Abstract
BACKGROUND AND PURPOSE: Hemodynamics are thought to play a role in intracranial aneurysm growth and rupture. Computational fluid dynamics is frequently performed to assess intra-aneurysmal hemodynamics, using generalized flow waveforms of healthy volunteers as inflow boundary conditions. The purpose of this study was to assess differences in inflow conditions for different aneurysmal parent artery locations and variations of circle of Willis configurations.
MATERIALS AND METHODS: In a series of 96 patients with 103 aneurysms, velocity measurements were acquired using 2D phase-contrast MR imaging perpendicular to the aneurysmal parent arteries in the circle of Willis. Circle of Willis configurations were inspected for variations using multiple overlapping thin-slab-acquisition MRAs. Flow rates, velocity magnitudes, and pulsatility indices were calculated for each parent artery location in subgroups of complete and incomplete circle of Willis configurations.
RESULTS: Flow rates, velocity magnitudes, and pulsatility indices were significantly different among aneurysmal parent arteries. Incomplete circle of Willis configurations were observed in 24% of the cases. Significantly lower basilar artery flow rates were observed in configurations with hypoplastic P1 segments. Significantly higher A1 flow rates were observed in configurations with a hypoplastic contralateral A1 segment.
CONCLUSIONS: Inflow conditions vary substantially between aneurysmal parent arteries and circle of Willis configurations. We have created a collection of parent artery–specific inflow conditions tailored to the patient-specific circle of Willis configuration that can be used in future computational fluid dynamics studies analyzing intra-aneurysmal hemodynamics.
ABBREVIATIONS:
- ACA
- anterior cerebral artery
- AcomA
- anterior communicating artery
- BA
- basilar artery
- CoW
- circle of Willis
- PC-MR
- phase-contrast MR imaging
- PcomA
- posterior communicating artery
- PI
- pulsatility index
- VA
- vertebral artery
The incidence of an unruptured intracranial aneurysm in the general population is approximately 3%.1 Most of these aneurysms are asymptomatic, and 50%–80% of all aneurysms do not rupture during the individual's lifetime.2 However, rupture results in subarachnoid hemorrhage, a devastating occurrence associated with high morbidity and fatality rates.2 In clinical practice, large size (≥7 mm) and high-risk location (posterior circulation and communicating arteries) are most frequently used to identify aneurysms with a high risk of rupture.3 However, most aneurysms are <7 mm, and a proportion of these small aneurysms rupture, nevertheless.4 Therefore, many studies have been performed to identify additional risk factors for rupture to improve the management of unruptured intracranial aneurysms.
Besides morphologic parameters, intra-aneurysmal hemodynamics are thought to play a role in aneurysm formation, growth, and rupture. Therefore, hemodynamics are frequently assessed to search for differences between ruptured and unruptured aneurysms.5,6 To analyze hemodynamic properties, computational fluid dynamics are commonly used to simulate the blood flow in patient-specific aneurysm models. Computational fluid dynamics depend highly on boundary conditions such as geometry and inflow waveforms.7⇓–9 Therefore, high-resolution 3D angiographic imaging and patient-specific data of inflow velocities are needed. Because patient-specific velocity waveforms are rarely available, generalized velocity waveforms of healthy subjects are frequently used.10,11 However, intracranial flow velocities vary widely among subjects.12,13 A previous study showed that generalized waveforms result in different hemodynamic characteristics, compared with patient-specific velocity waveforms.14 A similar heterogeneity in flow patterns is expected among variations in location and configuration of the circle of Willis (CoW).15 This variety of aneurysmal inflow conditions in different aneurysmal parent arteries, considering anatomic variations in the CoW, is insufficiently studied. In this study, we present location-specific aneurysmal inflow waveforms for arteries in the CoW and determine the influence of CoW variations on local flow conditions.
Materials and Methods
Patient Selection
All patients treated in the Academic Medical Center Amsterdam for a ruptured or unruptured aneurysm from January 2009 to October 2011 were invited to participate in the Hemodynamics for Rupture Risk Assessment of Intracranial Aneurysms (HEROICA) study.16 The HEROICA study assessed the additional value of hemodynamics in discriminating ruptured and unruptured aneurysms and was approved by the institutional review board. Written informed consent was obtained from all patients. To assess the variation of inflow in these aneurysms, we included all patients with sufficient quality phase-contrast MR imaging (PC-MR) in the HEROICA dataset.
