A One-Dimensional Model of a False AneurysmIJRESJOURNAL
ABSTRACT:A false aneurysm is a hematoma, i.e. collection of blood outside of a blood vessel, that forms due to a hole in the wall of an artery. This represents a serious medical condition that needs to be monitored and, under certain conditions, treated urgently. In this work a one-dimensional model of a false aneurysm is proposed. The new model is based on a one-dimensional model of an artery previously presented by the authors and it takes into account the interaction between the hematoma and the surrounding muscle material. The model equations are derived using rigorous asymptotic analysis for the case of a simplified geometry. Even though the model is simple it still supports a realistic behavior for the system consisting of the vessel and the hematoma. Using numerical simulations we illustrate the behavior of the model. We also investigate the effect of changing the size of the hematoma. The simulations show that our model can reproduce realistic solutions. For instance we show the typical strong pulsation of an aneurysm by blood entering the hematoma during the work phase of the cardiac cycle, and the blood returning to the vessel during the resting phase. Also we show that the aneurysm grows if the pulse rate is increased due to, e.g., a higher work load.
A One-Dimensional Model of a False AneurysmIJRESJOURNAL
ABSTRACT:A false aneurysm is a hematoma, i.e. collection of blood outside of a blood vessel, that forms due to a hole in the wall of an artery. This represents a serious medical condition that needs to be monitored and, under certain conditions, treated urgently. In this work a one-dimensional model of a false aneurysm is proposed. The new model is based on a one-dimensional model of an artery previously presented by the authors and it takes into account the interaction between the hematoma and the surrounding muscle material. The model equations are derived using rigorous asymptotic analysis for the case of a simplified geometry. Even though the model is simple it still supports a realistic behavior for the system consisting of the vessel and the hematoma. Using numerical simulations we illustrate the behavior of the model. We also investigate the effect of changing the size of the hematoma. The simulations show that our model can reproduce realistic solutions. For instance we show the typical strong pulsation of an aneurysm by blood entering the hematoma during the work phase of the cardiac cycle, and the blood returning to the vessel during the resting phase. Also we show that the aneurysm grows if the pulse rate is increased due to, e.g., a higher work load.
Echo assesment of Aortic Stenosis and Regurgitationdrpraveen1986
A simple ppt presentation on echo assesment of AS and AR. Don forget to leave a comment if u find this ppt useful. - Dr. Praveen Babu, Vijaya HOspital, Chennai
Transposition of Great Arteries;TGA,Firas Aljanadi,MDFIRAS ALJANADI
presentation about the Transposition of great arteries.Definition,Epidemiology,History,Embryology,Classification,Anatomy,Coronary arteries,Physiology,natural history,clinical presentation,doagnosis,management.palliative and definitive treatment,Arterial switch operation,atrial switch,senning,mustard,special cases,with VSD ,with PS.
Hemodynamic assessment of partial mechanical circulatory support: data derive...Paul Schoenhagen
Partial mechanical circulatory support represents a new concept for the treatment of advanced heart failure. The Circulite Synergy Micro Pump®, where the inflow cannula is connected to the left atrium and the outflow cannula to the right subclavian artery, was one of the first devices to introduce this concept to the clinic. Using computational fluid dynamics (CFD) simulations, hemodynamics in the aortic tree was visualized and quantified from computed tomography angiographic (CTA) images in two patients. A realistic computational model was created by integrating flow information from the native heart and from the Circulite device. Diastolic flow augmentation in the descending aorta but competing/antagonizing flow patterns in the proximal innominate artery was observed. Velocity time curves in the ascending aorta correlated well with those in the left common carotid, the left subclavian and the descending aorta but poorly with the one in the innominate. Our results demonstrate that CFD may be useful in providing a better understanding of the main flow patterns in mechanical circulatory support devices.
Del 10 al 14 de octubre de 2016, se realizó en la diócesis de San Cristóbal de Las Casas, Chiapas, el encuentro de Obispos presidentes de las Comisiones Episcopales de Pastoral Indígena de Centroamérica, México y Panamá, convocador por el Departamento de Cultura y Educación del CELAM.
