madymo human body models manual release 7.7 june...

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MADYMO

Human Body Models Manual

Release 7.7

June 2017

© Copyright 2017 by TASS International BV All rights reserved.

MADYMO® has been developed at TASS International BV.

This document contains proprietary and confidential information of TASS International BV.

The contents of this document may not be disclosed to third parties, copied, or duplicated in

any form, in whole or in part, without the prior permission of TASS International BV.

The terms and conditions governing the licensing of MADYMO® software consists solely of

those set forth in written contracts between TASS International BV or TASS International BV-authorised third parties and its customers. The software may only be used or copied in

accordance with the terms of these contracts.

MADYMO Human Models Manual Release 7.7

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Table of contents

Table of contents ....................................................................................................... 3

1 Introduction ....................................................................................................... 5 1.1 General human body model description .................................................... 6

1.1.1 Model types ................................................................................. 6 1.1.2 Facet occupant models ................................................................. 7 1.1.3 Facet active human model............................................................ 8 1.1.4 Facet pedestrian model ................................................................ 8 1.1.5 Ellipsoid pedestrian models ......................................................... 8 1.1.6 Available human models.............................................................. 8

1.2 Model validation ...................................................................................... 9 1.3 User instructions .................................................................................... 10

1.3.1 Human model files .................................................................... 10 1.3.2 Integration method and time step ............................................... 11 1.3.3 Human model positioning .......................................................... 11 1.3.4 Contacts .................................................................................... 12 1.3.5 Output ....................................................................................... 12

1.4 Examples ............................................................................................... 13 1.5 Required model licenses ......................................................................... 13

2 Facet occupant models ..................................................................................... 15 2.1 Model description................................................................................... 16

2.1.1 Anthropometry .......................................................................... 17 2.1.2 Configuration ............................................................................ 19 2.1.3 Spine and neck .......................................................................... 20 2.1.4 Thorax and abdomen ................................................................. 21 2.1.5 Pelvis ........................................................................................ 23 2.1.6 Shoulders .................................................................................. 23 2.1.7 Limbs ........................................................................................ 24 2.1.8 Skin ........................................................................................... 25

2.2 Model validation .................................................................................... 25 2.2.1 Blunt impact tests ...................................................................... 25 2.2.2 Sled tests ................................................................................... 27 2.2.3 Vertical vibration ....................................................................... 28 2.2.4 Child model validation .............................................................. 29

2.3 User instructions .................................................................................... 30 2.3.1 Integration method and time step ............................................... 30 2.3.2 Positioning ................................................................................ 30 2.3.3 Contacts .................................................................................... 38


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2.3.4 FE belt positioning and contact definition .................................. 39 2.3.5 Output ....................................................................................... 39

2.4 Examples ............................................................................................... 44 2.4.1 Frontal impact with a belt .......................................................... 44 2.4.2 Occupant model positioning method b ....................................... 44

3 Facet active human model ................................................................................ 45

4 Facet pedestrian model ..................................................................................... 46 4.1 Model description .................................................................................. 47 4.2 Model validation .................................................................................... 47 4.3 User instructions .................................................................................... 47

4.3.1 Integration method and time step ............................................... 47 4.3.2 Positioning ................................................................................ 47 4.3.3 Contacts .................................................................................... 51 4.3.4 Output ....................................................................................... 52

5 Ellipsoid pedestrian models .............................................................................. 58 5.1 Model description .................................................................................. 59

5.1.1 Anthropometry .......................................................................... 59 5.1.2 Configuration ............................................................................ 60 5.1.3 Spine and neck .......................................................................... 61 5.1.4 Thorax and abdomen ................................................................. 61 5.1.5 Hip ............................................................................................ 61 5.1.6 Knee ......................................................................................... 62 5.1.7 Upper and lower leg .................................................................. 62 5.1.8 Ankle, foot and shoe .................................................................. 65

5.2 Model validation .................................................................................... 66 5.2.1 Blunt impact tests ...................................................................... 66 5.2.2 Car-pedestrian tests ................................................................... 68

5.3 User instructions .................................................................................... 68 5.3.1 Integration method and time step ............................................... 68 5.3.2 Positioning ................................................................................ 69 5.3.3 Contacts .................................................................................... 72 5.3.4 Output ....................................................................................... 73

5.4 Example ................................................................................................. 77 5.4.1 Car-pedestrian impact ................................................................ 77

6 References ....................................................................................................... 79


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1 Introduction

Various types of MADYMO human body models have been developed for simulation

of the human body responses in various types of automotive applications see Table 1.1 and Figure 1.1.

Table 1.1 Human body models and applications.

Human model Impact simulation Comfort

Simulation

Facet occupant models

in various body sizes

Occupant crash

simulations

Prediction of vibration

transmission from the

seat through the human

body

Facet active human

model in sitting and

standing position

Occupant pre-crash and

crash simulations

Pedestrian impact

simulations

Prediction of vibration

transmission from the

seat through the human

body

Ellipsoid pedestrian

models in various body

sizes

Pedestrian impact

simulations

Pre-crash and crash impacts Seat vibration comfort Car-pedestrian impacts

Figure 1.1 Examples of human model applications.

The MADYMO human body models are applicable for frontal, lateral, rearward, and

vertical impact as well as intermediate impact directions and more complicated


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scenarios like rollover. Consequently, they are more biofidelic than dummy models, which are developed for a particular loading direction. Dummy models are mostly

used for simulations of standard (regulated) impact tests. The MADYMO human

models were developed for the evaluation and optimisation of passive and active restraint systems in a wider range of loading conditions than the standard impact tests.

The benefits of using human body models are:

Improved biofidelity compared to dummy models

Multi-directional

Scaleable to other body sizes

Biomechanical data can be easily incorporated

Modelling of post-failure (e.g. fracture) response

Inclusion of muscle activity

Inclusion of controlled posture maintenance

1.1 General human body model description

In this section, general features of the different types of MADYMO human body models are described. Also, information is given on what models are currently

available together with general guidelines on how to use these models. Specific

features and guidelines for using the facet occupant models, the facet active occupant model, and the ellipsoid pedestrian models are described in Chapters 2, 3, and 5,

respectively.

1.1.1 Model types

The types of MADYMO human models that have been released with MADYMO v7.7 are:

1. Facet occupant models

2. Facet active human model

3. Facet pedestrian model

4. Ellipsoid pedestrian models


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The skeleton of these human models mainly consists of chains of rigid bodies connected by kinematic joints. The inertia properties of the rigid bodies and the

ranges of motion of the kinematic joints have been based on biomechanical data

published in literature. Joint, cardan, point and six-dof restraint models are used to model the static and dynamic joint characteristics. The joint characteristics and

mechanical properties of the various segments of the human models are based on

biomechanical data from literature and have been tuned and validated using volunteer

and post mortem human subject (PMHS) responses in various impact tests. The geometry, inertial and mechanical properties of the human model segments depend on

the type of model and its size.

The different human models use different outer geometry definitions. The occupant models and the sitting active human model have been designed for accurate contact

interaction of the skin with the vehicle interior. Therefore, the outer geometry of the

occupant models is represented by facets. For pedestrian applications two different model types are available. The ellipsoid models are fast, robust and easy to scale to

other body dimensions. These models can be used for more conceptual analysis,

preferably with an MB vehicle. For interaction with an FE vehicle, it is recommended

to use the facet pedestrian model as it has a facet geometry which allows for more robust contact interaction with an FE environment.

1.1.2 Facet occupant models

The facet occupant models are developed and validated for impact simulation and for simulation of vibration transmission as related to seating comfort. The outer surface

of the facet occupant models is described with meshes of shell-type massless contact

elements (further referred to as facet surfaces). These facet surfaces are fully

connected to rigid and/or flexible bodies. They allow a more accurate geometric representation compared to ellipsoids. Although the facet surfaces are defined by FE

elements, the facet occupant models are still multi-body models, since no FE solver is

used in simulations. Inertial properties of the occupant segments are represented fully by the inertial properties of the rigid and flexible bodies in the facet occupant model.

Deformation of soft tissues (flesh and skin) is represented by stress-based contact

characteristics defined for the facet surfaces. Using these contact characteristics in contact definitions, soft tissue deformation is described accurately through the contact

interactions of the facet occupant model with itself and with its environment.

Structural deformation of the thoracic and abdominal area is modelled using flexible

bodies (MADYMO Theory Manual, Koppens 1988). The specific features and guidelines of the facet occupant models are described in Chapter 2.


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1.1.3 Facet active human model

The facet active human model is developed and validated for pre-crash simulation,

occupant and pedestrian impact simulation and for simulation of vibration

transmission as related to seating comfort. Compared to the facet occupant model, the neck, arms and lower extremities are modelled in more detail as well as active

behaviour to keep the initial position of the neck, spine, hips and elbows are

modelled. Besides occupant crash conditions (frontal, rear, side and vertical), the

model is suitable for pedestrian impact and low severity loading like pre-crash braking. The outer surface of the active human model is represented by facets similar

to that of the facet occupant model. The active human model is available in two

versions, a sitting model and a standing model. The specific features and guidelines of the facet active human model are described in the MADYMO Model Manual.

1.1.4 Facet pedestrian model

The facet pedestrian mode is identical to the standing facet active human model, except that it does not include active behaviour. This model can be used for

pedestrian impact simulations with an FE vehicle model, and is described in Chapter

4.

1.1.5 Ellipsoid pedestrian models

The outer geometry of the ellipsoid pedestrian models is represented by ellipsoids,

which provide a less accurate representation of the geometry but result in shorter

computation times than facets. The inertial properties of the pedestrian segments are incorporated in the rigid bodies of the pedestrian models. In the ellipsoid pedestrian

models, structural deformation of flexible components is lumped in kinematic joints

in combination with dynamic restraint models. This approach was applied in order to

simulate elastic long bone bending as well as fracture in femur and tibia. Deformation of soft tissues (flesh and skin) is represented by force-penetration based contact

characteristics for the ellipsoids. These characteristics are used to describe contact

interactions of the pedestrian model with itself and with its environment. Inertial properties of the pedestrian components are defined in the rigid bodies. The specific

features and guidelines of the pedestrian models are described in Chapter 5.

1.1.6 Available human models

The available occupant, active and pedestrian models are given in Table 1.2, Table

1.3 and Table 1.4 respectively. The human model files can be found in the directory

$MADHOME/share/dbs/human/3d.


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Table 1.2 Occupant models.

