- Research note
- Open Access
Carotid artery velocity time integral and corrected flow time measured by a wearable Doppler ultrasound detect stroke volume rise from simulated hemorrhage to transfusion
BMC Research Notes volume 15, Article number: 7 (2022)
Doppler ultrasonography of the common carotid artery is used to infer stroke volume change and a wearable Doppler ultrasound has been designed to improve this workflow. Previously, in a human model of hemorrhage and resuscitation comprising approximately 50,000 cardiac cycles, we found a strong, linear correlation between changing stroke volume, and measures from the carotid Doppler signal, however, optimal Doppler thresholds for detecting a 10% stroke volume change were not reported. In this Research Note, we present these thresholds, their sensitivities, specificities and areas under their receiver operator curves (AUROC).
Augmentation of carotid artery maximum velocity time integral and corrected flowtime by 18% and 4%, respectively, accurately captured 10% stroke volume rise. The sensitivity and specificity for these thresholds were identical at 89% and 100%. These data are similar to previous investigations in healthy volunteers monitored by the wearable ultrasound.
Inferring change in stroke volume (SV) is the bedrock of functional hemodynamic monitoring [1, 2]. Yet measuring SV change (SV∆) is clinically challenging, so surrogates like the common carotid artery Doppler pulse have been proposed [3, 4] with some conflicting data . We contend that statistically-inadequate beat sampling coupled with variation introduced by the respiratory cycle are important arbiters of inconsistent clinical research . To rectify the shortcomings of handheld examinations, we developed a wireless, wearable Doppler ultrasound [7, 8]. This device adheres to the neck, maintains a constant insonation angle and accurately measures beat-to-beat changes across multiple cardiorespiratory cycles [6, 7].
In early, proof-of-concept investigations, the carotid artery maximum velocity time integral (VTI) and corrected flow time (ccFT) accurately identified a + 10% SV∆ with thresholds of + 15% and + 2–4%, respectively [9, 10]. More recently, in a human model of hemorrhage and resuscitation comprising approximately 50,000 cardiac cycles, we found a strong, linear correlation between SV∆, and both changing maximum carotid VTI (VTI∆) and ccFT (ccFT∆) . While 10% SV∆ associated with 18% VTI∆ and 4.3% ccFT∆, the optimal VTI∆ and ccFT∆ thresholds for detecting a + 10% SV∆ were not investigated. In this Research Note, we report these thresholds, their sensitivities, specificities and areas under their receiver operator curves (AUROC).
11 healthy, adult volunteers with no cardiovascular history and who provided written, informed consent were recruited. The study was approved by the Research Ethics Board of the Mayo Clinic (IRB number 19–010,136).
Adherent Doppler system
The U.S. Food and Drug Administration (FDA) cleared, 4 MHz Doppler ultrasound (Fig. 1) (Flosonics Medical, Sudbury, Canada) was placed and the ccFT, maximum and power-weighted, i.e., centroid, VTIs were captured [6, 8,9,10].
Lower body negative pressure (LBNP) and stroke volume
As previously reported , all subjects underwent a 7-stage protocol in duplicate; a non-invasive SV monitor, the Nexfin® (Edwards Lifesciences, Irvine, California), was synchronized with the Doppler monitor for each cardiac cycle.
All data was averaged over 10-s windows. SV and carotid Doppler were referenced to resting baseline to model hemorrhage. Cardiac cycles with artifact or during LBNP stage transition were excluded, as described . SV change from the lowest-tolerated LBNP stage back to atmosphere modeled rapid blood transfusion, data from this transition was included.
Each 10-s data point was dichotomized as ≥ + 10% SV∆ or < + 10% SV∆ based on the non-invasive SV monitor. An equal number of data points were randomly sampled from negative pressure stages without replacement to match the sample size of the positive cases (≥ + 10% SV∆) for 1000 iterations. Within each iteration, the optimal threshold for each metric was selected using the Youden index. Averages of optimal thresholds and the corresponding sensitivities and specificities were calculated from all iterations and reported as the best final estimations. AUROC was calculated using the subsamples that produced the same optimal thresholds as the final estimation after 1000 iterations.
The median and interquartile ranges for age and BMI were 27 (23—38) years and 23 (21.9–25.6) kg/m2, respectively; 39% were female. Vital signs and their change are previously reported . Figure 2 A-D illustrates the progression of mean arterial pressure (MAP), SV, maximum VTI, ccFT and SV for all protocols. The optimal thresholds of % VTI∆, % ccFT∆ and their calculation are shown in Fig. 2 E and F. Both + 18% VTI∆ and + 4% ccFT∆ were 89% sensitive and 100% specific at detecting ≥ + 10% SV∆. The areas under their receiver operator curves were 0.97 and 0.98, respectively. Though not illustrated, a + 20% change in the centroid VTI had identical diagnostic characteristics.