Echo assesment of Aortic Stenosis and Regurgitationdrpraveen1986
A simple ppt presentation on echo assesment of AS and AR. Don forget to leave a comment if u find this ppt useful. - Dr. Praveen Babu, Vijaya HOspital, Chennai
Transposition of Great Arteries;TGA,Firas Aljanadi,MDFIRAS ALJANADI
presentation about the Transposition of great arteries.Definition,Epidemiology,History,Embryology,Classification,Anatomy,Coronary arteries,Physiology,natural history,clinical presentation,doagnosis,management.palliative and definitive treatment,Arterial switch operation,atrial switch,senning,mustard,special cases,with VSD ,with PS.
Hemodynamic assessment of partial mechanical circulatory support: data derive...Paul Schoenhagen
Partial mechanical circulatory support represents a new concept for the treatment of advanced heart failure. The Circulite Synergy Micro Pump®, where the inflow cannula is connected to the left atrium and the outflow cannula to the right subclavian artery, was one of the first devices to introduce this concept to the clinic. Using computational fluid dynamics (CFD) simulations, hemodynamics in the aortic tree was visualized and quantified from computed tomography angiographic (CTA) images in two patients. A realistic computational model was created by integrating flow information from the native heart and from the Circulite device. Diastolic flow augmentation in the descending aorta but competing/antagonizing flow patterns in the proximal innominate artery was observed. Velocity time curves in the ascending aorta correlated well with those in the left common carotid, the left subclavian and the descending aorta but poorly with the one in the innominate. Our results demonstrate that CFD may be useful in providing a better understanding of the main flow patterns in mechanical circulatory support devices.
Del 10 al 14 de octubre de 2016, se realizó en la diócesis de San Cristóbal de Las Casas, Chiapas, el encuentro de Obispos presidentes de las Comisiones Episcopales de Pastoral Indígena de Centroamérica, México y Panamá, convocador por el Departamento de Cultura y Educación del CELAM.
Relish the togetherness within an enchanting Villa with gracious living spaces, enjoying magical views of distant Kote Betta mountain. The villa features a king-size bedroom, a dressing room, black stone and wood bathroom, and a spacious living room that leads to a balcony overlooking the lush green valley and the mountain beyond.- Plinth Area - 1200 Square feet
Join us for a series of introductory and technical sessions on AWS Big Data solutions. Gain a thorough understanding of what Amazon Web Services offers across the big data lifecycle and learn architectural best practices for applying those solutions to your projects.
We will kick off this technical seminar in the morning with an introduction to the AWS Big Data platform, including a discussion of popular use cases and reference architectures. In the afternoon, we will deep dive into Machine Learning and Streaming Analytics. We will then walk everyone through building your first Big Data application with AWS.
Statistical analysis for measuring the effects of stenotic shapes and spiral ...Iwate University
Numerical simulations have been done for a statistical analysis to investigate the effect of stenotic shapes and spiral flows on wall shear stress in the three-dimensional idealized stenotic arteries. Non-Newtonian flow has been taken for the simulations. The wall of the vessel is considered to be rigid. Physiological, parabolic and spiral velocity profile has been imposed for inlet boundary condition. Moreover, the time-dependent pressure profile has been taken for outlet boundary condition. Reynolds number at the inlet has been ranged approximately from 86 to 966 for the investigation. Low Reynolds number k-w model has been used as governing equation. 120 simulations have been performed for getting the numerical results. However, the numerical results of wall shear stress have been taken for the statistical analysis. The simulations and the statistical analysis have been performed by using ANSYS-18.1 and SPSS respectively. The statistical analyses are significant as p-value in all cases are zero. The eccentricity is the most influencing factor for WSSmax. The WSSmin has been influenced only by the flow spirality. The stenotic length has an influence only on the WSSmax whereas the stenotic severity has an influence on the WSSmax and WSSave.