MR Imaging
MR imaging was performed at 3T (Intera; Philips Healthcare, Best, the Netherlands). 2D PC-MR imaging was performed for velocity measurements perpendicular to the aneurysmal parent arteries. These included the basilar artery (BA), vertebral artery (VA), internal carotid artery, middle cerebral artery, and the A1 and A2 segments of the anterior cerebral artery (ACA). Heart rate monitoring was performed by electrocardiography or by a peripheral pulse unit and was used for cardiac triggering and heart rate calculations. PC-MR imaging resolution was 0.63 × 0.63 × 3 mm. Velocity-encoding was 70–100 cm/s. Velocity measurements were acquired in 23–36 uniformly spaced cardiac phases. PC-MR imaging was performed before treatment for patients with unruptured aneurysms or at 6-month follow-up after endovascular treatment for cases with acutely ruptured aneurysms. A routine multiple overlapping thin-slab-acquisition MRA sequence with a scan resolution of 0.4 × 0.4 × 0.5 mm was performed to visualize the aneurysm and was used to assess CoW configurations.
Assessment of CoW Configurations
Absence or hypoplasia of arterial components in the CoW was assessed by an experienced neuroradiologist (M.E.S.), using axial reconstructions and volume-renderings of the multiple overlapping thin-slab-acquisition MRA data. A1 and VA hypoplasia were defined as diameters of ≤50% compared with the contralateral side.17,18 Hypoplasia of the P1 segment of the posterior cerebral artery was defined as a diameter smaller than that of the feeding posterior communicating artery (PcomA).19,20 Hypoplasia of the PcomA and anterior communicating artery (AcomA) was defined as diameters of ≤0.8 mm.21 A textbook-type CoW configuration and a variant-type CoW configuration with anatomic variations of the VA, P1, and A1 are schematically presented in Fig 1.
Schematic overview of 2 different CoW configurations. A, Textbook-type. B, Variant-type with hypoplastic VA, P1, and A1 segments, see arrows. VA and A1 segments with diameters ≤50% compared with the contralateral side and P1 segments < PcomA were defined as hypoplastic.
CoW configurations were dichotomized into perianeurysmal complete and incomplete groups. Configurations were considered incomplete in case the vascular morphology near the aneurysm presented anatomic variants that were expected to alter local flow rates. For ICA and MCA parent artery locations, configurations with hypoplastic ipsilateral P1 and/or contralateral A1 segments were considered incomplete. For A1 measurement cases, configurations with hypoplastic ipsi- or contralateral A1 segments were considered incomplete. For A2 parent artery locations, azygos ACA or ACA trifurcation configurations were considered incomplete. For the VA, configurations with hypoplastic ipsi- or contralateral VA segments were considered incomplete. For BA cases, 1- or 2-sided hypoplastic P1 segments were considered incomplete configurations.
Flow Parameters
To define the inflow region of the parent artery, we extracted a contour for each cardiac phase using a level-set evolution algorithm22 in the PC-MR magnitude images. Due to arterial pulsatility, the inflow region could have varied between cardiac phases. Spatial-averaged velocity waveforms were calculated for every patient by dividing the sum of the velocity magnitudes in each cardiac phase by the time-averaged inflow area. Flow waveforms were calculated by multiplying the sum of through-slice velocity components by the area of the inflow region for each cardiac phase. High-frequency components in the flow and velocity waveforms were considered noise and therefore suppressed using an eighth-order low-pass Butterworth filter23 with a half-power frequency of 0.32 Hz. Using the flow- and velocity-waveforms, we calculated temporally averaged flow rates and mean velocity magnitudes. In addition, the pulsatility index (PI) was calculated to quantify the pulsatile character of the flow waveforms. The PI was defined as the ratio of flow variation to the average flow during a cardiac cycle (Fig 2).24 Parent artery–specific flow parameters were calculated for subgroups with perianeurysmal complete and incomplete CoW configurations.