In this model of hemorrhage and transfusion, the % VTI∆ and % ccFT∆ thresholds for detecting a ≥ + 10% SV∆ are consistent with earlier proof-of-concept data using a separate paradigm, also in healthy volunteers [9, 10]. With simulated blood transfusion, the 4% ccFT∆ approximates an absolute ccFT∆ of 10 ms, comparable to the 7 ms threshold observed in critically-ill patients with undifferentiated shock . The + 18% VTI∆ threshold in this investigation is consistent with the slope of the SV∆- VTI∆ regression line, described previously . Curiously, the + 20% threshold for the power-weighted (i.e., centroid) VTI matches the threshold of changing carotid blood flow in septic patients . Assuming static vessel diameter, changing centroid velocity best approximates volumetric flow change .
Our findings have a number of limitations deserving of elaboration. First, from a broad hemodynamic perspective, common carotid blood flow relates to cardiac output (i.e., total blood flow) by the following, general relationship:
where Z is the impedance to flow for the listed vascular beds. Thus, using the carotid artery as a surrogate for SV∆ implies a constant ratio of whole body-to-downstream carotid impedance. That HR increased and MAP remained constant during the protocol, Zwhole body (e.g., total vascular resistance) likely rose relative to Zcarotid artery, especially if downstream internal carotid artery impedance fell by auto-regulation. This could partly explain the relatively large change in carotid VTI (i.e., 18%) observed to detect a 10% SV∆. Second, though we did not measure carotid diameter to calculate carotid artery flow, the normal carotid artery pressure-diameter relationship is relatively flat above a MAP of 80 mmHg [11, 12]. More specifically, the carotid diameter changes by only 0.2 mm when MAP rises from 80 to 110 mmHg ; the average MAP for our subjects during the lowest tolerated LBNP stage was 99 mmHg. Nevertheless, even a 0.2 mm diameter change in a 7 mm carotid artery affects total flow by ± 6% . On the other hand, in hypotensive patients, diameter assessment is likely more important; for example, measuring the diameter of the descending aorta improves the sensitivity of Doppler ultrasonographic flow assessment by approximately one-third in the critically-ill . Third, we chose non-invasive pulse contour analysis as a gold standard because it is continuous, user-independent and accurately trends % SV∆, which is important for functional hemodynamic monitoring. However, absolute SV measures by non-invasive pulse contour analysis are less adequate, especially in the critically-ill [15, 16]. Still, we believe that the pattern of SV∆ that we observed is valid because it replicates the SV∆ measured in other LBNP investigations [17, 18] and is consistent with the LBNP SV∆ measured by other gold standards including left ventricular outflow tract VTI , bioimpedance  and bioreactance .
In summary, in this large data set of continuously-monitored SV synchronous with carotid Doppler, multiple measures from a wearable ultrasound patch identified + 10% SV∆ with high accuracy.
The datasets used and/or analysed during the current study are available from the corresponding author on reasonable request.
Area under the receiver operator curve
- SV∆ :
Stroke volume change
Velocity time integral
Carotid corrected flow time
- VTI∆ :
Velocity time integral change
- ccFT∆ :
Carotid corrected flow time change
Food and Drug Administration
Lower body negative pressure
Body mass index
Mean arterial pressure
- Zwhole body :
Whole body impedance
- Zcarotidy artery :
Carotid artery impedance
Millimeters of mercury
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We wish to acknowledge Briana Ziegler, Alex Carlson and Brad Cierzan for their technical assistance, recruitment, scheduling and data management. Additionally, Matt Myers for his assistance in data analysis.
This work was supported by the Office of the Assistant Secretary of Defense for Health Affairs, through the Congressionally Directed Medical Research Program under Award No. W81XWH1910591. Opinions, interpretations, conclusions and recommendations are those of the authors and are not necessarily endorsed by the Department of Defense.
Ethics approval and consent to participate
The study was approved by the Research Ethics Board of the Mayo Clinic (IRB number 19-010136); written and informed consent was obtained for all subjects.
Consent for publication
JESK, ME, ZY, AME, JKE are employees of Flosonics Medical, a start-up building the wearable ultrasound, IB reports consulting fees for GE Healthcare, DCM, CHK and BDJ report no conflicts.
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
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Kenny, JÉ.S., Barjaktarevic, I., Mackenzie, D.C. et al. Carotid artery velocity time integral and corrected flow time measured by a wearable Doppler ultrasound detect stroke volume rise from simulated hemorrhage to transfusion. BMC Res Notes 15, 7 (2022). https://doi.org/10.1186/s13104-021-05896-y
- Carotid Doppler
- Stroke volume
- Velocity time integral
- Corrected flow time