Model name File name Version

Facet small female occupant h_occ05fc 3.4

Facet mid-size-male occupant h_occ50fc 5.2

Facet large male occupant h_occ95fc 1.8

Facet 1.5-year-old child occupant h_occ1_5yfc 1.6

Facet 3-year-old child occupant h_occ3yfc 1.6



Scalable facet mid-size male occupant h_occ50fc.par 4.11

Scalable facet small female occupant h_occ05fc.par 2.12

Table 1.3 Active human models.


Facet mid-size male active human model in sitting position

h_act50fc_sitting 2.0

Facet mid-size male active human model in standing position

h_act50fc_standing 2.0

Table 1.4 Pedestrian models.


Facet mid-size male pedestrian h_ped50fc 3.0

Ellipsoid 3-year-old child pedestrian h_ped3yel 5.1

Ellipsoid 6-year-old child pedestrian h_ped6yel 5.1

Ellipsoid small female pedestrian h_ped05el 5.1

Ellipsoid mid-size male pedestrian h_ped50el 5.1

Ellipsoid large male pedestrian h_ped95el 5.1

Ellipsoid scalable mid-size-male pedestrian h_ped50el.par 5.1

1.2 Model validation

Much effort has gone into into validating the MADYMO human body models for a wide range of loading conditions. The human models have been validated extensively


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on segment as well as full body level with volunteer (low to mid severity impact) as well as PMHS test data (mid to high severity impact). For segment validation static as

well as dynamic tests have been used for full body only dynamic tests. Model

parameters that have a wide range in the literature and model parameters that could not be found in the literature have been tuned with these validation tests. A review of

segment impact and full body impact test data used for model validation is given for

each type of human model in the corresponding chapter.

1.3 User instructions

The ‘user instructions’ sections of the corresponding chapters in this manual describe how to handle the human models model-specific. In this section, information is given

to guide users through implementing human models in their own applications.

1.3.1 Human model files

Like the MADYMO dummy models, each MADYMO human model is supplied in

two files: a user-file (<filename>_usr.xml) and an include-file (<filename>_inc.xml).

The user-file contains the human model system, in which the user-interactive human

model elements are defined and the include-file is called. The user-interactive elements are those model elements that may need modification when applying the

human model. Besides the human model system, the user-file contains the required

control elements and a reference space system. This makes it a complete MADYMO input deck containing the human model defined in its standard position. The user can

implement more systems, system interactions (contact definitions between different

system), loads applied to whole systems etc. in the user-file to complete the model for a particular application.

The include-file contains the human model itself, including features like pre-defined

contact of the human model with itself. It is strongly advised not to modify any

parameters in the include-file, since this may affect the performance of the human model. It is also recommended not to modify the BELT elements that are defined in

the facet occupant human model user-files, since these are part of these models. (For

user- and include-file architecture see also MADYMO Model Manual.)

The human models can be applied in two ways:

1. by building an ‘environment’ model around the human model in the user-file,

2. by including the human model system (the SYSTEM.MODEL element in the

user-file), accessory belts and functions in an existing ‘environment’ model input deck.


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When calling human model output signals, or defining loads on and (contact) interactions with the human model, reference must be made to the human model

system. This can be done by referring either to the system ID or the system NAME.

For the facet occupant and the pedestrian models, a human model can be included more than once in an application, by making the system IDs and NAMEs unique (no

reference is made to ID or NAME inside these a human models). For the active

human model the system model has to be kept at 99, and thus only one active human

model can be used in a application. Note that the DEFINE elements used for some human models can be included only once and hence will be identical in each human

model present in one simulation.

1.3.2 Integration method and time step

Each human model has a recommended integration method and minimum integration

time step for which it is validated and tested. The integration method and time step

are defined for each human model in the CONTROL.ANALYSIS_TIME element in the user-file. They are also given in the ‘user instructions’ section of the

corresponding chapter in this manual.

Note that the contact stiffnesses of the modelled environment mainly determine the

time step needed, thus stiffer contacts or contact interactions with high damping might need smaller time steps than the recommended time step of the human model.

1.3.3 Human model positioning

In order to position the human model, the INITIAL.JOINT_POS elements have to be used. All joints that are needed for positioning the human model are defined in the

INITIAL.JOINT_POS elements in the human model user-file. Positions of all other

joints are defined in the human model include-file, and these should not be edited by

the user.

For joints of type FREE and SPHERICAL the rotational degrees of freedom should

be defined either using the R1, R2 and R3 attributes in INITIAL.JOINT_POS, or in

the related ORIENTATION elements. The defined elements use the successive rotation method. Joints can be locked in the INITIAL.JOINT_STATUS elements.

A human model is by default positioned relative to the (global) reference space co-

ordinate system. However, the human model can be positioned relative to a body of another system. This can be done in the human attachment element

CRDSYS_OBJECT named ‘Human_Attachment’ and the associated orientation

‘Human_Attachment_ori’ in that element. The human attachment element

‘Human_Attachment’ is comparable to the dummy attachment element 'Dummy_attachment' in a dummy model, which is located at the H-point.


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All joints needed for human model positioning are listed in the human model positioning tables in the ‘user instructions’ section of the following chapters. In these

tables all rotations are referred to with the terms pitch, roll and yaw (see Figure 2.7,

Error! Reference source not found. and Figure 5.4). The directions given in the tables refer to positive translation and rotation directions. For all joints, the directions

are defined with respect to their co-ordinate system orientation, when the human

model is in its reference position.

The various human models each require a different positioning technique. These techniques are explained in the ‘user instructions’ section of the corresponding

chapters.

1.3.4 Contacts

All contacts with the human model itself are already included in the model include-

file. The user has to define the external contact interactions between the human model

and its environment. To facilitate this, the human models have pre-defined contact groups that can be used directly in the external contact interactions. These pre-defined

contact groups are available for all relevant human model components. Note that

these contact groups do not necessarily include all ellipsoids/elements/nodes of the

components, but are defined such that the relevant outer surface is covered. Model specific information on these contact groups is given in tables in the corresponding

chapters. It is recommended to define contact only if it is really needed, in order to

avoid an unnecessary increase in calculation time. As a start for a simulation, the most proper way is to define contact only where it is expected. Thereafter, the contact

assumptions should be checked, and necessary corrections and/or refinements can be

made. Some general guidelines for contact definitions can be found in the MADYMO

Theory Manual and the MADYMO Reference Manual.

1.3.5 Output

The most relevant output signals and injury criteria are predefined in the human

model include-file. All output signals are defined corresponding to the orientation of the body. Output signals are as far as possible filtered according to the SAE J211/1

sign convention. In order to avoid problems with filtering of output signals, it is

recommended to use an output time step of at least 1.0E-04 s (TIME_STEP under CONTROL_OUTPUT).

Output of the human model is called in the user-file. This is done in the

TIME_HISTORY.MB element inside the CONTROL.OUTPUT element. The user

can place these names in the elements inside the TIME_HISTORY.MB element in order to obtain these output signals.


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To obtain injury criteria output, all the output signals that are used for that criterion, must be called in the CONTROL_OUTPUT element. Model specific information on

the output signals and injury criteria is given in the tables in the ‘user instructions’

section in the corresponding chapter.

1.4 Examples

For each type of human model, one or more examples of an (validation) application are described in this manual. An overview of the available example application files

of the non-active human models is given in Table 1.5.

Table 1.5 Example application files.

Application model File name Version

Positioning of the facet mid-size male occupant model, method b

e_occ50fc_pos_b 1) 1.4.2

Frontal impact of the facet mid-size male occupant model

e_occ50fc_imp 1) 1.6

Lateral impact of the mid-size male pedestrian model

e_ped50el 1) 1.3

1) Available in the directory $MADHOME/share/appl/3d.

1.5 Required model licenses

Table 1.6 lists the required license module name for each of the MADYMO Human

models. The listed modules are in additions to the MADYMO /Solver Multibody and MADYMO/CPU licenses that are always required to run MADYMO models.

Ellipsoid and facet models do not require a MADYMO /Solver FEM license. Scalable

models will need a SCALER license in order to generate a scaled version of the model.

Table 1.6 Human body models and required licenses.

Human Body model name License

Facet 1.5-year-old child occupant MADYMO/ Human Models/ Full Body Child

Facet 3-year-old child occupant MADYMO/ Human Models/ Full Body Child



Facet small female occupant MADYMO/ Human Models


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Facet mid-size male occupant MADYMO/ Human Models

Facet large male occupant MADYMO/ Human Models

Scalable facet mid-size male occupant MADYMO/ Human Models

Scalable facet small female occupant MADYMO/ Human Models

Facet active human model MADYMO/ HumanActive

Facet mid-size male pedestrian MADYMO/ Human Models/ Pedestrian

Ellipsoid 3-year-old child pedestrian MADYMO/ Human Models/ Pedestrian

Ellipsoid 6-year-old child pedestrian MADYMO/ Human Models/ Pedestrian

Ellipsoid small female pedestrian MADYMO/ Human Models/ Pedestrian

Ellipsoid mid-size male pedestrian MADYMO/ Human Models/ Pedestrian

Ellipsoid large male pedestrian MADYMO/ Human Models/ Pedestrian

Scalable ellipsoid mid-size male pedestrian MADYMO/ Human Models/ Pedestrian


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2 Facet occupant models

The MADYMO facet occupant model described in this chapter is currently released

in seven body sizes. A small female model representing the 5th

percentile female population, a mid-size male model representing the 50

th percentile male model

population, and a large male model representing the 95th percentile male model are

available (Figure 2.1). Four child body sizes representing a 1.5, 3, 6 and 10-years-old are available (Figure 2.2). Please, note that the child occupant models are scaled from

adult anthropometries and hence they do not necessarily represent children in terms of

their biofidelic behaviour.

Figure 2.1 Adult size facet occupant models from left to right; large male, mid-size male

(middle), and small female (right).


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Figure 2.2 Child facet occupant models from left to right; 1.5, 3, 6 and 10-year-old.