Automatic extraction of 11 waveform features and the PI. M: diastolic minimum. S1–S3: 25, 50, and 75% of the amplitude before peak systole. P: peak systole. D1: 75% of the amplitude after peak systole. H: half-maximum after systole. D2–D5: late diastolic features, equally spaced in time (▵T). Feature S2 was set to time = 0s.
Location-Representative Waveforms
Eleven features were automatically extracted for each waveform (Fig 2). The waveform was characterized by the diastolic minimum (M) and peak systole (P).25 Additional systolic features were extracted for 25%, 50%, and 75% of the amplitude (S1, S2, S3). Diastolic features were extracted for 75% of the amplitude after systole (D1), half-maximum after systole (H), and 4 uniformly in time-spaced features between H and the end of the cardiac cycle (D2–D5). Feature S2 was set to time = 0 seconds. Median feature points were calculated by taking the median flow amplitude at the median time point in the cardiac cycle. Similarly, the interquartile range (IQR) was calculated for each feature point. Location-representative waveforms were generated by cubic spline interpolation of the median feature points for aneurysmal parent arteries in complete and incomplete configurations. The slopes of the first and last feature points were set to zero.
Statistical Analysis
The Kruskal-Wallis test was performed to determine whether flow parameters were different between aneurysmal parent arteries. Subsequently, the Tukey honestly significant difference was performed to analyze differences between combinations of groups. Mann-Whitney U tests were used to assess whether parent artery–specific flow parameters were different between complete and incomplete CoW configurations. In addition, mean velocity magnitudes and PIs were compared between anterior and posterior parent arteries. P values < .05 indicated statistically significant differences.
Results
A total of 96 patients (62 women) with 103 aneurysms (61 ruptured) were included in this study. The median patient age was 53 years (range, 27–76 years). Heart rates ranged between 51 and 109 beats per minute, with a mean of 69 ± 10 beats per minute. The prevalence of anatomic variants in the CoW is shown in Table 1. Only 10% of the patients had a textbook-type CoW configuration, and almost half of the CoW configurations presented with hypoplastic VA, A1, and/or P1 segments.
Prevalence of anatomic variants in the CoW
Table 2 shows the prevalence of perianeurysmal incomplete CoW configurations for each aneurysmal parent artery location. Configurations were incomplete in 24% of the cases. Figure 3 presents boxplots for aneurysmal parent artery–specific flow rates in complete and incomplete CoW configurations. Table 3 shows flow and velocity measures for aneurysmal parent arteries in complete and incomplete configurations. The Location-representative flow and velocity waveforms are shown in Figs 4 and 5, respectively, for aneurysmal parent arteries in perianeurysmal complete and incomplete CoW configurations. Group median (IQR) feature points are shown in the On-line Table.
Prevalence of perianeurysmal incomplete CoW configurations for each aneurysmal parent artery location
Boxplots for aneurysmal parent artery–specific flow rates in complete (left) and incomplete (right) CoW configurations. The asterisk indicates a statistically significant difference (P < .05).
Mean velocity magnitudes, flow rates, and PIs for aneurysmal parent arteries in complete and incomplete CoW configurations
Location-representative flow waveforms for aneurysmal parent arteries in perianeurysmal complete (blue) and incomplete (red, dashed) CoW configurations. Interquartile ranges are presented for feature points M, S2, P, H, and D6.
Location-representative velocity waveforms for aneurysmal parent arteries in perianeurysmal complete (blue) and incomplete (red, dashed) CoW configurations. Interquartile ranges are presented for feature points M, S2, P, H, and D6.
Flow rates, velocity magnitudes, and PIs were significantly different among parent artery locations: P < .001, P = .008, and P = .041, respectively. VA flow rates were significantly lower compared with ICA flow rates. Furthermore, significantly lower mean velocity magnitudes were observed for the VA arteries compared with the MCA arteries. No statistically significant differences in PIs were found in pair-wise comparisons among parent artery locations.
BA flow rates were significantly lower for subgroups with 1 or 2 hypoplastic P1 segments. Significantly higher A1 flow rates were observed in configurations with a hypoplastic contralateral A1 segment.
Cases of aneurysmal parent arteries in the posterior circulation showed significantly higher PIs (P = .017) and lower mean velocity magnitudes (P = .034) compared with parent arteries in the anterior circulation.
