1 / 23

February 22 nd , 2007 LPPD lab meeting

Brain Vasculature and Intracranial Dynamics. February 22 nd , 2007 LPPD lab meeting. Michalis A. Xenos and Andreas A. Linninger Laboratory for Product and Process Design , Departments of Chemical and Bio-Engineering, University of Illinois, Chicago, IL, 60607, U.S.A.

kenneth-douglas
Télécharger la présentation

February 22 nd , 2007 LPPD lab meeting

An Image/Link below is provided (as is) to download presentation Download Policy: Content on the Website is provided to you AS IS for your information and personal use and may not be sold / licensed / shared on other websites without getting consent from its author. Content is provided to you AS IS for your information and personal use only. Download presentation by click this link. While downloading, if for some reason you are not able to download a presentation, the publisher may have deleted the file from their server. During download, if you can't get a presentation, the file might be deleted by the publisher.

E N D

Presentation Transcript

  1. Brain Vasculature and Intracranial Dynamics February 22nd, 2007 LPPD lab meeting Michalis A. Xenos and Andreas A. Linninger Laboratory for Product and Process Design, Departments of Chemical and Bio-Engineering, University of Illinois, Chicago, IL, 60607, U.S.A.

  2. Motivation for studying Intracranial Dynamics • Many biological phenomena in the brain need better interpretation • Large deformation of biological tissues under hydrocephalic conditions. • Interaction of vasculature with soft brain tissue. • Fundamental transport processes in soft tissues are poorly understood. • Interpretation of experiments is inadequate. Hydrocephalic Brain MRI Normal Brain MRI

  3. Continuity Momentum Distensibility of vasculature are equal for i = 1, …,n Equations of motion for a vessel, Bifurcations and Unions Straight tube parent children l : tube length F: Poiseuille coef. E : Young modulus A0 : Initial cross sectional area p* : External pressure Unknowns: fin , p , A Bifurcation child parents Union

  4. T’2 T2 T4 T4 T1 T1 T3 Bifurcated tubes vs. lumped tubes

  5. Bifurcated tubes vs. lumped tubes … cont.

  6. Blood signals and fitting procedure Pulsatile blood pressure from MRI

  7. Arterial spectrum Ventricular spectrum Phase lag Spectral analysis for blood and ventricular signals from MRI data Applying FFT the spectrum for both pulses :

  8. Properties of the Brain

  9. Model Generator and obtained networks Model Generator Blood network same to Zagzoule’s

  10. A simple blood flow model – Zagzoule network Hademenos, Massoud, The physics of Cerebrovascular Diseases, 1998

  11. Complex compartmental results – physiological pulse

  12. QA QFfr Subarachnoid space (SAS) (r) QFfb Arteries (a) QFcf Ventricles (f) Qac QFpf Qap Choroid Plexus (p) Capillaries (c) Qpc Qpv QFcb Qcv QFfv Venous Sinus (n) Qvn QFbr Veins (v) QFbv Brain (b) QFri QFrn QA QFir Spinal Cord (s) A holistic brain compartmental model Blood flow CSF flow

  13. Normal case pressures

  14. Normal case flows

  15. Time snapshots for pressure and volume

  16. Continuity Momentum Continuity Distensibility of vasculature Momentum Total stress p* d solid p p fluid Open vs. Closed network systems Open system Closed system

  17. Egnor’s mathematical model Newton’s Law or we differentiate both sides of the above equation Forcing function the particular solution of the above equation is Damping force Elastic resistance Pulsatile resistance Elastic force Resonance : In an oscillating system with one degree of freedom, resonance is the state of minimal impedance. Acceleration

  18. RLC vs. 2nd order oscillators • Series RLC Circuit notations: • V - the voltage of the power source (V) • I - the current in the circuit (A) • R - the resistance of the resistor (Ohms = V/A); • L - the inductance of the inductor (H = V·s/A) • C - the capacitance of the capacitor (F = C/V = A·s/V) • Given the parameters v, R, L, and C, the solution for the current i using Kirchhoff's voltage law is: • For a time-changing voltage V(t), this becomes • Rearranging the equation (dividing by L and differentiating with respect to t gives the following second order differential equation: Damping factor • We now define two key parameters: Resonance frequency

  19. Continuity Momentum Distensibility of vasculature Straight tube R C Electrical analogy (RC) Our model vs. RLC I

  20. Assumptions of Egnor’s model 1. Intracranial CSF pulsations are normally synchronous with arterial pulsations. 2. Normal intracranial CSF pulsations are of similar amplitude and morphology in the ventricles and the subarachnoid space. 3. Arterial pulsations are normally filtered from the cerebelar circulation, so the capillary blood flow is nearly smooth (the windkessel mechanism). Oscillations of CSF with a single degree of freedom are described by the same differential equation that describes the oscillations of electrons in an alternating current electrical circuit Windkessel Effect The mechanism by which arterial pulsations are progressively dissipate to render the capillary circulation almost pulseless is called the windkessel effect. Egnor et al, Pediatric Neurosurgery, 2001; 2002

  21. The role of resonance in Egnor’s model and the reality • With the help of resonance Egnor assumes that the Intracranial CSF pulsations are synchronous with arterial pulsations. This is not true: Phase lag: aqueduct: – 52.5 ± 16.5o prepontine cistern: – 22.1 ± 8.2o C-2: +5.1 ± 10.5o (consistent with flow synchronous with the arterial pulse) Wagshul et al, J. Neurosurg, 2006 Zhu et al, J. MRI, 2006

  22. Conclusions • Current systems describe the brain until a point • Electrical analogies of the models • Egnor’s model and his assumptions were presented • The flow between blood and CSF has a phase lag and the assumption of synchronous pulsations is not valid • Advancement of these models with the inclusion of porosity! • Future steps – distributed systems

  23. THANK YOU

More Related