2.1 Model description

The MADYMO model names and input file names of the facet small female occupant

model, the facet mid-size male occupant model and the large male facet occupant model are:

Facet small female occupant: h_occ05fc_usr.xml

h_occ05fc_inc.xml

Facet mid-size male occupant: h_occ50fc_usr.xml h_occ50fc_inc.xml

Large male facet occupant: h_occ95fc_usr.xml

h_occ95fc_inc.xml

The MADYMO model names and input file names of the child occupant models are:

1.5-year-old child: h_occ1_5yfc_usr.xml

h_occ1_5y fc_inc.xml


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3-year-old child: h_occ3yfc_usr.xml h_occ3y fc_inc.xml

6-year-old child: h_occ6yfc_usr.xml

h_occ6y fc_inc.xml

10-year-old child: h_occ10yfc_usr.xml

h_occ10y fc_inc.xml

Besides these models, a scaleable facet male and female human occupant model are

available:

Parameter model mid size male: h_occ50fc.par

Parameter model small female: h_occ05fc.par

Using the MADYMO/SCALER utility, these models can be scaled towards different anthropometry data sets. It is recommended, to use the male model to create male and

child models and to use the female model to create adult or teenage female models.

A target model anthropometry can be created either by defining an anthropometry data set of 35 values, by defining 14 x 4 fixed scale factors or by using the GEBOD

database. Additional to the geometric properties, the following mechanical properties

are also scaled towards the target anthropometry: mass, inertia, stiffness and contact

characteristics. Several anthropometrically extreme models, ranging from small children to large adults, have been created using the 3 possible methods. The

definition of the anthropometry values and the fixed scaling factors produced

acceptable scaled models, whereas the GEBOD database sometimes generated models with unacceptable deviations, especially when scaling towards children.

The main limitation of the scalable models is that no age based material dependency

is taken into account during the scaling. As a result, the response of the child models

is not completely biofidelic. Furthermore, the impact behaviour (injuries, range of motion, etc.) of all models other than the base model has not yet been validated.

2.1.1 Anthropometry

2.1.1.1 Adults

The anthropometry of the adult facet occupant models has been obtained from the

database of the RAMSIS software package (RAMSIS 1997). The Western European

population aged 18 to 70 years of 1984 was used. For the facet mid-size male occupant model simply medium typologies were selected for height, weight and


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sitting height. For the small female a very short and very slim model was selected in RAMSIS. The resulting body mass and sitting height were considered to be somewhat

extreme also in comparison to the small female Hybrid III crash dummy. This was

resolved in a second step using the BODYBUILDER submodule of RAMSIS. The proportion and corpulence have been adapted by modification of the percentile values

of their related key parameters, respectively sitting height and waist circumference.

For the sitting height the percentile value was changed from 2.2% to 5.0%, the waist

circumference changed from 14.9% to 18.0%. The same procedure was followed to create the large male occupant model. In the first step a very tall subject with a large

waist was selected in RAMSIS, however the resulting body mass was somewhat high

and the standing height and sitting height were considered too low. Therefore, the BODYBUILDER module was used in a second step with the standing height, the

sitting height and the body mass as key parameters. In Table 2.1 the resulting

anthropometry of the facet occupant models is described. Note that the large male occupant model with an erect sitting height of 1.00 m is considerably taller than the

95th percentile Hybrid III, which has an erect sitting height of only 0.935 m.

Table 2.1 Anthropometry of the adult facet occupant models.

Parameter Small female Mid-size male Large male

Standing height [m] 1.52 m 1.74 m 1.91 m

Sitting height [m] 0.81 m 0.92 m 1.00 m

Weight [kg] 49.8 kg 75.7 kg 101.1 kg

The mass distribution of the facet occupant models is based on the RAMSIS database. Rotational inertia was derived by integration over the segment volume, where for

each segment a homogeneous density was assumed. The neck rotational inertia has

slightly been increased to allow larger time steps for the MADYMO calculations.

2.1.1.2 Children

The child models anthropometries were based on the CANDAT database (Twisk

1993). This database was developed by TNO and used for determination of the anthropometry of the Q-series of dummies. The child human models therefore

represent an identical anthropometry as the Q-dummies.

The scaling of the child occupant models from the adult occupant models was done

using MADYMO/SCALER (Happee et al., 1998). In MADYMO/SCALER different scaling factors are specified for x-, y-, and z-dimensions and for different body parts.

Thus the model geometry can be adapted freely to the desired anthropometry


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parameters. In addition to the geometry, all other model parameters can be scaled. Based on the desired anthropometry parameters there is scaling of:

Geometry

Mass and moments of Inertia

Joint characteristics (stiffness, friction, damping and hysteresis), including that of

protected joints

Ellipsoids and penetration characteristics

Force models

Fracture levels

Sensor locations

Besides these properties, the child occupant models are identical to the adult occupant models. The differences exisiting in material properties between tissues of adults and

children, as well as developmental stages of development of various organs have not

been taken into account in the current models. The anthropometry of the child

models, obtained with scaling is shown in Table 2.3.

Table 2.3 Anthropometry of the facet child occupant models.

Parameter 1.5-year-old 3-year-old 6-year-old 10-year-old

Standing height [m] 0.81 0.95 1.16 1.44

Sitting height [m] 0.50 0.55 0.63 0.75

Weight [kg] 11.0 kg 14.5 kg 21.0 kg 35.5 kg

2.1.2 Configuration

The occupant models each consist of 92 bodies. The first branch connects the head and vertebral bodies to the pelvis. The second and third branch connects the bodies of

the left and right leg to the pelvis, respectively. The fourth and fifth branch connects

the fingers to the shoulders, respectively. The thumb is connected to the mid-hand joint on a separate branch from the fingers. The thorax and the abdomen each consist

of 4 flexible bodies that divide the thorax and abdomen in horizontal slices. Attached

to each slice at the left and right side and at the front, bodies have been placed for


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attachment of force models. The thorax and abdomen bodies are divided over 3 branches (front, left and right) for each slice.

2.1.3 Spine and neck

2.1.3.1 General

The lumbar, thoracic and cervical spine is modelled in such a way that it gives a

biofidelic response in a wide range of loading conditions. The vertebrae are described

by rigid bodies connected by free joints with lumped joint resistance (restraint)

models. The geometries of the lumbar and thoracic vertebrae are each described by a single ellipsoid. The geometries of the cervical vertebrae are extended with ellipsoids

representing the transverse processes and spinal processes.

The spine and neck translational and rotational resistance has been implemented using non-linear lumped joint resistance (restraint) models. Parameters were based on

literature data (Prasad & King 1974, Kapandji 1974, Yamamoto et al. 1989, Schultz

et al. 1979, Berkson et al. 1979, Markolf 1972, Panjabi 1994, Jager 1996, Kroonenberg 1997). These joint resistance models describe the dynamic response of

the intervertebral discs, ligaments and effects of muscular resistance in a global way.

The spine model has been validated statically and dynamically with both PMHS and

volunteer tests.

The neutral position of the spine in the facet occupant models represents the spinal

curvature of an erect standing person. In Figure 2.3 the spine and neck model with the

origins of the vertebral joints are shown.


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Figure 2.3 Spine and neck in frontal and lateral cross-sectional view. The co-ordinate

systems indicate the origins of the vertebral joints.

2.1.4 Thorax and abdomen

In an impact loading case the human thorax and abdomen can deform in a complex 3D manner due to contact but also due to spinal deformations. This has been

modelled by using flexible bodies (see MADYMO Theory Manual and Koppens

1988). The flexible bodies describe 3D deformations with only a few degrees of

freedom and are therefore efficient. The flexible bodies describe global deformations while the contact algorithm describes local deformation. The resulting capability to

model torso deformation was found to correspond with experimental data.

The thorax and the abdomen each consist of 4 flexible bodies. The flexible bodies divide the thorax and abdomen in horizontal slices, as is shown in Figure 2.4. The

geometry of the flexible bodies is determined by the position of the skin nodes of the

flexible body in concern. A point mass is assigned to each node.


22

Figure 2.4 Right view of the facet active human model with the arrows pointing to the

flexible bodies, and the rigid bodies shown as green dots.

The flexible bodies are each connected to the closest rigid vertebral body of the spine. Each flexible body is able to deform in 3 predefined deformation modes: 1 frontal

mode and 2 lateral modes (left and right). The modes were determined analytically as

linear functions of the co-ordinates of the nodes. The frontal mode contains both x-

and y-displacements, the lateral modes only contain y-displacements. The input options for the flexible bodies only allow linear stiffness and damping, which is not

sufficient for describing the demonstrated non-linear behaviour of the torso in impact.

Therefore, point restraints were added for modelling the frontal and lateral stiffness and damping of the flexible bodies, and the stiffness and damping in all modes were

set to negligible low values (setting these values to zero is not allowed in

MADYMO).

For attachment of the point restraints rigid bodies were added: 1 frontal, 1 left and 1

right of each flexible body. These rigid bodies are connected to the skin nodes of the

thorax flexible body 4




abdomen flexible body 4





23

flexible body. The point restraints at the frontal bodies and the lateral bodies only contribute to loading in the x-direction and y-direction, respectively. Coupling

between frontal and lateral deformation is taken into account by the frontal

deformation mode.

Vertical point restrains were added between the rigid bodies of each flexible body.

These point restraints do not only have a z-component, but also have a small x- or y-

component for frontal respectively lateral stiffness. This was done in order to obtain a

more realistic skin deformation.

The two lowest flexible bodies also model the iliac wings. Since no biomechanic data

was available the resistance for frontal loading of these two lowest flexible bodies is

based on a model of the Hybrid III 50th percentile dummy.

2.1.5 Pelvis

The pelvis bone is modelled by facets. The facet pelvis can be used in contact with

the environment. For example in a frontal impact simulation with a lap belt defining contact between the belt and the skin and the facet pelvis will result in a more realistic

occupant response than with skin only.

2.1.6 Shoulders

The shoulder forms a moving base for the upper extremity. It consists of a number of joints connecting the humerus, scapula, clavicle and sternum. Furthermore, the

scapula contacts the back of the thorax; it can glide over the scapulothoracic gliding

plane. This connection makes the shoulder a closed chain mechanism. In the facet occupant models the clavicle, scapula and humerus are described by rigid bodies

connected by spherical joints. The geometry of the clavicles is represented by

cylinders, the geometry of the scapulae is represented by simple triangular elements,

as is shown in Figure 2.5.

The joint characteristics are based on biomechanical data from Engin (1984). The

clavicles and the sternum deform during shoulder loading. In the model such

deformations are incorporated by force models, which allow translational degrees of freedom between the clavicle and sternum. The translational deformation

characteristics are based on PMHS axial clavicle loading experiments as well as finite

element simulations of clavicle and rib cage loading.