EFFECT OF NEGATIVE ANGLE CANNULATION DURING CARDIOPULMONARY BYPASS – A COMPUT...ijbesjournal
Creation of emboli in the aortic root and changes in flow distribution between supra-aortic arteries and descending aorta can lead to stroke and perfusion related tissue damage during cardiopulmonary bypass. A thorough understanding of how the angle of cannulation affects the overall success of cardiopulmonary bypass during cannulation of the ascending aorta is needed. Previous simulation research has observed the effect of outflow cannula position by changing the location of the cannulation site to the subclavian artery and other vessels, as well as positions for innovative cannula designs. The purpose of this study is to evaluate the success of the procedure while using a straight cannula, modulating the angle of cannulation below horizontal in the frontal plane. A simplified geometry of the aorta was used. The success of the procedure was quantified by observing wall shear stress, normal stress, intra-fluid shear stress, and flow distribution. A numerical study was performed to solve the Reynolds Averaged Naiver Stokes governing equations, which were used in conjunction with a constant density fluid to simulate blood, and a realizable two-layer k-ε turbulence model
EFFECTS OF STENOSIS ON POWER LAW FLUID FLOW OF BLOOD IN BLOOD VESSELSJournal For Research
In this paper we assume that the blood is to be a Non-Newtonian and incompressible and Homogeneous fluid. An investigation has been done for the resistance to flow across mild stenosis situated symmetrically on steady blood flow through arteries with uniform or non-uniform cross section. An analytical solution for Power law fluid has been obtained. For the physiological insight of the problem various parameters systemic and pulmonary artery are taken and the study reveals that as the height of the stenosis increases in uniform or non-uniform portion of the artery, the resistance parameter and shear stress also steadily increases, whereas, flow rate decreases steadily and we analyze some cases between flux, pressure gradient and radius and give some significant results.
Casson flow of blood through an arterial tube with overlapping stenosisiosrjce
The objective of the present analysis is to study the effect of overlapping stenosis on blood flow
through an artery by taking the blood as Casson type non-Newtonian fluid. The expressions for flux and
resistance to flow have been studied here by assuming the stenosis is to be mild. The results are shown
graphically for different values of yield stress, stenosis length, stenosis height and discussed.
Simulation of Physiological Non-Newtonian Blood Flow through 3-D Geometry of ...Iwate University
Abstract: A numerical simulation has been performed to investigate blood flow behavior of three dimensional idealized carotid arteries. Non-Newtonian flow has been taken for the simulation. The wall of the vessel is considered to be rigid. Physiological and parabolic velocity profile has been imposed for inlet boundary condition. Reynolds number at the inlet has been ranged approximately from 86to 966 for the investigation. Low Reynolds number k-w model has been used as governing equation. The investigations have been carried out to characterize the flow behavior of blood. The numerical results have been presented in terms of wall shear stress distributions, streamlines contours and axial velocity contours. However, highest wall shear stress has been observed in the bifurcation area. Unexpectedly, transient or unstable flow has created flow disturbance regions in the arteries. Moreover, the disturbance of flow has risen as the severity of stenosis in the artery has been increased.
ANALYSIS OF FLOW CHARACTERISTICS OF THE BLOOD THROUGH CURVED ARTERY WITH MIL...indexPub
Narrowing of the arteries caused by atherosclerosis reduces blood flow to the heart, which results shows ischemia, angina pectoris, cerebral strokes, and other coronary artery disease signs and symptoms. Curvature is seen in blood vessels at various locations. The stenotic surface provides an additional curvature and the point of maximum shear which varies with the cross-section. A cylindrical form of the Navier-Stokes equations in polar coordinate system have been extended to include dynamic curvature along the axial direction. The blood flow behavior of taking different values of blood parameters like viscosity, the radius of the artery, and the thickness of the stenosis has been studied with and without curvature by using an extended blood flow model with dynamic curvature. Moreover, the aspects of blood flow, such as dynamic curvature velocity profile, volumetric flow rate, pressure drop, and shear stress, have been studied in relation to blood flow around curved arteries with stenosis, variations in the radii of the artery, thickness of the stenosis, and viscosity. The information may reveal that by increasing the values of curvature, viscosity, and thickness of stenosis, velocity, and volumetric flow rate can be quickly reduced. Increasing the curvature, viscosity, and thickness of stenosis also results in an increase in shear stress and a pressure drop. The presence of curved stenotic arteries has a significant impact on the flow parameters, and it is crucial to know about these dynamics in order to study the cardiovascular system.
Study on viscosity induced contrast in ultrasound color flow imaging of carot...IJECEIAES
Efficient imaging of blood flow disturbances resulted from carotid atherosclerosis plays a vital role clinically to predict brain stroke risk. Carotid atherosclerosis and its development is closely linked with raised blood viscosity. Therefore, study of viscosity changing hemodynamic effect has importance and it might be useful for improved examination of carotid atherosclerosis incorporating the viscosity induced contrast in conventional ultrasound imaging. This work considered the design of realistic models of atherosclerotic carotid artery of different stages and solved to compute the hemodisturbances using computational fluid dynamics (CFD) by finite element method (FEM) to investigate viscosity changes effect. Ultrasound color flow image of velocities of blood have been constructed using phase shift information estimated with autocorrelation of Hilbert transformed simulated backscattered radiofrequency (RF) signals from moving blood particles. The simulated ultrasound images have been compared with CFD simulation images and identified a good match between them. The atherosclerosis stages of the models have been investigated from the estimated velocity data. It has been observed that the blood velocities increase noticeably in carotid atherosclerotic growths and velocity distribution changes with viscosity variations. It is also found importantly that the viscosity induced contrast associated to atherosclerosis is detectable in ultrasound color flow imaging. The findings of this work might be useful for better investigation of carotid atherosclerosis as well as prediction of its progression to reduce the stroke risk.
