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A. Edwards, P. Fitzmorris, S. Pamboukian, James George, C. Wilcox, S. Peter (2018)
Association of Pulsatility with Gastrointestinal Bleeding in a Cohort of HeartMate II RecipientsASAIO Journal, 64
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Satoru Kishimoto, Y. Takewa, T. Tsukiya, T. Mizuno, Kazuma Date, H. Sumikura, Yutaka Fujii, Kentaro Ohnuma, K. Togo, N. Katagiri, N. Naito, Yuichiro Kishimoto, Y. Nakamura, M. Nishimura, E. Tatsumi (2018)
Novel temporary left ventricular assist system with hydrodynamically levitated bearing pump for bridge to decision: initial preclinical assessment in a goat modelJournal of Artificial Organs, 21
W. Chan, K. Ooi, Yan-Chuan Loh (2007)
Numerical and in vitro investigations of pressure rise in a new hydrodynamic blood bearing.Artificial organs, 31 6
Liangfan Zhu, Yue Wu, Yun Luo (2016)
Experimental evaluation of a novel injection suspended impeller for implantable centrifugal blood pumpInternational Journal of Applied Electromagnetics and Mechanics, 52
L. Leslie, L. Marshall, A. Devitt, A. Hilton, G. Tansley (2013)
Cell exclusion in couette flow: evaluation through flow visualization and mechanical forces.Artificial organs, 37 3
E. Muijderman (1965)
SPIRAL GROOVE BEARINGSIndustrial Lubrication and Tribology, 17
E. Potapov, M. Loebe, B. Nasseri, Hendryk Sinawski, A. Koster, H. Kuppe, G. Noon, M. Debakey, R. Hetzer (2000)
Pulsatile Flow in Patients With a Novel Nonpulsatile Implantable Ventricular Assist DeviceCirculation: Journal of the American Heart Association, 102
Qing Han, J. Zou, X. Ruan, Xin Fu, Huayong Yang (2012)
A novel design of spiral groove bearing in a hydrodynamically levitated centrifugal rotary blood pump.Artificial organs, 36 8
Yubing Shi, T. Korakianitis (2006)
Numerical simulation of cardiovascular dynamics with left heart failure and in-series pulsatile ventricular assist device.Artificial organs, 30 12
L. Belyaev, A. Ivanchenko, A. Zhdanov, V. Morozov (2015)
Mathematical Modeling of Hemodynamic Characteristics of Pumps for Pulsatile Circulatory Support SystemsBiomedical Engineering, 49
Felipe Amaral, S. Groß-Hardt, D. Timms, Christina Egger, U. Steinseifer, T. Schmitz-Rode (2013)
The spiral groove bearing as a mechanism for enhancing the secondary flow in a centrifugal rotary blood pump.Artificial organs, 37 10
T. Kink, H. Reul (2004)
Concept for a new hydrodynamic blood bearing for miniature blood pumps.Artificial organs, 28 10
D. Timms (2011)
A review of clinical ventricular assist devices.Medical engineering & physics, 33 9
T. Masuzawa (2017)
Magnetically suspended motor system applied to artificial hearts and blood pumpsProceedings of the Institution of Mechanical Engineers, Part I: Journal of Systems and Control Engineering, 231
O. Frazier, T. Myers, S. Westaby, I. Gregoric (2003)
Use of the Jarvik 2000 Left Ventricular Assist System as a Bridge to Heart Transplantation or as Destination Therapy for Patients With Chronic Heart FailureAnnals of Surgery, 237
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+ird-generation ventricular assist devices
T. Yamane, O. Maruyama, M. Nishida, R. Kosaka, D. Sugiyama, Yusuke Miyamoto, H. Kawamura, Takahisa Kato, T. Sano, Takeshi Okubo, Y. Sankai, O. Shigeta, T. Tsutsui (2007)
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M. Nishida (2017)
Artificial hearts—recent progress: republication of the article published in the Japanese Journal of Artificial OrgansJournal of Artificial Organs, 20
Qi Liu, Ye Jiahui, Guang Zhang, Zhe Lin, Hong-guang Xu, H. Jin, Zuchao Zhu (2019)
Study on the metrological performance of a swirlmeter affected by flow regulation with a sleeve valveFlow Measurement and Instrumentation
Qing Han, X. Ruan, Wen-yu Chen, Xin Fu (2013)
Numerical simulation and experimental research on passive hydrodynamic bearing in a blood pumpChinese Journal of Mechanical Engineering, 26
K. Yamazaki, S. Saito, S. Kihara, O. Tagusari, H. Kurosawa (2007)
Completely pulsatile high flow circulatory support with a constant-speed centrifugal blood pump: mechanisms and early clinical observationsGeneral Thoracic and Cardiovascular Surgery, 55