In the real human body, the scapula contacts the thorax. Active muscle force is

needed to maintain this contact and to stabilise the shoulder girdle. These complex

interactions between shoulder and thorax are modelled as a set of passive force

models. The scapula is supported on the spine by point restraints to T1 and T9. Thus,


24

the load transfer from shoulder to spine is modelled by the skeletal connection (scapula-clavicle-sternum-ribs-spine) and by these additional force models. The

resulting resistance of the shoulder model was verified against published quasi-static

volunteer test data as well as lateral impact data.

Figure 2.5 The shoulder model in frontal cross-sectional view. The co-ordinate systems

indicate the origins of the scapula joints, acromio-clavicular joints and

glenohumeral joints.

2.1.7 Limbs

The segments of the upper and lower limbs are all described by rigid bodies

connected by spherical joints. In impact conditions some passive bending is possible

in all rotational directions of all real human joints. Therefore, degrees of freedom, in which voluntary movement is not possible, are also included. The ranges of motion

(R.O.M.) of the different limb joints have been based on RAMSIS. Modelling has

been done by defining cardan or flexion torsion restraints with non-linear stiffness functions. The resistance parameters are based on literature data on passive human

joint properties (Engin et al. 1979-1989, Kapandji 1974, Ma et al. 1995).

The arm model contains 3-segment thumbs and a 3-segment description of the

combined fingers. The joints of thumbs and fingers have been locked, making the hands rigid. The leg model contains a 3-segment description of the foot. The joints

between the metatarsals (midfoot) and the foot have been locked. The outer geometry


25

of the feet has the form of shoes. The geometry of these shoes is from GINO shoe models and has been obtained from RAMSIS.

2.1.8 Skin

The outer surface of the facet occupant model (skin) is described by a mesh of triangular elements defined as a null material. The skin is divided into several

sections that are supported on the nearest bodies. In the thorax and abdomen area the

skin is supported by flexible bodies. Different parts of the skin have different contact

characteristics, based on validation.


The facet mid-size male occupant model has been validated extensively for impact

loading as described by de Lange et al. (2005). Two major categories of tests were

conducted: volunteer tests for low severity loading and post mortem human substitute (PMHS) tests for higher severity loading. The facet small female occupant model has

been validated as described in Happee et al. (2000a) using published small female

impactor corridors for the SID2s dummy (Daniel et al., 1995) and some other small

female PMHS tests. In sections 2.2.1 and 0 the blunt impactor tests and the sled tests that were used for the validation are described. The facet mid-size male occupant

model has also been validated for vertical vibration, see section 2.2.3.

Implementations of typical validation tests are described in the ‘examples’ section. The child human models are compared with corridors that were scaled based on a

method developed by Irwin & Mertz (1997). While the child models are merely

scaled adults, without a correct implementation of child specific structural and material differences, they are not validated models but research models.

2.2.1 Blunt impact tests

Blunt impact tests used for the validation of the facet occupant model are summarised

in Table 2.5. The modelled impactors of the various segment tests are all shown together with the male facet occupant model in Figure 2.6.


26

Figure 2.6 Frontal impactor locations (thorax, abdomen) and lateral impactor locations

(shoulder, thorax, pelvis).


27

Table 2.5 Blunt impact and drop tests used for validation of occupant models.

Model Test Reference

Segment Description Test object

Specifications

Small female shoulder

1 lateral impact PMHS 4.5 m/s, 14.0 kg Daniel et al. (1995)

Small female thorax

2 lateral impact PMHS 4.3, 6.7 m/s, 14.0 kg

Daniel et al. (1995)

Mid-size male head

2 frontal impact PMHSs 2.0, 5.5 m/s Don et al. (2003)

2 lateral drop PMHSs 2.0, 5.5 m/s ISO TR9790 (1997)

Mid-size male shoulders

4 lateral impact PMHSs 4.5-7 m/s ISO TR9790 (1997), Meyer et al. (1994), Lizee et al. (1998)

Mid-size male thorax

8 frontal impact PMHSs 3.4–9.9 m/s, 10.4–23.4 kg

Bouquet et al. (1994),

Neathery (1974), Kroell et al. (1971, 1974, 1976), Nahum et al. (1970,1975)

4 lateral impact PMHSs 3.3-6.7 m/s, 23.0-23.4 kg

Lizee et al. (1998), Talantikite et al. (1998), ISO TR9790 (1997)

2 rigid drop tests

PMHS 4.5, 6.3 m/s ISO TR9790 (1997)

Mid-size male abdomen

3 frontal impact PMHSs 6.1-10.4 m/s, 18.0-63.6 kg

Cavanaugh (1986), GESAC (2001), Don et al. (2003)

2 rigid drop tests on armrest

PMHSs 4.5, 6.3 m/s ISO TR9790 (1997)

Mid-size male pelvis

6 lateral impact PMHSs 3.5-10.0 m/s, 17.3-23.4 kg

Bouquet et al. (1994), ISO TR9790 (1997)

2 rigid drop tests

PMHSs 3.2, 4.5 m/s ISO TR9790 (1997)

Small female Side airbag deployment

PMHSs Happee et al. (2000a)

2.2.2 Sled tests

Sled tests used for the validation of the full body behaviour of the facet occupant

models are summarised in Table 2.6.


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Table 2.6 Sled tests used for validation of the full body behaviour of the facet occupant

models.


Description test object specifications

Mid-size male 9 frontal rigid seat sled tests

5 volunteers 15 G peak Thunnissen (1995)

Mid-size male 2 rear deformable seat sled tests

2 volunteers 4-5 G peak Kroonenberg et al. (1998)

Mid-size male 9 rear rigid seat sled tests

9 volunteers 3.6 G peak Ono et al. (1999)

Mid-size male 9 rear deformable seat sled tests

9 volunteers 3.6 G peak Ono et al. (1999)

Mid-size male 6 rear rigid seat sled tests

3 PMHS 9-12 G peak Bertholon et al. (2000)

Mid-size male Lateral rigid seat sled test

volunteer 6.7 G peak Ewing (1972)

Mid-size male Lateral rigid seat sled tests

PMHSs 20, 37 G peak, 6.8, 8.9 m/s

Happee et al. (2000a), ISO TR9790 (1997)

Mid-size male oblique rigid seat sled test

volunteer 11 G peak Philippens et al. (2004)

2.2.3 Vertical vibration

Vertical vibration tests used for the validation of the full body behaviour of the mid-

size-male facet occupant model are summarised in Table 2.7.

Table 2.7 Vertical vibration tests used for validation of mid-size male occupant models.


Description Test object Specifications

Facet mid-size male occupant

Vibration tests on rigid seat

11 volunteers 0.5-15 Hz, 0.4 G peak

Verver et al. (2003)

Facet mid-size male occupant

Vibration tests on standard car seat

11 volunteers 0.5-15 Hz, 0.4 G peak

Verver et al. (2003)


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2.2.4 Child model validation

The dynamic hub impactor tests of Neathery (1974) were simulated with all child

occupant models. The impactor mass and diameter were scaled according to the Irwin

& Mertz (1997) scaling method. An overview of the various simulations is given in Table 2.8. Additional data used to validate the 6 year old child model are summarized

in Table 2.9.

Table 2.8 Hub impactor tests used for assessment of performance of child occupant

models.


Description Test object Specifications

1.5-year-old Hub impactor test

Scaled corridor

2.9 kg, 4.3 and 6.7 m/s

Neathery (1974)

Irwin and Mertz (1997)

3-year-old Hub impactor test

Scaled corridor

3.8 kg, 4.3 and 6.7 m/s

Neathery (1974)



Scaled corridor

5.3 kg, 4.3 and 6.7 m/s

Neathery (1974)



Scaled corridor

10.0 kg, 4.3 and 6.7 m/s

Neathery (1974)


Table 2.9 Additional datasets used for validation of the 6 year old child model


Description Test object

Specifications

6-year-old Frontal thoracic pendulum

5 PMHS 3.5 kg, 6 m/s Ouyang et al (2006)

6-year-old Abdominal belt loading test

47 porcine 2 locations, 3 rates Kent et al (2006)

6-year-old Neck tension test

9 PMHS Quasi static Ouyang et al. (2005)


30



The recommended integration method and minimum integration time step for the

facet occupant models is given in Table 2.10.

Table 2.10 Recommended integration method and time step for the facet occupant models.

Model Integration method Time step (s)

Small female EULER ≤1.0E-05

Mid-size male EULER ≤1.0E-05

Large male EULER ≤1.0E-05

2.3.2 Positioning

Because of the flexibility of the facet occupant model’s spine and neck, it is a bit

more complex to position this model in a seat than a dummy model. The occupant

model must be in an equilibrium state at the start of a simulation. Otherwise, initial accelerations will take place. A pre-simulation is generally required to obtain this

equilibrium. Positioning of the facet occupant model is done in four steps:

1. The complete occupant model is positioned and orientated correctly with respect to its environment by initialising the position and orientation of the human joint

(Human_jnt). Vertebrae can be orientated in order to put the spine in a seating

position. The occupant model can best be positioned just above the seat with its pelvis at the correct horizontal position. In a relaxed seating position the human

spine is curved differently than in a standing position or a straight seating

position. To model a relaxed seating position the vertebral joints of the facet

occupant model can be rotated in the user-file in ORIENTATION.SUCCESSIVE_ROT. To put the spine of the facet occupant

model in a relaxed seating position the initial vertebral joint rotations should be

changed to the values given in Table 2.11 (seating position according to Davidsson et al. (1998)).

2. The extremities are orientated with respect to the parent component by changing

the orientation of the joints in the positioning elements (INITIAL.JOINT_POS).

The occupant can for example be put in a driving position.


31

3. A pre-simulation is performed in which the facet occupant model is put into the seat by a gravitational field only (acceleration field of -9.81 m/s

2 in z-direction).

The run time for positioning the facet occupant model needs to be large enough

for the occupant to find its equilibrium (typically about 1 s). To maintain the facet occupant model in an upright position when subjected to gravity, several methods

can be used. Depending on the situation a different positioning is preferred. In

case of simulations of live human behaviour, the active human model is

recommended (see Chapter 2). For PMHS tests, there are two options: however one likes to simulate a certain test, one should take into account the way the

PMHS was settled. For example, if the PHMS was kept upright with an

electromagnet attached to the top of his head, option a should be used. Option b is preferred for general simulations of PMHS behaviour.

a. To keep the head upright, a support as often applied in PMHS tests can

be simulated by defining a point-restraint with a constant force of 100 N in the z-direction (this compensates for the weight of the head and

vertebral masses) just above the head CG.

b. The settling of a human subject with only passive behaviour can be

simulated by defining a cardan restraint of about 1000 Nm/rad between OC and inertial space together with a point restraint of about 1000 N/m in

the x-direction and y-direction between the head and inertial space. For

an example file, see ‘e_occ50fc_pos_b.xml’ in $MADHOME/share/appl/3d.

