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The role of Doppler in the assessment of fetal and placental blood flow is well-established1. However, as exemplified by the large variability of results published in the literature, its role in the evaluation of uterine and ovarian hemodynamics is not so clearly defined. Velocimetric indices such as pulsatility index and resistance index have been shown to provide useful information on uterine perfusion and angiogenesis in the ovarian follicle and certain cancers, but have not been adopted to any significant degree into clinical practice. Because of the advantages of power Doppler compared with conventional two-dimensional color Doppler2, some investigators have advocated its use for blood flow mapping3, 4. However, this technique only provides information on the ‘vascular map’ of a given region of interest and assessment relies largely on the subjective impression of the examiner.

The advent of three-dimensional (3D) power Doppler ultrasound has begun a new era in tissue and organ vascularization research. Using this technique, we can now assess a virtually reconstructed vascular tree within a volume of interest5 and can ‘objectively’ determine its vascularization by calculating indices using the specially designed VOCAL software (GE Medical Systems, Zipf, Austria)6. Objective and non-invasive quantification of vascularization of a given tissue volume holds much promise, particularly because this method has proved to be highly reproducible between observers (thereby overcoming one of the main limitations of conventional Doppler ultrasound)7–9.

Since the pioneering study of Pairleitner et al.6 in 1999, more than 100 papers have been published analyzing the role of 3D power Doppler ultrasound in almost all areas of obstetrics and gynecology, including placental and fetal vascularization10, 11, reproductive medicine12, 13, gynecological endocrinology14, gynecological oncology15–17, breast pathology18 and the pelvic floor19.

Despite this abundance of literature on the application of 3D power Doppler ultrasound, it seems that so far few have stopped to ask what we are measuring. Calculation of the three 3D power Doppler ultrasound vascular indices, the vascularization index (VI), flow index (FI) and vascularization flow index (VFI), is based on and related to the total and relative amounts of power Doppler information within the volume of interest. VI denotes the ratio of color-coded voxels to all voxels within the volume and is expressed as a percentage, FI represents the mean power Doppler signal intensity from all color-coded voxels and VFI is the simple mathematical relationship derived from multiplying VI by FI and dividing the result by 1006. Both FI and VFI are unitless and are expressed as a numerical value ranging from 0 to 100. The indices are thought to reflect the number of vessels within the volume of interest (VI), the intensity of flow at the time of the 3D sweep (FI), and both blood flow and vascularization (VFI)6.

Although our knowledge about what these indices are actually measuring is limited, most examiners involved with the use of power Doppler are aware that several factors affect the power Doppler signal20, 21. Yet, studies evaluating how machine settings affect measurements are scanty22. In this issue of the Journal, three papers make a significant contribution to the understanding of what these indices are measuring and how machine settings affect the measurements23–25. All three studies were performed in an in-vitro setting using a flow phantom experiment.

In the first study by Raine-Fenning et al.23, the authors evaluated the relationship of VI, FI and VFI values with vessel number, flow rate, attenuation and ‘erythrocyte’ density. They found a positive linear relationship between VI and VFI and all these factors except attenuation, which showed a negative relationship. In other words, with increasing number of vessels, volume flow or erythrocyte density, VI and VFI values increase. In the case of VI, these findings are particularly interesting. VI actually quantifies the number of color-coded voxels, which does not necessarily mean the number of vessels. However, in this phantom study, the authors found a correlation between the number of color-coded voxels and ‘number of vessels’. This finding is in agreement with preliminary data from in-vivo studies that showed that VI correlates positively with microvessel density count as assessed by immunohistochemical techniques26. In contrast, the further the object under investigation is from the transducer, the lower the values obtained. This is of clinical relevance, because the route—transvaginal or transabdominal—should be taken into account when performing the calculations, as should the distance between the probe and the object under investigation. However, Raine-Fenning et al. found that FI showed a ‘more complex cubic relationship that is not always logical’. This could indicate that FI is less predictable than VI and VFI. For example, they discovered that VI and VFI increase steadily with an increasing number of vessels, while FI reached a peak with three vessels and decreased thereafter. Additionally, as the authors themselves proved, a greater distance from the transducer to the furthest ‘vessels’ in the phantom decreased the signal intensity, leading to an overall decrease of the power Doppler signal.

In their second paper, Raine-Fenning et al.24 demonstrate that machine settings and speed of acquisition affect significantly all three 3D power Doppler ultrasound indices. These findings could be anticipated because it is well known that machine settings affect the power Doppler signal20, 21. A potential weakness of their study is that it used an ultrasound machine from the old Voluson series, the Voluson 530, which did not have the power Doppler sensitivity of equipment in current use. However, in my opinion, this fact does not invalidate their results. In fact, in the third study, by Schulten-Wijman et al.25, the more modern Voluson 730 Expert was used and the principal study findings, that machine settings affect VI and FI calculation, were similar. An interesting additional finding is that ‘measured VI’ overestimated ‘actual VI’ even with different machine settings by up to 44 times! The concept of ‘actual VI’, as described by the authors in the paper, could be misleading but they are probably right. The VI is just a ratio between colored and total voxels and, since voxels are actually small cubes that occupy a predetermined volume, in my opinion, the VI is in fact the ratio between the volume of colored voxels and the volume of the total voxels. However, what I cannot understand is how they obtained those results because, assuming that all colored voxels within the tube are detected by the machine, the VI should be as high as the ‘actual VI’, but never higher. The experimental set-up in this study used a single tube, simulating one vessel, and it remains to be seen whether this finding could be extrapolated to true tissue vascularization where multiple vessels exist. Notwithstanding, this fact should be taken into consideration when measuring the VI in a single vessel, such as the uterine, umbilical, or fetal middle cerebral artery. Schulten-Wijman et al. also propose that the term ‘flow index’ be replaced by ‘power index’, a suggestion that I would endorse, because what we are actually measuring is mean power Doppler signal intensity.

Although it should be acknowledged that phantom studies for assessing Doppler systems have certain limitations27, 28, and that the authors of these three studies used somewhat exaggerated machine settings that are not usually used in clinical practice, the results they report are relevant for at least two reasons. First, they provide evidence that machine settings affect VI, FI and VFI calculations. The primary consequence of this should be that all future papers published using this method should report the machine settings used and even the maximum depth of the objects evaluated when performing investigations. Furthermore, these results should prompt us to reach a consensus about which machine settings should be used, at least in the research situation, in order to allow meaningful comparison among studies. To the best of my knowledge, only the 3D Ultrasound Group from the Spanish Society of Ultrasound in Obstetrics and Gynecology has documented recommendations about machine settings to be used for research29 and, in my opinion, the International Society of Ultrasound in Obstetrics and Gynecology (ISUOG) should formulate a proposal for standardized settings to be used worldwide.

Second, these studies have shown how VI, FI and VFI indices are not related equally to the number of vessels and volume flow. This implies that the most appropriate index to use might be different depending on the clinical setting. For example, for analyzing tumor vascularization, VI may be preferred because in clinical practice oncologists and pathologists already use the mean vessel density (i.e. the number of vessels as a measure of tumor vascularization), the amount of flow being less relevant. However, when volume flow is the target of investigation, for example in maternal–fetal and reproductive medicine, it may be that FI is more useful.

I believe that we are a long way from clearly defining the role of 3D power Doppler ultrasound indices in clinical practice. However, steps such as those reported in this issue of the Journal are important for the scientific understanding of this technology.

References

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