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Cardiac Assist

Development of Squeeze Flow in Mechanical Heart Valve: A Particle Image Velocimetry Investigation

Zhang, Pei*; Yeo, Joon Hock; Hwang, N H. C.

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doi: 10.1097/01.mat.0000225267.87767.68
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Abstract

Cavitation is the rapid formation and collapse of vaporous bubbles caused by a momentarily sharp drop in local pressure below vapor pressure.1 Some clinically explanted mechanical heart valves (MHVs) show erosions and pittings, which are typical of the damage caused by the collapse of cavitation bubbles.2 The mechanism and origin of MHV cavitation is yet to be fully understood. Factors affecting MHV cavitation and associated flow characteristics have been extensively studied in the past decade. MHV occluder closure behavior is widely believed to be the key factor in MHV cavitation.3,4 As the occluder is approaching its fully closed position, the gap between the occluder tip and the solid orifice wall becomes a narrowing flow channel. Fluid contained between this gap has a tendency to be squeezed out of this channel, causing a high-speed jet flow. This squeeze-flow characteristic of local pressure reduction may initiate cavitation.5

The MHV closure flow relating to cavitation was studied both by experimental work and computational fluid dynamics (CFD). Lee et al.6 identified possible valve design factors for cavitation initiation when studying nine different MHVs. The occluder stop seat, where fluid squeezing may occur, was suggested to be most critical to cavitation because the valve with this feature showed a high intensity of cavitation and a low threshold loading rate. Further investigation of transient pressure measurements and cavitation bubble visualization was performed at seven locations of an MHV.7 The presence of negative pressure and bubbles around the seat stop suggested that the fluid squeezing effect was the main cause of cavitation. Chandran et al.8 gave a rough estimation of the squeeze flow velocity of 12 m/s based on the observation of cavitation bubbles in a flow loop simulating single closing of mitral valve. The squeeze flow velocity in MHV was also approximately calculated from the impacting speed and gap width in two impinging rods. An increase of cavitation risk and intensity was found with elevated squeeze flow velocity.9 Maymir et al.10 found fluid velocity spike in the minor orifice of a monostrut valve upon closure, with a magnitude of 1.67 m/s in the aortic position and 3.02 m/s in the mitral position, which was suggested as evidence of “squeeze flow.” Kini et al.11 studied the flow field both for forward closure and occluder rebound with particle image velocimetry (PIV) techniques in a single-shot experiment setup. Flow velocity in excess of 1.5 m/s was detected 3 mm away from the valve seat on the major orifice side, where cavitation has been observed. Manning et al.12 also observed high-speed regurgitant jet along with vortex in PIV images. It was suggested that near leaflet vortex may provide a low pressure environment for cavitation.

The calculation of the squeeze flow inside the gap can reach as high as 30 m/s near the leaflet surface in the mitral position.13 With considerable leaflet deceleration and rebound, relatively low squeeze flow velocity (about 9m/s) is observed.14 CFD simulation coupled with occluder motion and housing deformation demonstrated that the squeeze flow field is influenced by the valve mounting compliance and the geometry of the contact region.15

Detailed experimental investigation in squeeze flow is still limited. This study aimed to provide some quantitative observations for the flow field upon valve closure, because the cavitation potential in MHV can be predicted through the explanation of squeeze flow field.

Materials and Methods

Pulsatile Flow Test Loop

The pulsatile flow experimental setup is illustrated in Figure 1. The computer controlled servo-motor (SEM Controlled Motor Technology) drives an 8-cm-diameter piston to produce pulsatile flow in the test loop. The piston motion curve can be created, modified, and implemented by Motion Generator software. The piston head is connected to a liquid-filled Perspex box, inside which a collapsible left ventricular (LV) sac is installed. Upstream of the simulated LV is a left atrium chamber connected via a commercial tilting-disk valve. Downstream of the LV is a perspex test section simulating the aorta, inside which a transparent aortic valve model is installed. The afterload resistive and compliance elements are connected with the test section and then return back to the atrium. These elements can be tuned separately to obtain desirable physiological pressure and flow rate. Two pressure transducers (Model T4812AD-R) coupled with a calibrated multichannel amplifier (AM-PACK AP9991, Vivitro System Inc., Victorìa, B.C., Canada) were used to measure the ventricle and aortic pressure. The transducers are located respectively at the LV immediate exit and MHV five aorta diameters downstream, as illustrated in Figure 1. Figure 2 shows a typical pressure waveform recorded by an oscilloscope (Tektronix, TDS36). The ventricular and aortic pressures fall in the range of 0∼160 mm Hg and 60∼130 mm Hg, respectively. The heart rate was 63 beats per minute with 40% systolic duration. The flow rate was measured as 4.3 l/min by a calibrated rotameter. These parameters were selected to protect the transparent MHV model operating under prolonged physiologic condition. The inhouse-developed 1:1 bileaflet MHV model, as shown in Figure 3, has a geometry and opening and closing angles similar to that of the SJM 29 mm MHV. Its transparency enables the closure flow field measurement by the PIV technique.

