3d modeling of cervical musculature

8/3/2019 3D Modeling of Cervical Musculature

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1Sofia HedenstiernaDivision of Neuronic Engineering, School of Technology and Health

3D Modeling of Cervical Musculature

and its Effect on Neck Injury Prevention

DIVISION OF

NEURONIC ENGINEERING

Defence of Doctoral Thesis

Sofia Hedenstierna


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With combined knowledge

of medicine and engineeringimprove the prevention of

head and neck injuries

?

Division of Neuronic Engineering

Neurotrauma + Mechanics


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Neck Injury Prevention

Experimental Research and Development

Davidsson et al. (1998)


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Neck Injury Prevention

Existing numerical models of the cervical musculature

Eindhoven (MADYMO)

(Van der Horst 2002)

France (RADIOSS)

(Frechede et al. 2006)

KTH (LS-DYNA)

(Brolin et al. 2005)

Duke (LS-DYNA)

(Chancey et al. 2003)

JAMA (LS-DYNA)

(Ejima et al. 2005)


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5

The KTH FE Neck Model

Intervertebral Disksand Ligaments

VertebraeMuscles

Sofia HedenstiernaDivision of Neuronic Engineering, School of Technology and Health

Numerical Modeling


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Solid model:

Improved Boundary Condition for InjuryPrediction in Cervical Column

3D geometry

Inertia forces

Compressive stiffness

Output from Muscle Tissue for Muscle

Injury Analysis Strain

Cross sectional forces

Strain energy

Passive force

Active force

Discrete model:

Numerical Modeling


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better understand the contribution from musculature on the stabilityof the head neck complex,

improve the injury prediction of the cervical spine e.g.vertebra andligament,

enable analysis of strain in the muscle elements to predict injury in themuscle tissue.


Objectives

Main objective:To develop a 3D finite element model of the cervicalmusculature using solid elements, in order to:


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Introduction

Method

Geometry

Material ModelingEvaluation

Results From Papers

Conclusions

Future Work

3D Modeling of Cervical Musculature and

its Effect on Neck Injury Prevention



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Geometry of the Cervical Musculature

The FE Muscle Model Geometry created from MRI

1. Segmented from MRI

(50th percentile)

2. Interpolated into 3D

surfaces


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1. Segmented from MRI

(50th percentile)

2. Interpolated into 3D

surfaces

3. Positioned relative the

KTH neck model in line

with the literature




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25 individual muscle pairs

Rigid body insertions to thevertebrae

One muscle can have multiple

origins/insertions





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Anterior: Hyoid, SCM Lateral: SCM, TZ

Posterior: TZ, SplCap Posterior: Suboccipital


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Introduction

Method

Geometry


Results From Papers

Conclusions

Future Work





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TheActive forceis generated voluntarily orby reflex. It has a maximum at optimalmuscle length Lopt and decreases rapidlyas the muscle is shortened or extended.

Force

Length

Passive

Active

Total

Isometriccontraction

Lopt


The Passive forcedepends on the stiffness

on the muscle tissue and increasenonlinearly with the length.

Mechanical properties of muscle tissue

The Total forceis the sum of passive andactive forces.

Materialresponse: passive stiffness and active contraction


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v=1/s10/s25/s

[Myers et al 1995]

[Davis et al 2003]

Materialformulations: Passive


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Nonlinear elastic

3

1 1

2)1(

2

11

i

n

j

i

j

jJKW j

Ogden Rubber Energy Potential

Parameters obtained from and validated for study on the rabbitTibialis Anterior muscle [Davis et al 2003]

[Ogden 1972]



Unidirectional stress

i

i

ii

12

1

1

e


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Nonlinear elastic

Viscoelastic

3

1 1

2)1(

2

11

i

n

j

i

j

jJKW j

Ogden Rubber Energy Potential

i

i

ii

12

1

1

[Ogden 1972]



Unidirectional stress

n

i

t

i

ieGtG

1

)(

Viscoelasticity

t

klijkl

V

ij tG0

)(

eV

Prony Series


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v=1/s10/s25/s

Ogden


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The Hill-type element


Materialformulations: Active


CECE Active force

Damper

Passive force


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0.0

1.0

0 1 2Lrel

normF

fTL(Lr)Act(t)

FmaxPCSAPeak muscle stress of 50

N/cm2

[Winters and Stark 1988]

The Hill-type element


Materialformulations: Active


CE

FCE= FmaxPCSAAct(t)fTL(Lr)

CE Active force


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CE

The Hill-typeelement

Discrete Muscle Model Continuum Muscle Model

Hill-typecontractileelement

+

CEActive force

Damper

Passive force

Active force

Damper

Passive force

CE

Nonlinear elastic

Viscoelastic

Continuum elements


Super-positioned Muscle Finite Element (SMFE)



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Passive Muscle

Active Muscle

50N

50N



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Introduction

Method

Geometry


Results From Papers

Conclusions

Future Work





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Evaluation of Muscle Models

Discrete Muscle Model

DMM Continuum Muscle ModelCMM

SMFE Muscle ModelSMFEMM


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Rear end ~4G[Ono et al 1999 and Davidsson et al 1999]




