This is the developer site of the OpenKnee project. The development efforts are organized by [http://www.lerner.ccf.org/bme/erdemir/ Ahmet Erdemir] and [http://www.lerner.ccf.org/bme/cobi/ CoBi Core] of the Cleveland Clinic. This study branched from a current NIH funded study on multiscale modeling and simulation of the knee joint, [https://simtk.org/home/j2c J2C]. If you are a new member ([:InstructionsForProjectSite#Team:How do I become a member?]), please read the following documentation to familiarize yourself with operational details:

For recent wiki activity, check RecentChanges.

At this moment:

-- ["aerdemir"] DateTime(2010-03-05T13:44:38Z) Scott has finished developing a full hexahedral mesh, model development is underway.

TableOfContents

Goals

Roadmap

Releases relies on the following numbering scheme:

version.major.minor.revision

version
numbering based on goals of the roadmap
major
implementation of a new feaure
minor
improvement of a feature or a bug fix
revision
revision number of the subversion repository on which the release is based on

Version 1.0

Long Term

Release Notes

Team Roles

Specifications

Geometry

Source: https://simtk.org/websvn/wsvn/openknee/dat/geo/

Currently, the knee geometry relies on manual digitization generated from sagittal MR images. Volsuite was used for this purpose. This initial geometry set was generated by Craig Bennetts of CoBi Core at Cleveland Clinic. 3D spline curves were used to develop NURBS surfaces using the loft feature in the CAD package Rhinoceros. Due to poor visibility of the lateral collateral ligament in sagittal image sets, its geometry is an approximation. Geometries are provided in a coordinate system aligned with the first sagittal MR image:

Mesh

Source: https://simtk.org/websvn/wsvn/openknee/dat/msh/

Current discretization relies on a fully hexahedral mesh generated using TrueGrid software (XYZ Scientific). The mesh file is a text based file conforming mesh definition convention of Abaqus.

Element Sets:

Surface Sets:

Node Sets

Interface nodes between bone and cartilage were merged to eliminate the need for tie constraint enforcement in the FE model.

Material Properties

Bone

Rigid

Cartilage

Incompressible, isotropic Neo-Hookean: C1=2.54 MPa, K=100 MPa [#Donahue02 Donahue (2002)] Converted Young's modulus and poisson ratio from linear elastic model to shear and bulk modulus to allow for finite strains using relationships: latex(\begin{displaymath}\mu=\frac{E}{2(1+\nu)}\end{displaymath}) and latex(\begin{displaymath}K=\frac{2\mu(1+\nu)}{3(1-2\nu)}\end{displaymath}) with latex(\begin{displaymath}C1=\frac{\mu}{2}\end{displaymath})

Ligament

Incompressible, transversely isotropic Neo-Hookean: C1=1.44 MPa, C3=0.57 MPa, C4=48, C5=467.1 MPa, lambda=1.062, K=144 MPa [#Gardiner03 Gardiner (2003)]

Meniscus

Incompressible, isotropic Neo-Hookean: C1=2.0 MPa, K=207 MPa - made to be approximately half as stiff as cartilage. -- ["aerdemir"] DateTime(2010-02-25T03:26:31Z) Let's rely on literature values.

Interactions

Ligaments are attached to bone via rigid interface definitions (interface nodes become part of rigid body).

Frictionless, sliding contact defined between tibial to femoral cartilage, cartilage to meniscus, ligament to bone, and ACL to PCL.

Loading & Boundary Conditions

The loading should allow prescription of tibiofemoral joint flexion and application of loads to the remainder of 5 degrees of freedom of the joint.

Output

* Stress distribution * Strain distribution * Tibiofemoral joint kinematics (pose and orientation) * Tibiofemoral joint kinetics (forces and moments) * Contact stress * Ligament forces

Solver

Non-linear system is solved using a standard BFGS quasi-Newton algorithm or full Newton method implemented by Steve Maas in FEBio. The linear system at each iteration is solved using Pardiso, a sparse matrix solver for shared memory architecture. http://www.pardiso-project.org/

Software

For finite element analysis [http://mrl.sci.utah.edu/software/febio FEBio], a freely accessible package, will be used. This software is a product of significant efforts by Jeff Weiss and his group from the [http://mrl.sci.utah.edu/ Musculoskeletal Research Laboratories] at the University of Utah. Current version used in this project is FEBio 1.2, which can be downloaded from their [http://mrl.sci.utah.edu/software/febio site].