4. joint position degrees of freedom (JOINT_DOF) of all joints in the user-file

should be defined in the output. The joints of which the initial positions are not

defined in the user-file should be locked. The output from the last time step in the JNTPOS file of the pre-simulation should be copied to the positioning elements

(INITIAL.JOINT_POS) of the impact simulation file. In the impact simulation

the user should remove the restraints used in the pre-simulation

When all joints in INITIAL.JOINT_POS are set to zero (except for the ankles), the

facet occupant model is in an erect standing position as is shown in Figure 2.7. This

position is called the reference position. In this position the joint translations and rotations are defined as shown in Figure 2.7. The default position is a seating position

as is shown in Figure 2.1.

The orientations of the translational (D) and rotational (R) DOF of the facet occupant

model positioning joints are given in Table 2.14. The positioning joints are schematically drawn in Figure 2.8.


32

Figure 2.7 Definition of joint translations and rotations of the facet occupant models. The occupant model is in its reference position.

Figure 2.8 Locations of positioning joints of the facet occupant model.

}

Scapula-ArmUp

Elbow

C7-T1, …, C1-Head

} L5-L4, …, T2-T1

Human joint Hip

Wrist

Knee

Ankle

Sacrum-L5

x

y

z

roll right

pitch down

yaw left


33

The model contains a large number of degrees of freedom, where many of these have only a limited range of motion. To obtain a realistic initial position care should be

taken that user-defined initial rotations and translations are within the range of

motion. Reasonable initial rotations of the limbs can be determined directly from the ranges of motion that are specified in the cardan and flexion-torsion restraint models

of the limbs. For the neck and spine joints both initial rotations and translations can

be specified. For neck and spine the ranges of motion cannot be seen in the user-file

nor in the include-file, since the joint resistance models are protected. Therefore, some information on the range of motion is given in Table 2.12 and Table 2.13.


34

Table 2.11: Vertebral joint rotations in a relaxed seating position according to Davidsson et.

al. (1998).

Joint orientation identifier

Degree of freedom

R1 R2 R3

Sacrum-L5_ori 0 0.1021 0

L5-L4_ori 0 0.0821 0

L4-L3_ori 0 0.0348 0

L3-L2_ori 0 0.0348 0

L2-L1_ori 0 0.0348 0

L1-T12_ori 0 0.0346 0

T12-T11_ori 0 0.0346 0

T11-T10_ori 0 0.0346 0

T10-T9_ori 0 0.0346 0

T9-T8_ori 0 0.0346 0

T8-T7_ori 0 0.0346 0

T7-T6_ori 0 0.0346 0

T6-T5_ori 0 0.0346 0

T5-T4_ori 0 0.0146 0

T4-T3_ori 0 0.0146 0

T3-T2_ori 0 0.0146 0

T2-T1_ori 0 0.0146 0

T1-C7_ori 0 0 0

C7-C6_ori 0 0 0

C6-C5_ori 0 0 0

C5-C4_ori 0 0 0

C4-C3_ori 0 0 0

C3-C2_ori 0 0 0

C2-C1_ori 0 0 0

C1-Head_ori 0 0 0


35

Table 2.12 Joints ranges of rotations.

Joint Minimum motion [rad]

Torque min. motion [Nm]

Maximum motion [rad]

Torque max. motion [Nm]

C0-C1:

roll right -0.0515 -1.5 0.0515 1.5

pitch down -0.1707 -7.5 0.1014 1.3

yaw left -0.0637 -1.5 0.0637 1.5

C1-C2:

roll right -0.0977 -10 0.0977 10

pitch down -0.1002 -7.5 0.1225 5

yaw left -0.3752 -1.5 0.3752 1.5

C2-C3:

roll right -0.105 -10 0.105 10

pitch down -0.0473 -7.5 0.0577 5

yaw left -0.0312 -1.5 0.0312 1.5

C3-C4:

roll right -0.1152 -10 0.1152 10

pitch down -0.0701 -7.5 0.0871 5

yaw left -0.0732 -1.5 0.0732 1.5

C4-C5:

roll right -0.1152 -10 0.1152 10

pitch down -0.0628 -7.5 0.1166 5

yaw left -0.0732 -1.5 0.0732 1.5

C5-C6:

roll right -0.084 -10 0.084 10

pitch down -0.0728 -7.5 0.1166 5

yaw left -0.0732 -1.5 0.0732 1.5

C6-C7:

roll right -0.0732 -10 0.0732 10

pitch down -0.0793 -2 0.0986 5

yaw left -0.063 -1.5 0.063 1.5

C7-T1:

roll right -0.042 -10 0.042 10


36

Joint Minimum motion [rad]

Torque min. motion [Nm]

Maximum motion [rad]

Torque max. motion [Nm]

pitch down -0.0419 -7.5 0.0523 5

Yaw left -0.021 -1.5 0.021 1.5

Thoracic joints:

pitch down -0.036 -48 0.065 88.14

roll right -0.03 -40.68 0.03 40.68

Yaw left -0.0509 -15.27 0.0509 15.27

Lumbar joints:

pitch down -0.122 -83 0.2094 142

roll right -0.1033 -25.8 0.1033 25.8

Yaw left -0.0175 -14.175 0.0175 14.175

Table 2.13 Joints ranges of displacements.

Joints Minimum disp [m]

Force at min. disp [N]

Maximum disp [m]

Force at max. disp [N]

T1-C2:

x-displacement -0.0001 -50 0.0011 50

y-displacement -0.0009 -50 0.0009 50

z-displacement -0.0007 -200 0.0033 400

Table 2.14 Positioning joints of the facet occupant models.

Joint description Identifier Degree of freedom

D1 / R1 D2 / R2 D3 / R3

Complete human Human_jnt X / Roll right Y / Pitch down Z / Yaw left

Sacrum-lumbar disc (L5-S1) Sacrum-L5_jnt Roll right Pitch down Yaw left

Lumbar interverterbal disc L5-L4_jnt Roll right Pitch down Yaw left

,, L4-L3_jnt Roll right Pitch down Yaw left



,, L1-T12_jnt Roll right Pitch down Yaw left


37


D1 / R1 D2 / R2 D3 / R3

Thoracic intervertebral disc T12-T11_jnt Roll right Pitch down Yaw left

,, T11-T10_jnt Roll right Pitch down Yaw left










Cervical intervertebral disc T1-C7_jnt Roll right Pitch down Yaw left

,, C7-C6_jnt Roll right Pitch down Yaw left






,, C1-Head_jnt Roll right Pitch down Yaw left

Right glenohumeral joint ScapulaR-ArmUpR_jnt Roll right Yaw left Pitch down

Right elbow ElbowR_jnt Yaw right Pitch down

Right wrist WristR_jnt Roll right

Left glenohumeral joint ScapulaL-ArmUpL_jnt Roll right Yaw left Pitch down

Left elbow ElbowL_jnt Yaw right Pitch down

Left wrist WristL_jnt Roll right

Right hip HipR_jnt Pitch down Roll right Yaw left

Right knee KneeR_jnt Roll right Pitch down Yaw left

Right ankle AnkleR_jnt Pitch down Roll right Yaw left

Left hip HipL_jnt Pitch down Roll right Yaw left

Left knee KneeL_jnt Roll right Pitch down Yaw left

Left ankle AnkleL_jnt Pitch down Roll right Yaw left


38

2.3.3 Contacts

The available contact groups (in the include-file) that can be used to define contact

between the occupant and its environment in the user-file are summarised in Table

2.15.

Table 2.15 Available contact groups in the facet occupant models to define contact with their environment.

Contact description Identifier Set

Complete occupant model HumanBody_gfe Elements

Complete occupant without arms BodyNoArms_gfe Elements

Complete occupant without head BodyNoHead_gfe Elements

Thorax Thorax_gfe Elements

Left arm ArmL_gfe Elements

Upper left arm Upper_ArmL_gfe Elements

Lower left arm Lower_ArmL_gfe Elements

Right arm ArmR_gfe Elements

Upper right arm Upper_ArmR_gfe Elements

Lower right arm Lower_ArmR_gfe Elements

Pelvis skin (including buttocks) Pelvis_gfe Elements

Left leg LegL_gfe Elements

Upper left leg Upper_LegL_gfe Elements

Left Knee KneeL_gfe Elements

Lower left leg (including knee) Lower_LegL_gfe Elements

Left shoe and foot FootL_shoeL_gfe Elements

Right leg LegR_gfe Elements

Upper right leg Upper_LegR_gfe Elements

Right Knee KneeR_gfe Elements

Lower right leg (including knee) Lower_LegR_gfe Elements

Right shoe and foot FootR_shoeR_gfe Elements

Head Head_gfe Elements

Neck Neck_gfe Elements

Left and right shoulder Shoulders_gfe Elements


39


Back side of occupant model HumanBody_backside_gfe Nodes

Left part of pelvis bone PelvisBoneLeft_gfe Nodes

Right part of pelvis bone PelvisBoneRight_gfe Nodes

2.3.4 FE belt positioning and contact definition

For the contacts with the belts, for most applications it is recommended to use the

contact group HumanBody_gfe. The belt can then be fitted with the XMADgic belt fitting tool. During the belt fitting, the initial conditions of the Scapula[LR]-

ArmUp[LR]_jnt and Elbow[LR]_jnt should be disabled to put the arms to the side.

2.3.5 Output

The occupant model output signals, defined in the include-file, are summarised in Table 2.16 and Table 2.17. The occupant model injury criteria, defined in the include-

file, are summarised in Table 2.18.

For the protected spine and neck joints the load output is generated by defining bracket joints and constraint load output. The Lower and Upper neck load cells have

been defined at the T1-C7 and C1-Head (OC) joint locations, respectively. The

constraint load output of the vertebral joints Sacrum-L5 to T2-T1 are not defined in

CONTROL_OUPUT by default, but the user can add them. The constraint load output is used to derive load cell signals in specified directions (see Table 2.17 for

neck load cells) and for the neck injury criteria FNIC and NIJ (see Table 2.18). Also,

the angular positions (ANG_POS) of the spine and neck bracket joints are defined as output in the include file. The angular positions are not defined in

CONTROL_OUPUT by default, but the user can add them.

