the calculation will not be valid in the presence of significant aortic regurgitation. In experienced hands, however, quantitative Doppler provides data of sufficient accuracy for clinical use and is generally regarded as the gold standard echo Doppler technique for quantification of valvar regurgitation.^28,29

Flow convergence method

The flow convergence (FC) method provides an alternative to quantitative Doppler for the calculation of EROA. It refers to the organised area of flow just proximal to the regurgitant orifice.³⁰ This is a more attractive option for flow quantification than the turbulent and disorganised regurgitant jet. The FC principle is best understood by considering the theoretical example of a flow field approaching a point orifice on a flat plate. As flow converges on the orifice, it accelerates along a series of multidirectional streamlines (fig 4) to reach maximum velocity at the orifice itself. If colour Doppler is used to image the flow field, it will be found that the velocity of flow will exceed the first colour Doppler aliasing velocity (v cm/s) at a certain distance r cm from the orifice. At this point an abrupt colour change will occur. In the case of a point orifice, each flow streamline will exceed the aliasing velocity at the same distance (r cm) from the orifice as shown. Two dimensional colour Doppler imaging of the flow field will therefore show an arc of abrupt colour change of radius r cm overlying the orifice. As the flow continues to accelerate towards the orifice, further arcs of progressively smaller radii will appear each time the velocity exceeds a multiple of the aliasing threshold.

Since flow approaches the orifice from all directions, in three dimensional space each arc in our point orifice model will appear as a hemisphere of radius r cm (fig 4). This “structure” is known as the region of flow convergence, and its physical area can be calculated as 2πr² (surface area of a hemisphere). Although in clinical practice the regurgitant orifice will be of finite size and unpredictable shape, the FC phenomenon is still encountered. Figure 5 shows a transoesophageal example of a large FC produced by severe MR secondary to posterior leaflet prolapse.

Since volume flow rate may be calculated as the product of surface area of flow and the flow velocity, the instantaneous volume flow rate at the FC will be 2πr²v. By the same principle, the instantaneous flow rate at the regurgitant orifice (regurgitant flow rate) will equal the product of the EROA and the velocity of flow through the orifice (by CW Doppler) at that instant. By the principle of conservation of mass, the volume flow rate at the FC must equal the regurgitant flow rate. Using the continuity equation, the EROA may be calculated as follows:where r = FC radius, v = colour Doppler aliasing velocity, and V_orifice = velocity at regurgitant orifice by continuous wave Doppler.

Although based on a theoretical model, a number of clinical studies have shown that these FC based flow and EROA computations produce results comparable to quantitative Doppler techniques.^31–33 The assumption of hemispherical geometry of the FC is central to the calculation, and it appears that the first (outer) aliasing boundary conforms more closely to this shape than successive, smaller FC zones. It is recommended therefore that the radius of the outermost FC (fig 5) is measured and used for flow computations.

It is important to realise that the EROA computed in this way reflects the area at that instant in time since the calculation is based on flow velocities which change dynamically over the cardiac cycle. In clinical practice, the operator will freeze the 2D colour Doppler image and scroll back through the digital cineloop until the frame where the FC size is maximal is found. This is assumed to correspond to the peak regurgitant flow rate since the velocity of flow will be highest at that point in time and the FC aliasing boundary will be at its furthest distance from the valve. FC flow rate is calculated from this frame using the above methodology. CW Doppler is then applied through the regurgitant orifice and the peak velocity of regurgitant flow recorded. In this way it can be assumed that FC and orifice flow rates correspond to the same point in time. The EROA thus generated will also coincide with the peak regurgitant flow rate. Quantitative Doppler on the other hand generates a mean EROA as its calculations are based on the regurgitant stroke volume and the VTI of the regurgitant flow signal. In practice, however, while there is minor variability in the EROA over the cardiac cycle, the difference between the peak and mean EROA is negligible for clinical purposes.

Thomas and colleagues have shown that the FC method can be simplified as follows, without significant loss of accuracy.³⁴ If it is assumed that the peak pressure difference from the left ventricle to left atrium in systole is in the order of 100 mm Hg (a reasonable assumption in the presence of normal left ventricular function), a mitral regurgitant jet of 5 m/s peak velocity will result. If the colour Doppler aliasing velocity is set to 40 cm/s, the FC calculation simplifies to EROA = r²/2. The amount of time saved by using this abbreviated version is debatable, however, since the majority of commercially available echocardiographic systems have on-board computation packages which greatly facilitate the formal FC calculations.