Settings

Data

Data for model development efforts are courtesy of [http://www.lerner.ccf.org/bme/bogert/ van den Bogert Laboratory] at the Cleveland Clinic. The information was collected is part of doctoral work conducted by Bhushan Borotikar.

Specimen

NDRI ID

08956 (Specimen acquired from National Disease Research Exchange)

MRMTC#

022508-03 (Specimen tested in Musculoskeletal Robotics and Mechanical Testing Facility at the Cleveland Clinic)

Side

Right

Donor Age

70 years

Donor Estimated Body Weight

170 lbs (77.1 kg)

Donor Heigt

5'6" (1.68 m)

Donor Gender

Female

Donor Cause of Death

Pneumonia/Cancer

Imaging

Source: https://simtk.org/websvn/wsvn/openknee/dat/mri/

The knee specimen was imaged at the Biomechanics laboratory of the Cleveland Clinic using a 1.0T (Tesla) extremity MRI scanner (Orthone, ONI Medical Systems Inc, Wilmington MA). The scanner has the capability to scan upper and lower extremities of up to 180mm diameter. A scanning protocol that gave a good contrast for articular cartilage and ligaments in the same scan were used [#Borotikar09 Borotikar (2009)]. The specifics of this protocol are detailed in following:

Setting for Magneric Resonance Imaging

Scan Parameters

Sagittal

Axial

Coronal

Pulse sequence

GE3D

GE3D

GE3D

TR

30

30

30

TE

8.9

8.9

8.9

Frequency

260

260

260

Phase

192

192

192

FOV

150

150

150

BW

20

20

20

Echo train

1

1

1

NEX

1

1

1

Flip angle

35

35

35

Time

5.03

3.19

3.30

Scan Options

Sagittal

Axial

Coronal

Graphics SL

Y

Y

Y

RF spoiling

Y

Y

Y

Fat suppression

N

N

N

Minimum TE

Y

Y

Y

Inversion recovery

N

N

N

Partial data

N

N

N

No phase wrap

Y

Y

Y

Spatial saturation

N

N

N

Flow comp

N

N

N

Magnetic transfer

N

N

N

Prescan Parameters

Sagittal

Axial

Coronal

Prescan

Auto

Auto

Auto

Center freq.

Peak

Peak

Peak

Slice Parameters

Sagittal

Axial

Coronal

Number of slices

70

45

60

Slice thickness (mm)

1.5

1.5

1.5

Gap (mm)

0

0

0

Range (mm)

105

67.5

90

The knee was kept in full extension position. Imaging technique utilizes 3D spoiled gradient echo sequence with fat suppression, TR = 30, TE = 6.7, Flip Angle = 200, Field of View (FOV) = 150mm X 150mm, Slice Thickness = 1.5mm. Scans in three anatomical planes, axial, sagittal, and coronal, were conducted. Total scanning time was approximately 18 minutes. Selecting these specific sequence parameters produced images that highlighted articular cartilage such that it could be easily discriminated from surrounding bone and tissue. The protocols and the image set reflect partial data from the doctoral work of [#Borotikar09 Borotikar (2009)].

Mechanical Testing

Documentation

Developer's Guide

User's Guide

Simulations

Test Suite

Physiological

References

Anchor(Borotikar09) Borotikar, Bhushan, Subject specific computational models of the knee to predict anterior cruciate ligament injury, Doctoral Dissertation, Cleveland State University, December 2009.

Anchor(Gardiner03) Gardiner JC, Weiss JA. Subject-specific finite element analysis of the human medial collateral ligament during valgus knee loading. J. Orthop. Res. 2003 Nov;21(6):1098-1106.

Anchor(Donahue02) Donahue TLH, Hull ML, Rashid MM, Jacobs CR. A finite element model of the human knee joint for the study of tibio-femoral contact. J Biomech Eng. 2002 Jun;124(3):273-280.

Pubmed

Results of a search with keywords ("finite element" AND knee) can be accessed:

http://www.ncbi.nlm.nih.gov/pubmed?term=%22finite%20element%22+knee