Similar to MODELLING STENOSIS DEVELOPMENT IN THE CAROTID ARTERY AT THE EARLY STAGES OF STENOSIS DEVELOPMENT (3) (20)
Study on viscosity induced contrast in ultrasound color flow imaging of carot...
MODELLING STENOSIS DEVELOPMENT IN THE CAROTID ARTERY AT THE EARLY STAGES OF STENOSIS DEVELOPMENT (3)
1. MODELLING STENOSIS DEVELOPMENT IN
THE CAROTID ARTERY AT THE EARLY
STAGES OF STENOSIS DEVELOPMENT
A.C.Stamou1, J.M.Buick2
1 Faculty of Engineering and Computing, Coventry University
2 School of Engineering, Anglesea Building, Portsmouth
2. Objectives of the talk
Presentation outline
Description of the problem
Methodology
Lattice Boltzmann method
Stenosis growth model
Results
Conclusion
3. Presentation outline
In the present work, the position of the development of a
stenosis in the carotid artery has been simulated based on
regions of stagnation in blood flow.
The interest is focused on:
the blood flow properties, computed here using the Lattice
Boltzmann Method,
prediction of the initial growth of the stenosis, based on
regions of blood stagnation at the artery wall structure,
variation of the haemodynamic properties with the growth of
the stenosis.
4. 4
Carotid artery (ICA, ECA, CCA: External
Carotid Artery, Internal Carotid Artery,
Common Carotid Artery)
ICA
CCA
ECA
Regions prone
to stenosis
development
ATHEROSCLEROSIS AND SUSCEPTIBILITY
TO ATHEROSCLEROSIS
Atherosclerosis, one of the major causes
of strokes. It is a disease which
is likely caused by the lipoprotein
accumulation accompanied with
endothelial cell damage (1,2) on the wall
surface,
manifests on areas of high curvature and
bifurcations.(1,2)
These atherosclerotic-prone-sites are
often characterized by:
low endothelial stress (3, 4)(endothelial
stress: the applied shear stress on the
walls because of the fluid movement),
disturbed flow (2) (flow characterized by
high oscillations of the shear stress from
the predominant flow direction (5)),
stagnant flow. (6)
5. LATTICE BOLTZMANN METHOD
LBM equation-Kinematic behaviour
𝑓 𝑥, 𝑡 is the particle distribution function
along the 𝑖 𝑡ℎ
direction
Evolution equation
𝑓𝑖 𝑥 + 𝑒𝑖, 𝑡 + 1 = 𝑓𝑖 𝑥, 𝑡 + Ω𝑖 𝑥, 𝑡
where 𝑒𝑖 is the vector along link 𝑖,
the collision operator is
Ω𝑖 𝑥, 𝑡 = −
1
𝜏
𝑓𝑖 𝑥, 𝑡 − 𝑓𝑖
𝑒𝑞
𝑥, 𝑡
and the equilibrium distribution function is
𝑓𝑖
𝑒𝑞
= 𝑤𝑖 𝜌 1 + 3𝑒𝑖 ⋅ 𝑢 +
9
2
𝑒𝑖 ⋅ 𝑢 2 −
3
2
𝑢2
where 𝑤𝑖 0 < 𝑤𝑖 < 1 is weight function and
the density and the velocity are given by:
𝜌 = 𝑓𝑖
8
𝑖=0 and 𝜌𝑢 = 𝑓𝑖 𝑒𝑖
8
𝑖=0
The D2Q9 lattice
6. STENOSIS GROWTH MODELLING
(CRITERIA)
The velocity magnitude along the wall is considered of
significant effect on the simulation of the growth of the
stenosis.