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Frontal~15G[Ewing et al 1977]

Lateral ~7G[Ewing et al 1977]




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Introduction

Method

Geometry


Results From Papers

Conclusions

Future Work





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Paper Aim Method Result

I Analyze importance ofmuscle activation

FE spring neck musclemodel (DMM)

II Measure muscle activationschemes on volunteers

Experimental EMG

III Define material descriptionof passive and active

muscle tissue

FE solid rabbit musclemodel (SMFE)

IV Create a 3D musclegeometry with continuumelements

FE solid neck musclemodel (CMM)

V Evaluate the muscle loadresponse in the solid neckmuscle model

FE solid neck musclemodel(CMM passive)

VI Create an active neckmuscle model withcontinuum elements

FE solid neck musclemodel (SMFEMM)

Papers

Measure muscle activ.schemes on volunteers

Analyze importance ofmuscle activation


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Paper I: The importance of muscle tension on theoutcome of impacts with a major vertical component.

Aim: To analyze how activated cervical musculature protectsthe neck during injurious impacts.


Brolin K., Hedenstierna S., Halldin P., Bass C.R., Alem N. InternationalJournal of Crashworthiness, 13(5): 487-498, 2008.


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Paper I: The importance of muscle tension on theoutcome of impacts with a major vertical component.

Aim: To analyze how activated cervical musculature protectsthe neck during injurious impacts.


Brolin K., Hedenstierna S., Halldin P., Bass C.R., Alem N. InternationalJournal of Crashworthiness, 13(5): 487-498, 2008.

Conclusion: Muscle activation stabilizes the spinal columnduring impacts with a major vertical component,

and reduces the risk of ligament injury at high impactseverities.


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Paper II: Electromyography of Superficial and DeepNeck Muscles During Isometric, Voluntary, and

Reflex Contractions.

Aim:To improve knowledge about muscle activation schemesduring voluntary and subjected motions, covering deepand superficial cervical muscles for multiple directions ofmotion.


Siegmund G.P, Blouin J-S, Brault J, Hedenstierna S, Inglis J Journal of Biomechanical Engineering, 129(1), 66-77, 2007.

Muscles with EMG electrodes Dynamic sled tests/Static force generation


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Activationtime

Duration

Paper II: EMG in multiple directions


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Paper II: Electromyography of Superficial and DeepNeck Muscles During Isometric, Voluntary, and

Reflex Contractions.

Aim:To improve knowledge about muscle activation schemesduring voluntary and subjected motions, covering deepand superficial cervical muscles for multiple directions ofmotion.


Siegmund G.P, Blouin J-S, Brault J, Hedenstierna S, Inglis J Journal of Biomechanical Engineering, 129(1), 66-77, 2007.

Conclusion: Muscle activation is directional dependent. Allmuscles except Splenius Capitis, acted consistentlywith their anatomical location.


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II Measure muscle activationschemes on volunteers

Experimental EMG

III Define materialdescription of passive

and active muscle tissue








Papers


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Paper III:Evaluation of a combination of continuumand truss finite elements in a model of passive and

active muscle tissue.

Aim: To suggest and evaluate a method to model activemuscle tissue with continuum material properties andactive force generation.


Hedenstierna S, Halldin P, Brolin K. Computer Methods in Biomechanics and Biomedical Engineering, 11(6), 627-39, 2008.

Super-positioned Muscle Finite Element


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Eccentric contraction

Concentric contraction

Paper III: SMFE


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Paper III:Evaluation of a combination of continuumand truss finite elements in a model of passive and

active muscle tissue.

Aim: To suggest and evaluate a method to model activemuscle tissue with continuum material properties andactive force generation.


Hedenstierna S, Halldin P, Brolin K. Computer Methods in Biomechanics and Biomedical Engineering, 11(6), 627-39, 2008.

Conclusion: It is possible to model active muscle tissuewith continuum material properties by combiningpassive solid elements and active discrete elements.


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II Collect information onmuscle activation

Experimental EMG


muscle tissue


IV Create a 3D musclegeometry withcontinuum elements






Papers


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Paper IV: How does a Three-Dimensional Continuum MuscleModel Affect the Kinematics and Muscle Strains of a FiniteElement Neck Model Compared to a Discrete Muscle Model in

Rear-End, Frontal, and Lateral Impacts.

Aim: To create and validate a solid model of the neckmuscles including nonlinear and viscoelastic materialproperties.


Hedenstierna S, Halldin P. Spine, 33(8), E236-45, 2008.

CMMDMM


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Kinematics: Rear-end Impact

Paper IV: Evaluation of Solid muscle model



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Kinematics: Lateral Impact




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Kinematics: Frontal Impact




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Paper IV: How does a Three-Dimensional Continuum MuscleModel Affect the Kinematics and Muscle Strains of a FiniteElement Neck Model Compared to a Discrete Muscle Model in

Rear-End, Frontal, and Lateral Impacts.

Aim: To create and validate a solid model of the neckmuscles including nonlinear and viscoelastic materialproperties.


Hedenstierna S, Halldin P. Spine, 33(8), E236-45, 2008.