While the hemispherical assumption appears to work well for “free” or unconstrained FCs, in cases where flow proximal to a regurgitant orifice is constrained (for example, by an adjacent wall in the case of eccentric regurgitation) the FC shape may not be a true hemisphere. In such cases it is reasonable to adjust the formula by measuring the angle α subtended by the arc of the constrained FC and correcting the EROA calculation by a factor of α/180.³⁵

A further potential difficulty with the FC methodology can be the identification of the regurgitant orifice when making the radius measurement to the first aliasing boundary. To overcome this problem, the concept of “inter-aliasing distance” has been introduced.³⁶ This is based on the principle that by conservation of mass, the flow rate at any of the multiple FC zones approaching the orifice must be equal. A mathematical model has been developed which uses the distance between the first and second aliasing boundaries (the inter-aliasing distance) to generate a derived radius which may be used in FC flow computations. The mathematics are complex but the model does circumvent the need to define the position of the orifice.

Vena contracta measurements

The vena contracta (VC) is the narrowest portion or “neck” of the regurgitant jet which occurs at or just beyond the regurgitant orifice (figs 6 and 7). Although flow in this region is of high velocity, the flow pattern is organised into a series of parallel flow lines. Distal to the VC, flow becomes progressively more turbulent and disorganised as blood in the receiving chamber is entrained by the expanding regurgitant jet. Theoretically, the cross sectional area of the VC should bear a direct relation to the regurgitant orifice area. As the mitral regurgitant orifice in the clinical setting is likely to be complex and unpredictable in shape, to make such an area measurement would require the regurgitant jet to be imaged in a short axis plane. Hall and colleagues have shown that in the clinical setting, localisation of the narrowest portion of the regurgitant jet during short axis transthoracic imaging is difficult.³⁷ They do, however, demonstrate a clinically useful correlation between the width of the VC measured in zoom mode during long axis imaging of the jet in the parasternal and apical views, and the EROA measured by quantitative Doppler. The relation between VC width and EROA has been confirmed by other investigators,^38–40 and appears to hold true even in eccentric MR.⁴¹

Clearly there are limitations to using a one dimensional measurement (VC width) for the quantification of a two dimensional structure (EROA), but Hall shows that the former is a useful tool for quantification of MR with VC widths of < 0.3 cm and > 0.5 cm indicating mild and severe regurgitation, respectively (table 4). There are limitations to the technique, however. Even in the long axis view, localisation of the VC is difficult and requires considerable operator skill and patience. In addition, since the regurgitant orifice is unlikely to be regular in shape and may occur at any point along the mitral valve closure line, the VC must be identified and measured in a number of planes and “off-axis” views. Finally, since the absolute dimensions of the VC are small (several millimetres) there are issues regarding the axial versus lateral resolution of the ultrasound system. Axial resolution is related to wavelength and pulse duration and is superior to lateral resolution which is dependent on scan line spacing and beam width. VC measurements made in the direction of the axial imaging plane (parasternal views in the case of MR) should therefore be more accurate than those made in the lateral plane (apical views for MR). This effect becomes more significant at greater imaging depths since scan lines are radially distributed and become more separated as distance from the probe increases. The issue of axial versus lateral resolution is likely to be less pronounced in newer ultrasound systems which scan multiple lines simultaneously, but it is still advisable to make VC measurements in the axial plane where possible.

TRANSTHORACIC VERSUS TRANSOESOPHAGEAL IMAGING

All of the quantitative techniques discussed above may be performed by both transthoracic (TTE) and transoesophageal (TOE) echocardiography. It is certainly not necessary to perform TOE imaging in all patients with MR, but the superior resolution of that modality makes it easier to visualise and measure the FC zone if formal quantification is required. TOE also allows localisation of the vena contracta and measurement of its dimensions.^38,40

Doppler examination of pulmonary vein flow is also easier with TOE, although in our experience the introduction of ultrasonic contrast agents has made this possible in the majority of patients by TTE.

TOE imaging is extremely useful for the assessment of patients with mitral valve prolapse, particularly if surgical repair is contemplated. TOE is superior to TTE for the determination of the extent and distribution of leaflet involvement, both of which are of major importance in deciding on the suitability of the valve for repair.