Figure 1.
Figure 1.:
The pulsatile flow test loop experimental setup.
Figure 2.
Figure 2.:
Typical pressure wave form recorded by oscilloscope.
Figure 3.
Figure 3.:
The inhouse-developed bileaflet mechanical heart valve model.

PIV System

The TSI Insight PIV system (TSI Incorporated, Ithaca, NY) was used in this study. The double-pulsed Nd:YAG laser (maximum 50 mJ/pulse) provides illumination for the flow field plane. A CCD camera (1000*1016 pixel), coupled with an X-Y traveling mechanism (revolution step 0.01 mm) and Stemi 2000-C microscope (Zeiss), precisely position the observation of the minute channel flow upon MHV closure. The system magnification can be gradually adjusted and the maximum value is up to 3.2. The minimum velocity vector spacing is 0.09 mm under 50% overlapped Nyquist sampling.

Leaflet thickness (1 mm) is used to calibrate the velocity value when processing PIV images in Insight software. The corresponding vector files are then loaded into Tecplot to present PIV data with velocity, strain rate, and vorticity.

Working Fluid and Seeding Particle

The working fluid was composed of 79% saturated aqueous sodium iodide, 20% percent pure glycerol, and 1% of distilled water by volume. This composition yields a kinematics viscosity of 3.4 × 10–6 m2/s (3.4 cS), matching that of human blood at higher shear rates. The refractive index of this fluid was measured as 1.49, same as the test section (perspex), hence eliminating the refractive deformation when light passes through the curved liquid-solid interfaces. The seeding particle, 10 μm silver-coated glass sphere, was selected because of its good image contrast and suitable particle image diameter.

Triggering Setup

The frame rate of the CCD camera, 30 frames per second, is not adequate for analyzing one cycle of MHV operation, especially when its opening and closing process is <50 milliseconds. Hence a triggering method was developed. A photoelectric sensor (HPX-NT1, Yamatake), its position fixed as in Figure 4, captured the closing movement of MHV leaflet. The sensor signal was imputed into a Intel 82C54 Programmable Interval Counter/Timer (1600 Data Acquisition Board, Keithley Instruments) for time delay via a written program. The delayed signal was connected with synchronizer for PIV trigger with a time step of 10 μs. The PIV frame was taken only at specific instant in each cycle, and 100 cycles of images at this instant were saved for postprocessing

Figure 4.
Figure 4.:
Fixed position of photoelectric sensor capturing closing movement of a mechanical heart valve leaflet.

With the increase of system magnification, the sensor position was finely tuned closer to the leaflet full-closure position so that the time delay was triggered within a narrower orifice. The leaflet tip velocities within the decreasing gap dimensions were then obtained.

Local Flow Field Observation

A complete transparent MHV model enables the investigation of channel flow between the occluder and orifice wall. As the closing process proceeds, the channel becomes narrower until zero gap when the valve is considered fully closed. Figure 5 schematically depicts the local flow field when the MHV nearly impacts on the housing wall. Three profiles were selected within the gap: profile 1 along the leading tip, profile 3 along the trailing tip, and profile 2 between them.

Figure 5.
Figure 5.:
Schematic depiction of a local flow field when the mechanical heart valve nearly impacts the housing wall.

Results

Leaflet Closure Velocity

The MHV average tip velocity within Δt, i.e., from zero instant to the leaflet full-closure instant, can be calculated by analyzing leaflet position in the PIV image. Due to the variation from beat to beat, Δt was selected as the value at which the occluder reaches its full closure position over 85% of 100 continuous cardiac cycles. Table 1 summarizes the average leaflet tip velocities within various gap dimensions, in which α is the angle the leaflet oriented with the transverse direction, as in Figure 5. The results demonstrate that the leaflet tip velocity accelerates as the closing process proceeds.