Hindawi Journal of Healthcare Engineering Volume 2019, Article ID 8065920, 6 pages https://doi.org/10.1155/2019/8065920 Research Article The Impact of Pulsatile Flow on Suspension Force for Hydrodynamically Levitated Blood Pump 1,2 1 2,3 2,4 Yang Fu , Yimin Hu , Feng Huang , and Maoying Zhou School of Mechanical & Energy Engineering, Zhejiang University of Science & Technology, Hangzhou, China State Key Laboratory of Fluid Power & Mechatronic Systems, Zhejiang University, Hangzhou, China College of Metrology & Measurement Engineering, China Jiliang University, Hangzhou, China School of Mechanical Engineering, Hangzhou Dianzi University, Hangzhou, China Correspondence should be addressed to Feng Huang; hf@cjlu.edu.cn Received 25 August 2018; Revised 28 March 2019; Accepted 21 May 2019; Published 3 June 2019 Academic Editor: Jinshan Tang Copyright © 2019 Yang Fu et al. +is is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited. Hydrodynamically levitated rotary blood pumps (RBPs) with noncontact bearing are effective to enhance the blood compatibility. +e spiral groove bearing (SGB) is one of the key components which offer the suspension force to the RBP. Current studies focus on the suspension performance of the SGB under continuous flow condition. However, the RBP shows pulsatile characteristics in the actual clinical application, which may affect the suspension performance of the SGB. In this paper, the impact of pulsatile flow upon the suspension force from the SGB is studied. A model of the SGB with a groove formed of wedge-shaped spirals is built. +en, the CFD calculation of the hydrodynamic force offered by designed SGB under simulated pulsatile flow is introduced to obtain the pulsatile performance of the suspension force. +e proposed method was validated by experiments measuring the hydrodynamic force with different bearing gaps. +e results show that the suspension force of the SGB under pulsate flow is the same as under steady flow with equivalent effective pressure. +is paper provides a method for suspension performance test of the SGB. showed that the hydraulic performance of the RBP was not 1. Introduction influenced compared to the contact bearing. Yamane et al. Implanted rotary blood pumps (RBPs) are considered as [7] made a new groove shape for the SGB to levitate the replacement therapy for heart disease due to the lack of impellers of RBP, and thrombus formation was reduced in organ donation. +e RBP requires a rotor bearing to their design. Experimental studies by Zhu et al. [8] pointed maintain longtime operation. Compared with contact out that the pressure generated by SGBs is sufficient to bearings, noncontact bearings avoid wearing and thrombus support the rotor. Han et al. [9, 10] developed a novel SGB formation around the bearing [1]. Magnetic bearings have that the groove width decreases with increasing spiral radius been applied in RBPs, enhancing the blood compatibility of to improve washout of the RBP. +e exposure time of blood flow to high shear stresses of the RBP is demanded to be the RBPs [2]. However, magnetic bearings need sensors and control system to guarantee the suspension, which increases lower in order to improve its hemocompatibility. Amaral the complexity of the implanted device. +us, hydrodynamic et al. [11] introduced an optimized SGB design which can bearings, which offer suspension force depending on its enhance the washout flow between the rotor and pump hydraulic characteristics, were widely studied for RBPs casing, significantly decreasing the exposure time and im- [3–5]. proving the overall efficiency of the pump. Spiral groove bearing (SGB), which is small in size and +e existing studies of the SGBs are mainly focused on has excellent loading capacity, is considered as a good the suspension performance under continuous flow con- structure used for the hydrodynamic bearing. +e SGB was dition, where the RBPs are tested with given constant flow first introduced by Kink and Reul in the RBP to minimize the rate and the outlet pressure of zero. However, in the actual size of the implant device, and the mock-loop test result [6] clinical application, the inlet pressure and outlet pressure of 2 Journal of Healthcare Engineering the RBPs vary according to the periodic pressure change of Inlet the ventricular, as the RBPs are connected between the left Impeller ventricular and aorta [12–14]. erefore, the �ow of the RBPs shows pulsatile characteristics even with �xed rotating speed [12, 13]. Studies [15–17] show that the pulsatile Rotor characteristics of the RBPs a€ect the performance of the Outlet RBPs, such as hydraulic characteristics, blood compatibility, Shaf t Stator etc. However, no relevant studies were reported about the impact of the RBPs’ pulsatile characteristics on the sus- pension performance of the SGBs. Magnet For the conventional SGB with logarithmic spiral grooves, mathematical analysis [18] has been deduced with Spiral groove bearings the conclusion that the hydrodynamic force on the bearing Figure 1: e schematic of the RGB. was not a€ected by the pressure variation. As mentioned in [9], the RBP used novel SGBs with the groove formed of wedge-shaped spirals has superior load/�ow characteristics, grooves. e purpose of the novel SGB structure is to but it