TECHNICAL PAPERS: Fluids/Heat/Transport

Numerical Simulation of Noninvasive Blood Pressure Measurement

[+] Author and Article Information
Satoru Hayashi

 Tohoku University, 15-4 Kitatakamori, Izumi-ku, Sendai 981-3202, Japan

Toshiyuki Hayase, Atsushi Shirai

Institute of Fluid Science, Tohoku University, 2-1-1 Katahira, Aoba-ku, Sendai 980-8577, Japan

Masaru Maruyama

 Tohoku Electric Power Co. Inc., 7-1 Honcho, 1-chome, Aoba-ku, Sendai 980-8550, Japan

J Biomech Eng 128(5), 680-687 (Feb 23, 2006) (8 pages) doi:10.1115/1.2241592 History: Received December 02, 2004; Revised February 23, 2006

In this paper, a simulation model based on the partially pressurized collapsible tube model for reproducing noninvasive blood pressure measurement is presented. The model consists of a collapsible tube, which models the pressurized part of the artery, rigid pipes connected to the collapsible tube, which model proximal and distal region far from the pressurized part, and the Windkessel model, which represents the capacitance and the resistance of the distal part of the circulation. The blood flow is simplified to a one-dimensional system. Collapse and expansion of the tube is represented by the change in the cross-sectional area of the tube considering the force balance acting on the tube membrane in the direction normal to the tube axis. They are solved using the Runge-Kutta method. This simple model can easily reproduce the oscillation of inner fluid and corresponding tube collapse typical for the Korotkoff sounds generated by the cuff pressure. The numerical result is compared with the experiment and shows good agreement.

Copyright © 2006 by American Society of Mechanical Engineers
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Figure 1

Partially pressurized collapsible tube model for the arterial flow channel

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Figure 2

Tube law of brachial artery

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Figure 3

External pressure distribution by cuff

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Figure 4

Pressure change in the aorta during one heartbeat cycle

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Figure 5

Temporal change of pulsatile pressure in the aorta and pressure in the cuff

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Figure 6

Staggered grid system with inequable mesh size

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Figure 7

Accuracy analysis of the calculation

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Figure 8

Simulated results of the time history of aorta pressure, cuff pressure, and flow velocities at the proximal and distal ends of the cuff during blood pressure measurement

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Figure 9

Measured results for aorta pressure, cuff pressure, Korotkoff sounds (top), and flow velocities at the proximal (center) and distal (bottom) ends of the cuff by Shimizu and Tatsumae (6)

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Figure 10

Simulated results of the time history of pressure at the immediately distal end of the cuff at x=0.5605m and the first and the second derivatives

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Figure 11

Directly measured blood pressure change at the distal end of the cuff by Tavel (2)

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Figure 12

Measured result of rapid pressure rise at the distal end of the cuff, the first derivative, and Korotkoff sounds by Tabel (2)

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Figure 13

Rapid pressure rise at the distal end of the cuff at x=0.5605m and the first derivative by simulation




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