It is advisable to use both TTE and TOE in the assessment of prosthetic mitral valve regurgitation, especially in the case of mechanical valves. This will minimise the effect of “shielding” by the metal components of the valve. For mitral valve prostheses, TOE imaging also allows differentiation between valvar and paravalvar regurgitation which may be difficult by transthoracic imaging. It also allows precise localisation of the site and extent of the paravalvar leak.

OTHER CONSIDERATIONS

In addition to quantifying the severity of regurgitation, it is important to assess the size and function of the left ventricle. In the early stages, the large volume overload associated with severe MR produces a left ventricle which is dilated with hyperdynamic function, where the end systolic cavity volume is small compared to the end diastolic volume. With time, however, sustained volume overload will ultimately lead to left ventricular dysfunction, and it is clearly desirable to correct severe MR before significant dysfunction has occurred. In this situation, end systolic chamber size is a more sensitive marker of impending ventricular dysfunction than end diastolic dimensions. The American Heart Association/American College of Cardiology recommend valve surgery in those patients with severe MR and a left ventricular end systolic diameter of 4.5 cm or greater even if the patient is asymptomatic.² Regular monitoring of left ventricular dimensions in patients with significant MR is therefore of the utmost importance.

Pulmonary artery systolic pressure should also be monitored where possible. The onset of pulmonary hypertension is an ominous sign in the setting of MR, and its early detection is mandatory.

Care must be taken in the evaluation of those MR patients who are apparently symptomatic with significant limitation to their activity, but whose echocardiographic study indicates “non-severe” MR. In this situation it is useful to reproduce the symptoms by exercising the patient (for example, with two minutes of sit-ups or leg raising) and repeating the study immediately after. The altered haemodynamics on exercise may increase the degree of MR and it is possible to quantify this formally by calculating EROA pre- and post-exercise. In addition, in those patients with functional MR secondary to regional or global left ventricular ischaemia, the true extent of regurgitation will only be seen if ischaemia is induced either by exercise or pharmacological stress echocardiography.

Exercise echocardiography has also been used to assess the contractile reserve of the left ventricle in MR patients. The post-exercise end systolic volume has been shown to be an effective predictor of left ventricular function after mitral valve repair.⁴²

FUTURE DIRECTIONS

Quantitative Doppler is a cumbersome technique. A number of measurements must be made to calculate volume flow rates through the LVOT and mitral annulus to ultimately generate mitral regurgitant volumes. Error will arise if any one of these measurements is made incorrectly. More sophisticated echo-Doppler methods are available which use spatio-temporal integration of digital flow velocities through these regions to compute volume flow rates automatically. One such implementation is automated cardiac output measurement (ACOM, Toshiba Imaging Systems). This method has been validated by a number of investigators and is a potential alternative to complex quantitative Doppler techniques.^43,44

Three dimensional echocardiography is a new technique which has been shown to be superior to conventional methods for the calculation of cardiac chamber volumes. Work is currently in progress examining its role in the quantification of regurgitant flow. A new three dimensional digital colour Doppler method has recently been introduced which should allow more accurate quantification of mitral and LVOT flow volumes, and hence regurgitant volumes.⁴⁵ Three dimensional echocardiography also has potential advantages over two dimensional methods in that flow events such as the FC can be viewed in their entirety, obviating the need to make a hemispherical shape assumption for surface area computations.⁴⁶ Since the entire regurgitant jet can be imaged and stored by three dimensional echocardiography, precise localisation of the VC should also be possible.

SUMMARY

Echo-Doppler is an extremely effective tool both for determining the pathology responsible for MR and for making an assessment of its severity. In the majority of patients, an “eyeball” grading of severity on a range from mild to severe is generally sufficient for clinical purposes. More formal quantitative approaches may be required in cases where there is discrepancy between this eyeball assessment and other clinical findings, and all cardiac sonographers should be conversant with at least one of these techniques. Exercise echocardiography may be required to assess the degree of regurgitation during the haemodynamic conditions occurring at the time of the patient’s symptoms. Exercise or pharmacological stress echocardiography may be also required in those patients with MR related to dynamic myocardial ischaemia. Serial measurement of left ventricular dimensions and pulmonary artery pressure is vitally important to detect impending problems with left ventricular dysfunction or pulmonary hypertension. Finally, as mitral valve repair becomes a safer procedure contemplated for asymptomatic patients, serial monitoring of EROA may also become advantageous to aid the decision of timing of valve surgery.