is diŒcult to construct CFD model of the RBP for maintain high load-carrying capacity while producing a analysis of its suspension performance. us, computational large �ow rate to reduce blood damage. e two groove �uid dynamics (CFD) [19] analyses and experiments were pro�les in polar coordinates are expressed as conducted in this article to investigate the behavior of SGBs θ tan α under physiological pulse conditions. e remainder of this r r e , i 1 article o€ers the following: (1) θ − br /r tan α j () () i i r r e , j 1 (1) CFD model of the SGB with wedge-shaped spiral grooves is built. en, the CFD calculation of the where r is the radius, b is the groove width, θ is the phase hydrodynamic force o€ered by designed SGB under angle, α is the spiral angle and remains constant, r is the simulated pulsatile �ow is introduced to obtain the radius at zero polar angle, and b is the groove width at r . 1 1 pulsatile performance of the suspension force. And the groove width is a function of r: (2) e proposed method is validated by comparing b − b 2 1 experimentally measured suspension force with CFD b(r) r − r + b , (2) 1 1 r − r 2 1 calculation under di€erent bearing gaps. where b b(r ), b b(r ), and b > b . us, the groove e impact of pulse �ow on the suspension performance 1 1 2 2 1 2 width decreases along the radius. e geometry of a SGB is of the SGB to the RBP has been studied in this paper, which shown in Figure 2. e groove depth and bearing gap are h provides a method for suspension performance test of the 0 and h , respectively. e total distance between the groove SGB. e CFD calculation and experiment test have been 2 and the corresponding surface is h h + h . implemented. Also, the results show that the suspension 1 0 2 force of the SGB under pulsate �ow is the same as under steady �ow with equivalent e€ective pressure. 2.2. Numerical Analysis. Numerical simulation was carried out to calculate the suspension force of the SGB under 2. Materials and Methods continuous and pulsatile �ow condition. According to Han’s 2.1. Structure of SGB. e structure of the RBP with hy- study [9], the geometrical parameters of the SGB used in the drodynamic bearings is shown in Figure 1. e pump simulation are listed in Table 1, with groove depth and the consists of the pump housing, impeller, stator, and shaft. e spiral angle of 80 μm and 20 . Also, the number of grooves SGB is �xed on the rotor which o€ers suspension force to was set to 8. levitate the rotor, whose performance will be discussed. As shown in Figure 3, three-dimensional grids of the ere is a big di€erence in size between the pump and the �ow �eld were developed with ANSYS ICEM CFD. Prism groove, where the size order of the groove depth and the grids are generated using the same settings for all cases, and −5 −2 bearing gap is 10 m and the pump as 10 m. As mentioned the boundary-layer grids include more than 5 layers of el- in the method part, more than 1,800,000 elements are used ements. e total number of elements was between 1,800,000 to fully represent the computational domain of the SGB. and 3,000,000 according to the actual �uid domain. A mesh Correspondingly, the number of grids will be very huge to re�nement study was conducted for 50,000 up to 10,000,000 cover the whole blood pump, which will exceed the capa- elements. e estimated hydrodynamic force showed a bility of general computers. us, only SGB is modeled and deviation lower than 5% for meshes over 1,700,000 elements. studied in this paper. e computation was conducted through ANSYS CFX and e wedge-shaped SGB is based on the design of Han assumed to achieve convergence when the RMS (root mean −5 et al. [9], where the groove width decreases along the �ow square) residuals were below 1e . In this paper, simulations path. us, the relative motion between the SGB and the were carried under continuous �ow and pulsatile �ow as corresponding surface facilitates the �ow through the follows. Journal of Healthcare Engineering 3 Figure 2: e axial and cross-sectional view of a SGB. Table 1: Geometrical parameters of tested SGB. with time invariant boundary conditions based on Pao-Plv at a certain time, as shown in Table 2. Inner radius r 5 mm Outer radius r 9.5 mm Groove angle α 20 2.3. Experimental Validation. Experiments were carried out Groove width b /b 3.92 mm/1.96 mm 1 2 to validate the suspension performance test method and the Groove depth h 80 μm e€ectiveness of the simulation presented above. e sche- Number of grooves k 8 matic of the experimental setup is shown in Figure 5, which is modi�ed from previous devices on suspension force test for First, steady-state simulations were performed to acquire hydrodynamically levitated blood pump reported in col- the