Table 2.16 Occupant models output.

Signal Identifier Degree of freedom Filter

D1/R1 D1/R2 D1/R3

Head CG disp. w.r.t. IS6) HeadCG_lds x y z CFC1000

Head OC disp. w.r.t. IS HeadOC_lds x y z CFC1000

T1AO disp. w.r.t. IS T1AO_lds x y z CFC1000

Head CG disp. w.r.t. T1AO

HeadCG_T1AO_rds x y z CFC1000


40


D1/R1 D1/R2 D1/R3

Head OC disp. w.r.t. T1AO

HeadOC_T1AO_rds x y z CFC1000

Sternum velocities w.r.t. T1AO

Sternum_T1AO_dvl x y z CFC600

Ribs n velocities w.r.t. spine body

Ribsn_Spine_dvl1) y x z CFC180

Head CG acc. w.r.t IS HeadCG_lac x y z CFC1000

Head OC acc. w.r.t. IS HeadOC_lac x y z CFC1000

T1AO acc. w.r.t. IS T1AO_lac x y z CFC1000

Sternum acc. w.r.t. IS Sternum_lac x y z CFC1000

Sternum_CFC180_lac x y z CFC180

Pelvis acc. w.r.t. IS Pelvis_lac x y z CFC1000

Head CG angular acc. HeadCG_aac Roll right Pitch down Yaw left CFC1000

T1 angular acc. T1_aac Roll right Pitch down Yaw left CFC1000

Frontal abdomen disp. w.r.t. spine body

AbdomenFrontn1,2) x y z

Frontal thorax disp. w.r.t. spine body

ThoraxFrontn1,2) x y z

Right abdomen disp. w.r.t. spine body

AbdomenRn1,2) x y z

Right thorax disp. w.r.t. spine body

ThoraxRn1,2) x y z

Left abdomen disp. w.r.t. spine body

AbdomenLn1,2) x y z

Left thorax disp. w.r.t. spine body

ThoraxLn1,2) x y z

Head w.r.t. T1 cardan output2)

Head_wrt_T13) Roll right Pitch down Yaw left

T1 w.r.t. inertial space cardan output

T1_wrt_RefSpace3) Roll right Pitch down Yaw left

Head w.r.t. IS cardan output

Head_RefSpace3) Roll right Pitch down Yaw left

Lower neck torque NeckLow_Torque4) Roll right Pitch down Yaw left CFC600

Lower neck force NeckLow_Force4) x Y z CFC1000

Upper neck torque NeckUp_Torque4) Roll right Pitch down Yaw left CFC600


41


D1/R1 D1/R2 D1/R3

Upper neck force NeckUp_Force4) x y z CFC1000

Upper neck force NeckUp_Force_CFC6005) x y Z CFC600

1) n = 1 to 4, number of ribs, thorax or abdomen layer, see Figure 2.4. 2) This point restraint output can be found in the PTR file. 3) Note that the cardan output is given in successive rotations. The cardan output can be found in the

CAN file. 4) These output signals are used for calculation of the neck output specified in directions and for The

Neck Injury Criteria FNIC. The force output can be found in the RTF file and the torque output in the RTT file. It is recommended to use the specified neck output, see Table 2.17.

5) This output signal is used for the calculation of the Neck Injury Predictor NIJ, see Table 2.18. 6) IS=Inertial System


42

Table 2.17 Occupant models load cell output of lower and upper neck in specified directions.


D1/R1 D1/R2 D1/R3

Spec. lower neck forces:

Resultant NeckLowFRES1) CFC1000

For-rearward shear NeckLowFX_SHEAR1) x CFC1000

Lateral shear NeckLowFY_SHEAR1) y CFC1000

Axial NeckLowFZ_AXIAL1) z CFC1000

Spec. lower neck torques:

Resultant NeckLowMRES1) CFC600

Lateral NeckLowMX_ROLL1) Roll right CFC600

For-rearward NeckLowMY_PITCH1) Pitch down CFC600

Axial NeckLowMZ_YAW1) Yaw left CFC600

Spec. upper neck forces:

Resultant NeckUpFRES1) CFC1000

For-rearward shear NeckUpFX_SHEAR1) x CFC1000

Lateral shear NeckUpFY_SHEAR1) y CFC1000

Axial NeckUpFZ_AXIAL1) z CFC1000

Spec. upper neck torques:

Resultant NeckUpMRES1) CFC600

Lateral NeckUpMX_ROLL1) Roll right CFC600

For-rearward NeckUpMY_PITCH1) Pitch down CFC600

Axial NeckUpMZ_YAW1) Yaw left CFC600

1) The load cell output can be found in the INJURY file.


43

Table 2.18 Injury criteria of the facet occupant models.

Injury criteria Identifier Filter

Head Injury Criterion 36 ms HIC_inj2)

Contigious 3 ms criterion:

Head Con3ms_HeadCG_inj2) CFC1000

Chest Con3ms_Sternum_CFC180_inj2) CFC180

Chest Con3ms_Sternum_inj2) CFC1000

Cumulative 3 ms criterion:

Head Cum3ms_HeadCG_inj2) CFC1000

Chest filtered Cum3ms_Sternum_CFC180_inj2) CFC180

Chest Cum3ms_Sternum_inj2) CFC1000

Viscous Injury Response Criterion for rib layer n

VCRibsn_inj1,2)

Neck Injury Criteria:

Tension FNICTension_inj2,3) CFC1000

Shear FNICShear_inj2,3) CFC1000

Bending FNICBending_inj2,3) CFC1000 (force) CFC600 (torque)

Neck Injury Predictor:

Tension-extension NIJTensionExtension_inj2) CFC600 (force) CFC600 (torque)

Tension-flexion NIJTensionFlexion_inj2) CFC600 (force) CFC600 (torque)

Compression-extension NIJCompressionExtension_inj2) CFC600 (force) CFC600 (torque)

Compression-flexion NIJCompressionFlexion_inj2) CFC600 (force) CFC600 (torque)

Combined Thoracic Index CTI_inj2)

1) n = 1 to 4, number of ribs layer, see Figure 2.4. 2) The injury output can be found in the PEAK file. 3) This injury output can also be found in the INJURY file.


44

2.4 Examples

2.4.1 Frontal impact with a belt

An example application file of the facet occupant model with belts in a frontal impact

‘e_occ50fc_imp.xml’ can be found in $MADHOME/share/appl/3d.

2.4.2 Occupant model positioning method b

In section 2.3.2 different positioning methods have been described. Method ‘b’ is demonstrated in an example ‘e_occ50fc_pos_b.xml’, which can be found in

$MADHOME/share/appl/3d.


45

3 Facet active human model

The MADYMO facet active human model is described in the Madymo Model

manual.


46

4 Facet pedestrian model

The MADYMO facet pedestrian model described in this chapter is currently released

in one body size, being a mid-size male model representing the 50th percentile male

model population (Figure 4.1). This model is identical to the standing active human

model (Chapter 3), except for the controllers, which are not included in the facet

pedestrian model.

Figure 4.1 Facet pedestrian model.


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4.1 Model description A facet mid-size male pedestrian model is available. The input is given in the files:

Mid-size male: h_ped50fc_usr.xml

h_ped50fc_inc.xml

To run this model, the following licenses are required:

Mid-size male: MADYMO/Solver (Multibody)

MADYMO/Human Models/Pedestrian

Since the facet pedestrian model is identical to the standing active human model

(Chapter 3), except for the active behaviour, for the model description is referred to

Error! Reference source not found. - Error! Reference source not found..


The facet pedestrian model was validated using all post mortem human subject (PMHS) tests described in section Error! Reference source not found.. Since the

facet pedestrian model is identical to the standing facet active human model without

active behaviour, the responses of this model are almost similar to that of the standing active human model in the PMHS tests.



Table 4.1 Recommended integration method and time step for the facet pedestrian model.


Mid-size male EULER <1.0E-05

4.3.2 Positioning

In order to position the facet pedestrian model, the INITIAL.JOINT_POS elements

have to be used. All joints that are needed for positioning the facet pedestrian model are defined in the INITIAL.JOINT_POS elements in the user-file. Positions of all

other joints are defined in the include-file, and these should not be edited by the user.


48

A human model is by default positioned relative to the (global) reference space coordinate system. However, the human model can be positioned relative to a body of

another system. This can be done in the CRDSYS_OBJECT ‘Human_Attachment’

and the associated ORIENTATION ‘Human_Attachment_ori’. The human attachment element ‘Human_Attachment’ is comparable to the dummy attachment

element 'Dummy_attachment' in a dummy model, which is located at the H-point.

The orientations of the positioning joints are given in Table 4.2. In this table all

rotations are referred to with the terms pitch, roll and yaw, as well the anatomical terms for the arms and legs. The directions given in the tables refer to positive

rotation directions. For all joints, the directions are defined with respect to their

coordinate system orientation, when the human model is in its reference position, as shown in Figure 4.2, in which all initial rotations are equal to zero. The anatomical

terms for the rotations of the arms and legs are also in the DESCRIPTION attributes

in INITIAL.JOINT_POS in the user file.

Figure 4.2 Definition of joint translations and rotations of the facet pedestrian model in its

reference position.


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Table 4.2 Positioning joints of the facet pedestrian model.