Conclusion: The continuum element muscle modelstabilizes the vertebral column compared to thespring muscle model, and improves the biofidelityof the neck model.


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Experimental EMG


muscle tissue




V Evaluate the muscleload response in thesolid neck muscle model




Papers


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Paper V: Neck Muscle Load Distribution in Lateral,Frontal and Rear-end Impact; a 3D Finite Element

Analysis.

Aim: To study how the load distribution in the cervicalmuscles varies as a function of impact severity andimpact direction, using the model developed anddescribed in Paper IV.


Hedenstierna S, Halldin P, Siegmund G.P. Submitted for publication, 1-16

Green Effective StrainInternal EnergyCross Sectional Force


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Paper V: Cross Sectional Forces vs. EMG activity

FRONTAL

LATERAL

REAR-END

Kumar

Schldt


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Cross Sectional ForceREAR-END IMPACT

t=0.13

t=0.072

Paper V: Muscle Load during impact



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Green Effective Strain

REAR-END IMPACT

Paper V: Muscle Load during impact



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Paper V: Neck Muscle Load Distribution in Lateral,Frontal and Rear-end Impact; a 3D Finite ElementAnalysis.

Aim: To study how the load distribution in the cervicalmuscles varies as a function of impact severity andimpact direction, using the model developed anddescribed in Paper IV.


Hedenstierna S, Halldin P, Siegmund G.P. Submitted for publication, 1-16

Conclusion: The muscle load predicted by the model issensitive to load direction and severity.

The resulting local strains and global energies/forcespredicts different load distributions.


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Experimental EMG


muscle tissue








Papers


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Paper VI: Development of an active solid neckmuscle FE model and its influence on neck injuryprediction.

Aim: To study the effect of incorporated active muscle forcesin the solid element model of the cervical musculature onneck kinematics, using the materials described in PaperIIIin the solid musculature model described in Papers IV

and V.


Hedenstierna S.Manuscript, 1-15

SMFEMMCMM


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Paper VI: Active Continuum Muscle Model with SMFE


CMM SMFEMM


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CMM SMFEMM


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Global Vertebral Rotations: Rear-end




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Paper VI: Development of an active solid neckmuscle FE model and its influence on neck injuryprediction.

Aim: To study the effect of incorporated active muscle forcesin the solid element model of the cervical musculature onneck kinematics, using the materials described in PaperIIIin the solid musculature model described in Papers IV

and V.


Hedenstierna S.Manuscript, 1-15

Conclusion: The SMFEMM gives a more realisticresponse than the CMM and DMM, and thekinematics are closer to volunteer data.


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Introduction

Method

Geometry


Results From Papers

Conclusions

Future Work





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Conclusions

The solid elements stabilizes and restricts themotion of the vertebral column compared to thespring muscle model

The load distribution between muscles reflects the

different impact directions and severities applied The solid muscle model visualizes muscle

dynamics and strains in an easy perceptual way



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Introduction

Method

Geometry


Results From Papers

Conclusions

Future Work





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Future Work


Boundaryconditions

The stability of theSMFE

Myotendinous-junctions/insertion

Muscle activation

A female version


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THANK

YOU!


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I. The importance of muscle tension on the outcome of impacts with a major verticalcomponent. Brolin K., Hedenstierna S., Halldin P., Bass C.R., Alem N. International Journal of Crashworthiness,13(5): 487-498, 2008.

II. Electromyography of Superficial and Deep Neck Muscles During Isometric, Voluntary,and Reflex Contractions. Siegmund G.P., Blouin J.S., Brault J.R., Hedenstierna S., Inglis J.T. Journal ofBiomechanical Engineering, 129(1), 66-77, 2007.

III. Evaluation of a combination of continuum and truss finite elements in a model ofpassive and active muscle tissue. Hedenstierna S., Halldin P., Brolin K. Computer Methods in Biomechanics

and Biomedical Engineering, 11(6), 627-39, 2008.

IV. How does a Three-Dimensional Continuum Muscle Model Affect the Kinematics andMuscle Strains of a Finite Element Neck Model Compared to a Discrete Muscle Model inRear-End, Frontal, and Lateral Impacts. Hedenstierna S., Halldin P. Spine, 33(8), E236-45, 2008.

V. Neck Muscle Load Distribution in Lateral, Frontal and Rear-end Impact; a 3D FiniteElement Analysis. Hedenstierna S., Halldin P., Siegmund G.P. Submitted for publication, 1-16

VI. Development of an active solid neck muscle FE model and its influence on neck injuryprediction. Hedenstierna S.Manuscript, 1-15

Papers


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Flexion 15g: Passive CMM and active SMFE

Passive

Active


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Extension 4g: Passive CMM and active SMFE

Passive

Active

Passive DMM


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Lateral 7g: Passive CMM and active CMM

Passive

Active

Passive DMM


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v(t)

Frontal impact

Muscle Activation

Degree of activation over time


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Activationtime

Duration

Paper II: EMG in multiple directions


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Peak headrot (deg)

DMM pas 80

CMM pas 67

CMM act 49

SMFEMM 46

Peak Head rotation relative T1

3d modeling of cervical musculature

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