suspension forced by the SGB. In the normal operation leagues’ research [11, 22]. A SGB manufactured with ABS was of the SGB in the RBP, the bearing gap is commonly between �xed on a motor shaft (EC32 Flat, maxon motor ag, Sachseln, Switzerland) which was controlled by a monitor (maxon 20 μm to 300 μm [7, 11, 20]. erefore, the bearing gap in the simulation was chosen from 20 μm to 300 μm, and the data motor ag, Sachseln, Switzerland). e motor was supported were calculated every 20 μm. e boundary condition was by a 5 mm lifting platform (Winner Optics, WN01VM5) with set with inlet and outlet pressure of zero. e estimated 5 μm resolution through a cantilever made of aluminum alloy. hydrodynamic force was further compared with the e 5 mm lifting platform was mounted on a 60 mm Z stage experiments. (Winner Optics, WN08VM60) that regulates height roughly. Second, numerical simulation was operated under e SGB to be tested was immerged in a cylindrical reservoir, pulsatile �ow condition to �gure out whether the suspension and the �uid was a mixture of water and glycerol with 38% force of the SGB was a€ected. Shi and Korakianitis [21] built glycerol in weight. A 6-DOF force and moment sensor (ATI Nano 43) was �xed between the reservoir and a X-Y stage a numerical model of the cardiovascular system, where the left ventricular pressure (Plv) and the aortic pressure (Pao) (Winner Optics, WN202WM25M) to adjust the SGB to the in healthy condition were given as shown in Figure 4. e center of the reservoir. All signals were acquired by a DAQ left ventricular pressure varies between 10 and 120 mmHg, card (National Instruments, Austin, Texas, USA), and a and the aortic pressure changes from 80 to 120 mmHg. In control program was written with LabVIEW (National In- the actual operation, the inlet and outlet of the RBP were struments, Austin, Texas, USA) to monitor the motor speed connected to the ventricular and aorta, respectively. and the sensor response. erefore, the pressure at r and r was set equal to Plv and In this experiment, the hydrodynamic force on the 1 2 Pao to simulate the pulsate �ow condition, which was close counter plane of the SGB with di€erent bearing gaps to the actual operation condition of the SGB. For com- changed by the elevator-platform was measured. According parison, a series of steady-state simulations were carried out to Newton’s third law, the suspension force o€ered by the 4 Journal of Healthcare Engineering 0 0.0002 0.0004 (m) 0.0001 0.0003 0.004 0.008 (m) 0.002 0.006 Figure 3: CFD mesh result of the SGB. Table 2: Boundary conditions for di€erent pressure heads. Time (s) Pressure at r (mmHg) Pressure at r (mmHg) 120 1 2 0.0 1.2 94.3 0.2 7.2 83.5 0.4 120.3 120.1 0.6 39.6 102.1 0.8 2.3 88.8 results matched the experiment results well especially when the bearing gap was larger than a critical value, which was about 60 μm in this design. When the bearing gap was small, it was found that the suspension force of the simulation was 0 0.2 0.4 0.6 0.8 1 larger than the experimental value. As shown in Figure 6, the –20 Time t (s) suspension force showed a large discrepancy with the var- iation of the bearing gap when the bearing gap was below Pao 50 μm. In the experiment, the bearing gap was regulated by Plv the displacement platform, leading to the diŒculty in Figure 4: Left ventricular pressure (Plv) and aorta pressure (Pao) adjusting the bearing gap to a precision level, especially in with the cardiovascular model in healthy conditions [21]. the tiny distance range. erefore, the simulation result was di€erent from the experiment when the bearing gap was SGB was equal to the hydrodynamic force on the counter small. In general, the experiment result �ts the simulation. plane. e geometrical parameters of the SGB were designed us, the conclusion could be made that the numerical the same to the simulation. e rotating speed of the motor simulation model built above was valid to estimate the was �xed at 3000 rpm, the same as the speci�ed speed of the suspension forced by the SGB. blood pump. e bearing gap ranged from 80 μm to 300 μm in 20 μm steps. 2.5. Impact of Pulsatile Flow on the Hydrodynamic Force. e hydrodynamic force under pulsatile �ow was calculated 2.4. Validation of the Model Accuracy. e suspension force by CFD, where the pressure at inlet and outlet of the SGB of the SGB measured by the experiment was compared with was set equal to Plv and Pao, as shown in Figure 7. First, the the CFD calculated result to validate the e€ectiveness of the transient simulation was carried out with the pressure varied CFD model, as shown in Figure 6. In the experiment and continuously according to the Plv and Pao, and the hy- CFD calculation, the pressure of the inlet and outlet was set drodynamic force was calculated continuously. en, CFD to zero. calculation was carried out under steady state with several e suspension force o€ered by SGB decreases with the given pressures the same as the transient condition as increase of the bearing gap. It was found that the simulation comparisons. It can be found that the hydrodynamic force Pressure (mmHg) Journal of Healthcare Engineering 5 Motor Cantilever 5 mm Lifting Reservoir platform SGB Force sensor 60 mm Z stage X-Y stage Figure 5: Test system for the measurement of hydrodynamic force. 