Abstract:In this study, an infusion roller pump comprising two separate innovative resilient tube designs is presented. The first incorporates the flexible tubing cross-section area in its relaxed state as a lenticular one for power reduction reasons. The second keeps the previous lenticular cross-section along its length, while it additionally incorporates an inflating portion, for creating a momentary flow positive pulse to balance the void generated by the roller disengagement. Fluid–Structure Interaction (FSI) simu… Show more
“…Similar trends were predicted elsewhere. 7–10 Figure 4.Outlet flow rate versus roller angle location. (a) Tube A, (b) Tube B, (c) Tube C. Symbols: (diamond) time mean, (circle) standard deviation.…”
Section: Resultsmentioning
confidence: 99%
“…Apparently, if the inflated part were absent, the outlet flow rate reduction would be greater. In a recent published numerical work by the same group 10 examining various lengths of the inflated part of Tube C, the predicted minimum flow pulsation was 32%.…”
Section: Flow Ratementioning
confidence: 94%
“…Similar trends were predicted elsewhere. [7][8][9][10] More specifically, the outlet flow rate starts being reduced from φ = 130°(Tube B) or 150°(Tube A and C) till φ = 50°(Tube A) or 70°(Tube B and C). Higher deceleration rates occur in the interval φ = 0°to φ = 50°for Tube A and B, and from φ = 30°to φ = 70°for Tube C. The higher flow rate reduction is attributed to the increase of the tube volume during the disengagement phase, so that eventually a smaller fluid mass is discharged at the pump outlet.…”
Section: Flow Ratementioning
confidence: 99%
“…Moreover, it has to be stressed that there is no CFD code nowadays that can solve the flow if the tube is deeply occluded due to singularities which appear when the computational cells touch each other at the occluded part of the tube. Recent attempts by this group 10 using ANSYS software with 3D fluid-structure interaction (FSI) simulations in a lenticular tube of a two-roller peristaltic pump ended up with a minimum gap of 0.08 mm or 4.3% of the tube’s inner diameter. Another group 11 using a finite element source code with a CFD solver studied the 3D flow in a circular tube of a three-roller pump with a minimum gap of 0.023 mm or 1.7% of the tube inner diameter.…”
A drug infusion peristaltic pump is experimentally studied, examining its performance for three flexible tubes, two cylindrical, and an innovative one of lenticular cross-section with an inflated part. Using water as flowing medium, the pump outlet flow rates were measured at nine phases of the semi-period, based on phase-locked 2D-PIV data. The roller disengagement phase showed to cause a reduction of the outlet flow rate, and in a lesser degree, the engagement phase. Flow acceleration at the pump outlet occurred when only one roller was squeezing the tube. The gauge pressure waveforms at the pump inlet and outlet although noisy had a phase lead with respect to the flow rate. According to the pump motor current waveform, the work of the forces necessary for the tube deformation was about 10 times higher than that of the fluid viscous and inertial forces. Among the three examined flexible tubes, the pump performance was the best when the lenticular tube was used, presenting the highest volumetric efficiency and the smallest outlet flow rate pulsations, pressure amplitudes, and energy consumption. The high pump performance is attributed to the innovative inflated part of the lenticular tube, its cross-sectional shape and its higher compliance compared to the other tubes.
“…Similar trends were predicted elsewhere. 7–10 Figure 4.Outlet flow rate versus roller angle location. (a) Tube A, (b) Tube B, (c) Tube C. Symbols: (diamond) time mean, (circle) standard deviation.…”
Section: Resultsmentioning
confidence: 99%
“…Apparently, if the inflated part were absent, the outlet flow rate reduction would be greater. In a recent published numerical work by the same group 10 examining various lengths of the inflated part of Tube C, the predicted minimum flow pulsation was 32%.…”
Section: Flow Ratementioning
confidence: 94%
“…Similar trends were predicted elsewhere. [7][8][9][10] More specifically, the outlet flow rate starts being reduced from φ = 130°(Tube B) or 150°(Tube A and C) till φ = 50°(Tube A) or 70°(Tube B and C). Higher deceleration rates occur in the interval φ = 0°to φ = 50°for Tube A and B, and from φ = 30°to φ = 70°for Tube C. The higher flow rate reduction is attributed to the increase of the tube volume during the disengagement phase, so that eventually a smaller fluid mass is discharged at the pump outlet.…”
Section: Flow Ratementioning
confidence: 99%
“…Moreover, it has to be stressed that there is no CFD code nowadays that can solve the flow if the tube is deeply occluded due to singularities which appear when the computational cells touch each other at the occluded part of the tube. Recent attempts by this group 10 using ANSYS software with 3D fluid-structure interaction (FSI) simulations in a lenticular tube of a two-roller peristaltic pump ended up with a minimum gap of 0.08 mm or 4.3% of the tube’s inner diameter. Another group 11 using a finite element source code with a CFD solver studied the 3D flow in a circular tube of a three-roller pump with a minimum gap of 0.023 mm or 1.7% of the tube inner diameter.…”
A drug infusion peristaltic pump is experimentally studied, examining its performance for three flexible tubes, two cylindrical, and an innovative one of lenticular cross-section with an inflated part. Using water as flowing medium, the pump outlet flow rates were measured at nine phases of the semi-period, based on phase-locked 2D-PIV data. The roller disengagement phase showed to cause a reduction of the outlet flow rate, and in a lesser degree, the engagement phase. Flow acceleration at the pump outlet occurred when only one roller was squeezing the tube. The gauge pressure waveforms at the pump inlet and outlet although noisy had a phase lead with respect to the flow rate. According to the pump motor current waveform, the work of the forces necessary for the tube deformation was about 10 times higher than that of the fluid viscous and inertial forces. Among the three examined flexible tubes, the pump performance was the best when the lenticular tube was used, presenting the highest volumetric efficiency and the smallest outlet flow rate pulsations, pressure amplitudes, and energy consumption. The high pump performance is attributed to the innovative inflated part of the lenticular tube, its cross-sectional shape and its higher compliance compared to the other tubes.
“…This finding suggests that the O-shaped setting is more suitable for blood and other cell-containing fluids, as it poses less hemolysis, or cytolysis in general, risk. Backflow suppression and uniformization of roller pump outflow were addressed by Manopoulos et al [15] by introducing an appropriate inflating portion of the deformable tube, thus producing momentum to compensate for the negative pressure gradient at the outlet of the pump that occurs when there is zero occlusion by a roller.…”
Peristaltic motion arises in many physiological, medical, pharmaceutical and industrial processes. Control of the fluid volume rate and pressure is crucial for pumping applications, such as the infusion of intravenous liquid drugs, blood transportation, etc. In this study, a simulation of peristaltic flow is presented in which occlusion is imposed by pairs of circular rollers that squeeze a deformable channel connected to a reservoir with constant fluid pressure. Naturally, this kind of flow is laminar; hence, the computation occurred in this context. The effect of the number and speed of the pairs of rollers, as well as that of the intrapair roller gap, is investigated. Non-Newtonian fluids are considered, and the effect of the shear-thinning behavior degree is examined. The volumetric flow rate is found to increase with an increase in the number of rollers or in the relative occlusion. A reduction in the Bird–Carreau power index resulted in a small reduction in transport efficiency. The characteristic of the pumping was computed, i.e., the induced pressure as a function of the fluid volume rate. A strong positive correlation exists between relative occlusion and induced pressure. Shear-thinning behavior significantly decreases the developed pressure compared to Newtonian fluids. The immersed boundary method on curvilinear coordinates is adapted and validated for non-Newtonian fluids.
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