However, the maximum stagnation of the flow is
considered in our work as the criterion for the growth of
the stenosis, with stagnation index:
SI = N/T
where T is the period of the cardiac pulse and N is the
number of time-steps in a period when 𝑢1, the local
velocity magnitude at the 1 grid length from the wall, is
less than 1% of the average 𝑢1 over the whole of the wall
during the previous period.
7. 7
Arterial grid
CALCULATION OF THE
VELOCITY MAGNITUDE
The simulation of the growth of the
stenosis is accomplished assuming
an extrapolation scheme that
supports the movement-boundary
mechanism.
The velocity magnitude locally at the
1 grid space from the wall is worked
out, by:
𝑢1= 1 − 𝛿 *𝑢 𝑑 𝑝1
+ 𝛿 ∗ 𝑢 𝑑
δ: distance of the first fluid node 𝑥 𝑓
from the wall. 𝑢 𝑑𝑝1, 𝑢 𝑑, 𝑢1:velocities
at 𝑥𝑓𝑓, 𝑥 𝑓 and one grid length (1 lu)
from the wall.
8. 8
APPLYING THE MOVING
BOUNDARY MECHANISM
Picking out the point satisfying the mechanical
criterion (stagnation)
Applying the illustrated boundary-movement
scheme at the first fluid node from the wall
Comparing the 𝛿 and 𝑙 (the distance the
boundary moves, here set to 0.5)
𝛿 ≦ 𝑙 ∶ the selected fluid node 𝑥𝑓 turns to
wall (case a)
𝛿 > 𝑙: the selected fluid node 𝑥𝑓 remains a
fluid node (case b)
Working out the new 𝛿′
𝛿′
= 𝑙 − 𝛿 (case a)
𝛿′
= 𝛿 − 𝑙 (case b)
Set up the new boundary as shown
Movement-boundary mechanism
9. RESULTS ANALYSIS
The presentation of the results is structured as follows:
Stenosis development in layers
Effect of stenosis growth on the blood flow along
the wall
Flow profiles
10. 10
STENOSIS DEVELOPMENT
The stenosis is formed in layers
built up on the outer walls of the
ECA and ICA.
The stenosis layers are built up
consecutively on either the same
arterial wall or on the opposite
wall.
The growth occurs on the ECA
below the bifurcation.
In the ICA the stenosis occurs
from slightly below the bifurcation
and extends significantly in to the
ICA.
Stenosis growth in layers with Ts, the number of
grid sites, originally in the blood flow region,
which have been enclosed by the growth of the
stenosis.
11. 11
CHANGE IN THE WALL VELOCITY
WITH STENOSIS GROWTH
B)A)
The growth of the stenosis influences mainly
the flow at the stenosed regions.
A) Velocity magnitude along the ECA
B) Velocity variation with the growth of
the stenosis as a function of TS
15. Conclusions
The position of the stenosis has been simulated
here based on regions of flow stagnation.
The stenosis is formed on the outer wall of both
the ICA and the ECA in the region where vortex
motion develops in the healthy artery.
The growth of the stenosis influences mainly the
flow close to the stenosed wall.
An increased velocity was observed in both the
ICA and the ECA with the growth of the stenosis.
16. Future research
Simulation of the progression of the stenosis in a number
of other arteries which are similarly susceptible to this
disease, in particular the human aorta
Comparison of haemodynamics between stenosed and
stented arteries
Simulation of the non-Newtonian blood considering
alternative models to the Carreau-Yasuda
Development of a 3D model to enable the secondary flows
in the artery to be assessed and their effect on stenosis
development
17. References
1. C.G. Caro. Atherioscler Thromb Vasc Biol. 29: 18-161, 2009.
2. X. He, D.N. Ku. Journal of Biomechanical Engineering. 118: 74-82,
1996.
3. Y.S. Chatzizisis, M. Yoman, A.U. Coskun, R. Beigel, B.V. Stone, C.
Meynard et al. Circulation. 117: 993-1002, 2008.
4. J. Knight, U. Olgac, S.C. Saur, D. Poulikakos, W. Marshall, P.C. Cattin
et al. Atherosclerosis. 211: 445-450, 2010.
5. D.N. Ku, D.P. Giddens, C.K. Zarins and S.Glagov. Atherioscler Thromb
Vasc Biol. 5: 293-302, 1985.
6. C.V. Soulis, O. P. Lampri, D.K. Fytanidis and G.D. Giannoglou.
Biomedical Engineering, 2011 10th International Workshop on 5-7
Oct. 2011 1-4.