Table 1
Table 1:
Average Leaflet Velocities within Various Gap Dimensions

Flow Field Results

Under magnification of 1.8, the channel dimension was narrowed from 1.1∼1.4 mm to 0.5∼0.8 mm. Typical velocity map, speed profile, and vorticity plot with different gap sizes are demonstrated in Figures 6–8. To further increase spatial resolution, magnification of 3.2 was applied. The dimension of observation field was thus decreased to about 2.70 × 2.70 mm. Related PIV measurements when the gap is 0.2∼0.3 mm and <0.1 mm are shown in Figures 9 and 10.

Figure 6.
Figure 6.:
With the gap at about 1.1–1.4 mm: (a) velocity map, (b) speed profile, and (c) vorticity plot.
Figure 7.
Figure 7.:
With the gap at about 0.7–1.1 mm: (a) velocity map, (b) speed profile, and (c) vorticity plot.
Figure 8.
Figure 8.:
With the gap at about 0.5–0.8 mm: (a) velocity map, (b) speed profile, and (c) vorticity plot.
Figure 9.
Figure 9.:
With the gap at about 0.2–0.3 mm: (a) velocity map, (b) speed profile, and (c) vorticity plot.
Figure 10.
Figure 10.:
With the gap at <0.1: (a) velocity map, (b) zoomed-in velocity map around the gap region, and (c) vorticity plot.

Discussion

When the gap is about 1.1∼1.4 mm, as in Figure 6, the leaflet is pushed to close by the backwind flow with the fluid velocity perpendicular to the surface. In the upwind region, the flow adjacent to the leaflet is perpendicular to the solid surface, which is driven in motion by the valve rotation. While apart from the surface, the flow field is the combined result of the back flow through the gap and the occluder-driven flow. Thus, the fluid velocity in this area diverts parallel to the axial direction. A vortex flow is formed around the trailing tip, produced by the solid-fluid interaction (SFI) at the tip and backflow around the gap. The peak velocity is found around 0.27 m/s. The speed profile inside the gap shows the highest magnitude at the leading tip and lowest magnitude at the trailing tip.

When the gap decreases to about 0.7∼1.1 mm, as in Figure 7, both the backflow momentum and SFI around the occluder become stronger as the peak flow velocity reaches 0.36 m/s. The intensity of the trailing vortex and the magnitude of the speed profiles also increase. When the gap continuously decreases to about 0.5∼0.8 mm, as in Figure 8, the flow momentum inside the gap further strengthens, possibly due to the increased aortic-ventricular pressure gradient and ever-narrowing gap dimension. The resultant flow in the upwind region, as described earlier, is stronger than that in the backwind region. The maximum velocity at the leading tip reaches 0.4 m/s. The vorticity also strengthens to about 420 per second.

Figure 9 shows the flow field when the gap is about 0.2∼0.3 mm. Due to the stronger backflow momentum from the gap and backwind region, together with the acceleration of occluder motion, the peak flow velocity increases to 0.7 m/s at the upwind region. When the gap is <0.1 mm, as in Figure 10, the jet with magnitude of 2.3 m/s is observed at the immediate exit of the gap. The zoom-in map shows that the high speed flow coming from the leading tip encounters a sudden geometry expansion. Then it mixes with relatively weak flow in the upwind region, which may result in local pressure reduction for possible cavitation occurrence. The vorticity around the leading tip reaches about 1400 per second.

Conclusion

For the first time, the development of squeeze flow is verified experimentally. The PIV system coupled with a microscope enables gap flow observation from the dimension of 1.1∼1.4 mm to <0.1 mm. As the gap between the tip of the valve occluder and housing wall becomes narrower, evidence of high-speed jet flow becomes more apparent. The flow velocity between 1 and 3 m/s is observed rushing out the gap when the gap dimension is <0.1 mm. This high-speed jet may cause a low-pressure center around the leading tip with the potential for cavitation occurrence.

The squeezing velocity shown in this study differs from other CFD works, possibly because of the varied valve position or working conditions. The limitation of our study is that there is a difference in material density between our clear MHV model and commercial ones, which may result in different MHV closure dynamics.

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