D1 / R1 D2 / R2 D3 / R3


Lumbar intervertebral joint

L5_jnt X1) / Roll right1) Y1) / Pitch down Z1) / Yaw left1)

,, L4_jnt X1) / Roll right1) Y1) / Pitch down Z1) / Yaw left1)




Thoracic intervertebral joint

T12_jnt X1) / Roll right1) Y1) / Pitch down Z1) / Yaw left1)

,, T11_jnt X1) / Roll right1) Y1) / Pitch down Z1) / Yaw left1)











Cervical intervertebral joint

C7_jnt X1) / Roll right1) Y1) / Pitch down Z1) / Yaw left1)

,, C6_jnt X1) / Roll right1) Y1) / Pitch down Z1) / Yaw left1)





Atlanto-axial joint C1_jnt X1) / Roll right1) Y1) / Pitch down Z1) / Yaw left1)

Atlanto-occipital joint HeadOC_jnt X1) / Roll right1) Y1) / Pitch down Z1) / Yaw left1)

Sternum joint1) SternumUp_jnt1) X1) / Roll right1) Y1) / Pitch down1) Z1) / Yaw left1)


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D1 / R1 D2 / R2 D3 / R3

Left sterno-clavicular joint1)

SternoClavicularL _jnt1)

-X1) / Roll left1) Y1) / Pitch down1) -Z1) / Yaw right1)

Right sterno-clavicular joint1)

SternoClavicularR _jnt1)

X1) / Roll right1) Y1) / Pitch down1) Z1) / Yaw left1)

Left acromio-clavicular joint1)

AcromioClavicularL_jnt1)

Roll left1) Pitch down1) Yaw right1)

Right acromio-clavicular joint1)

AcromioClavicularR_jnt1)

Roll right1) Pitch down1) Yaw left1)

Left glenohumeral joint (shoulder)

GlenohumeralL_jnt Adduction (roll left)

Flexion (yaw right)

Lateral rotation (pitch up)

Right glenohumeral joint (shoulder)

GlenohumeralR_jnt Adduction (roll right)

Flexion (yaw left)

Lateral rotation (pitch up)

Left elbow ElbowL_jnt Flexion (yaw right)

Right elbow ElbowR_jnt Flexion (yaw left)

Left radio-ulnar joint RadioUlnarisL_jnt Supination (pitch down)

Right radio-ulnar joint RadioUlnarisR_jnt Supination (pitch down)

Left wrist WristL_jnt Flexion (roll left)

Adduction (yaw right)

Right wrist WristR_jnt Flexion (roll right)

Adduction (yaw left)

Left hip HipL_jnt Extension (pitch down)

Adduction (roll left)

Lateral rotation (yaw left)

Right hip HipR_jnt Extension (pitch down)

Adduction

(roll right) Lateral rotation (yaw right)

Left knee KneeL_jnt Adduction1) (roll left)

Flexion (pitch down)

Medial rotation1) (yaw right)

Right knee KneeR_jnt Adduction1) (roll right)

Flexion (pitch down)

Medial rotation1) (yaw left)

Left ankle AnkleL_jnt Lateral rotation (yaw left)

Plantarflexion (pitch down)

Inversion (roll left)

Right ankle AnkleR_jnt Lateral rotation (yaw right)

Plantarflexion (pitch down)

Inversion (roll right)

Left shoe joint1) ShoeL_jnt1) X1) / Roll right1) Y1) / Pitch down1) Z1) / Yaw left1)


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D1 / R1 D2 / R2 D3 / R3

Right shoe joint1) ShoeR_jnt1) X1) / Roll right1) Y1) / Pitch down1) Z1) / Yaw left1)

1) Not to be changed during manual positioning. Only for equilibrium, based on a settling simulation.

4.3.3 Contacts

Table 4.3 Available contact groups in the facet pedestrian model to define contact with its

environment.


Complete human model HumanBody_gfe Elements and nodes

Complete human without arms BodyNoArms_gfe Elements and nodes

Complete human without head BodyNoHead_gfe Elements and nodes

Head Head_gfe Elements and nodes

Neck Neck_gfe Elements and nodes

Thorax Thorax_gfe Elements and nodes

Pelvis Pelvis_gfe Elements and nodes

Complete left arm ArmL_gfe Elements and nodes

Complete right arm ArmR_gfe Elements and nodes

Upper left arm Upper_ArmL_gfe Elements and nodes

Upper right arm Upper_ArmR_gfe Elements and nodes

Lower left arm (incl. hand) Lower_ArmL_gfe Elements and nodes

Lower right arm (incl. hand) Lower_ArmR_gfe Elements and nodes

Complete left leg LegL_gfe Elements and nodes

Complete right leg LegR_gfe Elements and nodes

Upper left leg Upper_LegL_gfe Elements and nodes

Upper right leg Upper_LegR_gfe Elements and nodes

Lower left leg (excl. foot/shoe) Lower_LegL_gfe Elements and nodes

Lower right leg (excl. foot/shoe) Lower_LegR_gfe Elements and nodes

Left shoe ShoeL_gfe Elements and nodes

Right shoe ShoeR_gfe Elements and nodes


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4.3.4 Output

The facet pedestrian model output signals, defined in the include-file, are summarised

in Table 4.4 and Table 4.5. The facet pedestrian model injury criteria, defined in the

include-file, are summarised in Table 4.6.

Table 4.4 Facet pedestrian model time history output.


D1/R1 D1/R2 D1/R3

Head CG angular acc. HeadCG_aac Roll right Pitch down Yaw left CFC1000

T1 angular acc. T1_aac Roll right Pitch down Yaw left CFC1000

Head w.r.t. IS angular displacement

Head_ang Roll right Pitch down Yaw left CFC1000

T1 w.r.t. IS1) angular displacement

T1_ang Roll right Pitch down Yaw left CFC1000

Head w.r.t. T1 angular position Head_T1_ang Roll right Pitch down Yaw left CFC1000

Left/Right knee bending/torsion KneeS_ang10) Flexion Lateral bending

Torsion CFC1000

Head CG acc. w.r.t IS2) HeadCG_acc x y z CFC1000

Head OC acc. w.r.t. IS2) HeadOC_ acc x y z CFC1000

C1 acc. w.r.t. IS2) C1_acc_CFC60 x y z CFC60

T1 acc. w.r.t. IS2) T1_acc x y z CFC1000

T1_acc_CFC60 x y z CFC60

T12 acc. w.r.t. IS2) T12_acc x y z CFC1000

Sternum acc. w.r.t. IS2) Sternum_acc x y z CFC1000

Sternum_acc_CFC180 x y z CFC180

Pelvis acc. w.r.t. IS2) Pelvis_acc x y z CFC1000

Left/Right femur acc. w.r.t. IS2) FemurnS_acc 3,10) x y z CFC1000

Left/Right tibia acc. w.r.t. IS2) TibianS_acc 3,10) x y z CFC1000

Head CG disp. w.r.t. IS HeadCG_dis x y z CFC180

Head OC disp. w.r.t. IS HeadOC_dis x y z CFC1000

T1 disp. w.r.t. IS T1_dis x y z CFC1000

Head CG position w.r.t. IS HeadCG_pos x y z CFC180

T1 position w.r.t. IS T1_pos x y z CFC180

Pelvis position w.r.t. IS Pelvis_pos x y z CFC180


53


D1/R1 D1/R2 D1/R3

Left knee position w.r.t. IS KneeS_pos10) x y z CFC180

Left/Right ankle position w.r.t. IS

AnkleS_pos10) x y z CFC180

Head CG velocity w.r.t. IS HeadCG_vel x y z CFC180

Head CG disp. w.r.t. T1 HeadCG_T1_dis x y z CFC1000

Head OC disp. w.r.t. T1 HeadOC_T1_dis x y z CFC1000

Left/Right knee shear/compression

KneeS_dis10) Fore/aft shear

Lateral shear

Tension CFC1000

Sternum displacement/velocities w.r.t. T1

Sternum_T1_dvl x y z CFC600

Chest deflection/velocity at rib n w.r.t. spine

Ribsn_Spine_dvl4) x CFC180

Lateral chest deflection/velocity at left rib n w.r.t. spine

RibnL_Spine_dvl5) y CFC180

Lateral chest deflection/velocity at right rib n w.r.t. spine

RibnR_Spine_dvl5) y CFC180

Upper neck force NeckUp_lce_F_CFC6006) x y z CFC600

Upper neck force NeckUp_lce_F6) x y z CFC1000

Upper neck torque NeckUp_lce_T6) Roll right Pitch down Yaw left CFC600

Head OC force HeadOC_lce_F6) x y z CFC1000

Head OC torque HeadOC_lce_T6) Roll right Pitch down Yaw left CFC600

Cn force Cn _lce_F6,7) x y z CFC1000

Cn torque Cn _lce_T6,7) Roll right Pitch down Yaw left CFC600

Tn force Tn _lce_F6,8) x y z CFC1000

Tn torque Tn _lce_T6,8) Roll right Pitch down Yaw left CFC600

Ln force Ln _lce_F6,9) x y z CFC1000

Ln torque Ln _lce_T6,9) Roll right Pitch down Yaw left CFC600

Left/Right hip force HipS_lce_F6,10) x11) y11) z CFC600

Left/Right femur force FemurS_lce_F6,10) x y z CFC600

Left/Right femur torque FemurS_lce_T6,10) x y z CFC600

Left/Right upper tibia force TibiaUpS_lce_F6,10) x y z CFC600

Left/Right upper tibia torque TibiaUpS_lce_T6,10) x y z CFC600

Left/Right mid tibia force TibiaMidS_lce_F6,10) x y z CFC600


54


D1/R1 D1/R2 D1/R3

Left/Right mid tibia torque TibiaMidS_lce_T6,10) x y z CFC600

Left/Right low tibia force TibiaLowS_lce_F6,10) x y z CFC600

Left/Right low tibia torque TibiaLowS_lce_T6,10) x y z CFC600

1) IS=Inertial System 2) Acceleration outputs are corrected for acceleration fields in x and y 3) n=1 to 4, from proximal to distal. 4) n = 1 to 4, from lower to upper. 5) n = 2 to 4, from lower to upper. 6) These output signals are used for calculation of the load cell output and for injury criteria. The force

output can be found in the RTF file and the torque output in the RTT file. It is recommended not to use these signals, but the load cell output as listed in Error! Reference source not found..

7) n = 1 to 7, neck vertebrae from upper to lower. 8) n = 1 to 12, thoracic vertebrae from upper to lower. 9) n = 1 to 5, lumbar vertebrae from upper to lower. 10) S = L or R, for left or right leg. 11) Hip joint orientations are: x is lateral y is frontal.

Table 4.5 Facet pedestrian model load cell output (in injury file).