2.50 140 6 2.00 1.50 1.00 60 3 0.50 0.00 0 50 100 150 200 250 300 –0.50 0 0.2 0.4 0.6 0.8 1 Bearing gap (μm) –20 0 Time t (s) Experiments CFD Pao Transient Plv Steady state Figure 6: Comparison between experiment and simulation results under steady state. Figure 7: Comparison between transient and steady-state results by CFD calculation. under pulsatile �ow was the same as steady state value. In this calculation, the hydrodynamic force was calculated e€ective pressure. In this study, the simulation and exper- including the pressure on the surface of the SGB. us, the iments were implemented for the SGB, not including the hydrodynamic force was relative to the set pressure on inlet whole region of the RBP. e motion of the pump rotor is and outlet. rough comparison between the transient re- a€ected by the coupling of the suspension force of the SGB, sults and steady state results, it can be concluded that the the normal force of the impeller, and the magnetic force of suspension force of the SGB under pulsating �ow is the same the motor. In future works, the in�uence of the latter two as under steady �ow with equivalent e€ective pressure. forces will be considered and studied. 3. Conclusion Data Availability e impact of the pulsatile �ow on the suspension force of the SGB was studied in this paper. A model of the SGB with a e data used to support the �ndings of this study are groove formed of wedge-shaped spirals was built. CFD available from the corresponding author upon request. calculation of the designed SGB was carried out to obtain the e€ects of the suspension force according to the changing Conflicts of Interest �ow. e hydrodynamic force with di€erent bearing gaps was measured by experiment. e measured suspension e authors declare that they have no con�icts of interest. forces were in accord with the CFD calculation results under steady state, which validated the e€ectiveness of CFD cal- Acknowledgments culation for the SGB. Also, the CFD calculation results showed that the suspension force of the SGB under pulsating is work was supported by the National Natural Science �ow is the same as under steady �ow with equivalent Foundation of China (grant no. 51505455), funded by the Force (N) Pressure (mmHg) Force (N) 6 Journal of Healthcare Engineering assist device,” Circulation, vol. 102, no. 3, pp. III183–III187, Open Foundation of the State Key Laboratory of Fluid Power and Mechatronic Systems (nos. 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Nasseri et al., “Pulsatile flow in patients with a novel nonpulsatile implantable ventricular International Journal of Advances in Rotating Machinery Multimedia Journal of The Scientific Journal of Engineering World Journal Sensors Hindawi Hindawi Publishing Corporation Hindawi Hindawi Hindawi Hindawi www.hindawi.com Volume 2018 http://www www.hindawi.com .hindawi.com V Volume 2018 olume 2013 www.hindawi.com Volume 2018 www.hindawi.com Volume 2018 www.hindawi.com Volume 2018 Journal of Control Science and Engineering Advances in Civil Engineering Hindawi Hindawi www.hindawi.com Volume 2018 www.hindawi.com Volume 2018 Submit your manuscripts at www.hindawi.com Journal of Journal of Electrical and Computer Robotics Engineering Hindawi Hindawi www.hindawi.com Volume 2018 www.hindawi.com Volume 2018 VLSI Design Advances in OptoElectronics International Journal of Modelling & Aerospace International Journal of Simulation Navigation and in Engineering Engineering Observation Hindawi Hindawi Hindawi Hindawi Volume 2018 Volume 2018 Hindawi www.hindawi.com Volume 2018 www.hindawi.com Volume 2018 www.hindawi.com www.hindawi.com www.hindawi.com Volume 2018 International Journal of Active and Passive International Journal of Antennas and Advances in Chemical Engineering Propagation Electronic Components Shock and Vibration Acoustics and Vibration Hindawi Hindawi Hindawi Hindawi Hindawi www.hindawi.com Volume 2018 www.hindawi.com Volume 2018 www.hindawi.com Volume 2018 www.hindawi.com Volume 2018 www.hindawi.com Volume 2018
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Published: Jun 3, 2019
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