Discussion
Our study presents location-specific flow rates and velocity magnitudes and shows significant differences among aneurysmal parent artery locations in the CoW. Hypoplastic VA, A1, or P1 segments were observed in almost half of our population. Higher flow rates were observed in A1 segments with an absent or hypoplastic contralateral A1, and lower flow rates for BAs with hypoplastic P1 segments.
Intracranial flow rates have been assessed in several previous PC-MR studies26,27 with relatively small study populations of healthy subjects. In these studies, flow rates were comparable with our findings; however, no information regarding anatomic variations in the CoW configurations was provided in these studies. Other studies investigated relationships between anatomic variations in the CoW and neurovascular diseases; however, no relations with aneurysmal inflow were assessed. The prevalence of VA, A1, and P1 hypoplasia in our study was similar to that reported previously.18,19,28 The cerebral blood flow distribution in different configurations of the CoW was assessed previously.29 In this study, decreased BA flow rates were observed in fetal-type posterior cerebral artery configurations, and increased ICA flow rates, in the ipsilateral fetal-type posterior cerebral artery and missing contralateral A1 configurations. Our study also showed significantly lower BA flow rates in hypoplastic P1 configurations, and a trend toward higher ICA flow rates in ipsilateral hypoplastic P1s and hypoplastic contralateral A1 configurations was seen. The relation between the CoW configuration and flow rates of the ICA and BA has also been studied in healthy volunteers; this study showed similar findings.15 However, A1 and P1 hypoplasia was only observed in 5% of the study population.
It has been shown that inflow variations of <25% have little effect on flow characteristics in computational fluid dynamics simulations.30 Our study presents larger velocity and flow variations among parent artery locations and CoW configurations. Furthermore, in accordance with previously reported data,31 the interpatient variability of peak systolic flow measures was >25%. This finding suggests that those parameters should be taken into account in computational fluid dynamics calculations.32
Our study has several limitations. The limited imaging resolution of the PC-MR image resulted in partial volume artifacts, which might have led to inaccurate delineations of inflow regions, resulting in inaccurate velocity magnitude calculations. We used time-averaged cross-sectional areas of the PC-MRA imaging to calculate temporal velocity profiles, which might not agree with the areas of the 3D rotational angiography–derived vascular models used for computational fluid dynamics because of differences in imaging and segmentation methods. Furthermore, differences in velocity-encoding might have influenced the results, and the quality requirements for the PC-MR imaging might have resulted in a selection bias. Another limitation of our study was the relatively small sample size. For VA and A2 cases, large differences in flow rates were observed between complete and incomplete configurations, but due to the small sample size, we could not determine whether this was a systematic deviation. Furthermore, low TOF intensities hindered the assessment of hypoplastic segments in some cases due to slow flow or coil artifacts. In addition, CoW assessment was performed by 1 observer only, and comparison with previous results from the literature was hampered by the use of different definitions for hypoplasia of vascular segments.
Conclusions
There is variation in aneurysmal inflow conditions among parent arteries and CoW configurations. When patient-specific inflow waveforms are not available, we recommend using parent artery–specific flow waveforms, tailored to the patient-specific CoW configuration to improve the accuracy of intra-aneurysmal hemodynamic simulations. We have made a collection available of flow and velocity waveforms that can be used in future computational fluid dynamics studies.
Footnotes
Henk A. Maquering and Charles B.L.M. Majoie contributed equally to this work.
Disclosures: René van den Berg—UNRELATED: Consultancy: Codman Depuy Neurovascular, Comments: coil development,* Henk A. Marquering—OTHER RELATIONSHIPS: cofounder and shareholder of Nico-lab. Charles B.L.M. Majoie—RELATED: Grant: TWIN Foundation*; UNRELATED: Grants/Grants Pending: Dutch Heart Foundation, Stryker.* *Money paid to the institution.
This work was supported by a grant from the Stichting Toegepast Wetenschappelijk Instituut voor Neuromodulatie (TWIN), the Netherlands. The HEROICA study was supported by a grant from the Nuts-OHRA Foundation, the Netherlands.
References
- Received October 23, 2017.
- Accepted after revision January 31, 2018.
- © 2018 by American Journal of Neuroradiology