D1/R1 D1/R2 D1/R3

Upper neck force NeckUp_Fdir_lce1) x y z CFC1000

Upper neck torque NeckUp_Mdir_lce1) Roll right Pitch down Yaw left CFC600

Head OC force HeadOC_Fdir_lce1) x y z CFC1000

Head OC torque HeadOC_Mdir_lce1) Roll right Pitch down Yaw left CFC600

Cn force Cn _Fdir_lce1,2) x y z CFC1000

Cn torque Cn _Mdir_lce1,2) Roll right Pitch down Yaw left CFC600

Tn force Tn _Fdir_lce1,3) x y z CFC1000

Tn torque Tn _Mdir_lce1,3) Roll right Pitch down Yaw left CFC600

Ln force Ln _Fdir_lce1,4) x y z CFC1000

Ln torque Ln _Mdir_lce1,4) Roll right Pitch down Yaw left CFC600

Left/Right hip force HipS_Fdir_lce1,5) x6) y6) z CFC600

Left/Right femur force FemurS_Fdir_lce1,5) x y z CFC600

Left/Right femur torque FemurS_Mdir_lce1,5) x y z CFC600


55


D1/R1 D1/R2 D1/R3

Left/Right upper tibia force

TibiaUpS_Fdir_lce1,5) x y z CFC600

Left/Right upper tibia torque

TibiaUpS_Mdir_lce1,5) x y z CFC600

Left/Right mid tibia force

TibiaMidS_Fdir_lce1,5) x y z CFC600

Left/Right mid tibia torque

TibiaMidS_Mdir_lce1,5) x y z CFC600

Left/Right low tibia force

TibiaLowS_Fdir_lce1,5) x y z CFC600

Left/Right low tibia torque

TibiaLowS_Mdir1,5) x y z CFC600

1) dir = res, x, y, z. 2) n = 1 to 7, neck vertebrae from upper to lower. 3) n = 1 to 12, thoracic vertebrae from upper to lower. 4) n = 1 to 5, lumbar vertebrae from upper to lower. 5) S = L or R, for left or right leg. 6) Hip joint orientations are: x is lateral y is frontal.

Table 4.6 Injury criteria of the facet pedestrian model.


Head Injury Criterion 15 ms HIC15_inj2) CFC1000

Head Injury Criterion 36 ms HIC36_inj2) CFC1000


Head Con3ms_HeadCG_inj2) CFC1000

Chest Con3ms_Sternum_CFC180_inj2) CFC180

Chest Con3ms_Sternum_inj2) CFC1000

T1 Con3ms_T1_inj2) CFC1000

T12 Con3ms_T12_inj2) CFC1000

Pelvis Con3ms_Pelvis_inj2) CFC1000


Head Cum3ms_HeadCG_inj2) CFC1000

Chest filtered Cum3ms_Sternum_CFC180_inj2) CFC180

Chest Cum3ms_Sternum_inj2) CFC1000


56


T1 Cum3ms_T1_inj2) CFC1000

T12 Cum3ms_T12_inj2) CFC1000

Pelvis Cum3ms_Pelvis_inj2) CFC1000

Viscous Injury Response Criterion for rib layer n

VCRibsn_inj1,2,3) CFC180

Lateral Viscous Injury Response Criterion for left rib layer n

VCRibnL_inj1,2,4) CFC180

Lateral Viscous Injury Response Criterion for right rib layer n

VCRibnR_inj1,2,4) CFC180

Neck NIC Forward:

Tension FNICTension_inj1) CFC1000

Shear FNICShear_inj1) CFC1000

Bending FNICBending_inj1) CFC1000 (force) CFC600 (torque)

Neck NIC Rearward: NIC_rearward_C1_T11,2) CFC60

Neck combined injury criteria:

Nij Tension-extension NTE_inj1,2) CFC600 (force) CFC600 (torque)

Nij Tension-flexion NTF_inj1,2) CFC600 (force) CFC600 (torque)

Nij Compression-extension NCE_inj1,2) CFC600 (force) CFC600 (torque)

Nij Compression-flexion NCF_inj1,2) CFC600 (force) CFC600 (torque)

Nkm Flexion-anterior NFA_inj1,2) CFC600 (force) CFC600 (torque)

Nkm Extension-anterior NEA_inj1,2) CFC600 (force) CFC600 (torque)

Nkm Flexion-posterior NFP_inj1,2) CFC600 (force) CFC600 (torque)

Nkm Extension-posterior NEP_inj1,2) CFC600 (force) CFC600 (torque)

Combined Thoracic Index CTI_inj2)

Left Femur Force Criterion FFCL_inj1) CFC600

Right Femur Force Criterion FFCR_inj1) CFC600

1) This injury output can be found in the INJURY file.


57

2) The injury output can be found in the PEAK file. 3) n = 1 to 4, from lower to upper. 4) n = 2 to 4, from lower to upper.


58

5 Ellipsoid pedestrian models

The MADYMO ellipsoid pedestrian models described in this chapter is currently

released in five body sizes. A small female model representing the 5th percentile

female population, a mid-size male model representing the 50th

percentile male model

population, and a large male model representing the 95th percentile male model are

available, and two child body sizes representing a 3 and 6-yeas-old are available (Figure 5.1). Please note that the child occupant models are scaled from adult

anthropometries and hence they do not necessarily represent children in terms of their

biofidelic behaviour.

Figure 5.1 Ellipsoid pedestrian models, from left to right; 3-year-old child, 6-year-old

child, small female, mid-size male and large male.


59

5.1 Model description

The MADYMO model names and input file names of the ellipsoid pedestrian models are:

3-year-old child: h_ped3yel_usr.xml

h_ped3yel_inc.xml

6-year-old child: h_ped6yel_usr.xml h_ped6yel_inc.xml

Small female: h_ped05el_usr.xml

h_ped05el_inc.xml

Mid-size male: h_ped50el_usr.xml

h_ped50el_inc.xml

Large male: h_ped95el_usr.xml h_ped95el_inc.xml

Besides these models, a scaleable pedestrian model is available:

Parameter model mid size male: h_ped50el.par

Using the MADYMO/SCALER utility, this model can be scaled towards different anthropometry data sets.

5.1.1 Anthropometry

The mid-size male pedestrian model was developed first. The anthropometry of this model was, similar to the facet occupant models, based on the database of the

RAMSIS software package (RAMSIS, 1997). Like for the facet occupant models, the

Western European population aged 18-70 years in 1984 has been used. Afterwards, the mid-size male pedestrian model has been scaled towards a 3-year-old child, a 6-

year-old child, a small female and a large male model (see Figure 5.1). The

anthropometries of the small female and large male pedestrian models were also

based on the RAMSIS database. The anthropometries of the 3- and 6-year-old child were based on the specification of the Q child dummies. Global anthropometry

specifications are given in Table 5.1.


60

Table 5.1 Anthropometry of the ellipsoid pedestrian models.

Parameter 3 year old child

6 year old child

Small female

Mid-size male

Large male

Standing height [m] 0.95 1.17 1.53 1.74 1.91

Seated height [m] 0.55 0.64 0.81 0.92 1.00

Shoulder breadth [m] 0.25 0.28 0.40 0.47 0.52

Knee height [m] 0.28 0.35 0.47 0.54 0.59

Weight [kg] 14.5 23.0 49.77 75.7 101.1

The scaling of the pedestrian models was done using MADYMO/SCALER (Happee

et al., 1998). In MADYMO/SCALER different scaling factors are specified for x-, y-,

and z-dimensions and for different body parts. Thus the model geometry can be

adapted freely to the desired anthropometry parameters. In addition to the geometry, all other model parameters can be scaled. Based on the desired anthropometry

parameters there is scaling of:

Geometry

Mass and moments of Inertia

Joint characteristics (stiffness, friction, damping and hysteresis), including that of

protected joints

Ellipsoids and penetration characteristics

Force models

Fracture levels

Sensor locations

5.1.2 Configuration

The pedestrian models each consist of 52 rigid bodies, organised in 7 configuration

branches. The outer surface is described by 64 ellipsoids and 2 planes. The first branch connects the head and thorax to the pelvis. The second and third branch

connect the bodies of the left and right arm to T1, respectively. The fourth and fifth

branch connect the bodies of the left and right leg to the pelvis, respectively. The

heels are each connected to the mid-foot joint by a separate branch.


61

5.1.3 Spine and neck

The spine and neck are modelled by 4 kinematic joints. The spine consists of 1

spherical joint at lumbar location and 1 free joint at thoracic location. The neck is

modelled by 2 free joints at the lower neck location (T1-C7) and 1 at the upper neck (C1-Head OC) location, respectively. The free joints in the spine and neck allow

elongation. The stiffness in the different directions is modelled by six-DOF restraints

at the joint locations. The rotational stiffnesses in the spine are based on Yang et al.

(2000). The translational stiffness in the z-direction is based on the resultant elongation stiffness of the facet occupant models. The translational stiffnesses in x-

and y-direction are higher than in z-direction, in order to prevent lateral translation. In

the z-direction also damping coefficients are added, which are also based on the facet occupant models.

5.1.4 Thorax and abdomen

For application in contact with vehicle models, it was considered desirable to represent each torso section (pelvis, abdomen, ribs, shoulder and for female also

breasts) by just one ellipsoid of sufficient size. The ellipsoids are sufficiently large to

avoid unrealistic discontinuities, when ellipsoids contact the edges of vehicle parts,

like the bonnet leading edge. In defining the ellipsoids it was already taken into account that scaled pedestrian models should also interact realistically with vehicle

models. Using few ellipsoids also diminishes the chance on multiple contacts with

one vehicle part. When using combined contact functions, multiple contacts with one vehicle part lead to a too high resultant stiffness.

Contact characteristics have been implemented for lateral loading of pelvis, abdomen,

ribs and shoulder. The contact characteristics (stiffness, hysteresis, damping) were

based on data found in literature and optimized in simulations of a large range of PMHS impactor tests on various body parts, see Section 5.2. Based on various pelvis

impactor simulations, different contact stiffness characteristics were used for the

lateral and rear part of the pelvis to represent the difference in the amount of flesh in these areas.

5.1.5 Hip

The hip joint is modelled by a spherical joint. The joint stiffness curves were taken from the validated pedestrian model by Yang & Lovsund (1997) who selected the hip

resistance after Frankel & Nordin (1980). The joint stiffness curves were found to

agree well with ranges of motion of the RAMSIS human model (Speyer and Seidl,

1997).


62

5.1.6 Knee

The knee is a complex joint with a strong coupling between the degrees of freedom.

The resistance for axial rotation is, for instance, dependent on the knee flexion angle.

In principle, geometric modelling of the relevant joint surface interactions and ligaments, muscles, and other soft tissues allows the definition of a general knee

model. However, detailed knee models for impact are still restricted in their range of

application. Therefore, the pedestrian knee is modelled by just one free joint and the

knee model characteristics have been optimized for an approximately extended position, as this position is most relevant for pedestrian loading. Linear and non-linear

joint resistance functions have been implemented in accordance with available data

from literature.

Linear lateral bending stiffness matching the dynamic data of Kajzer et al. (1997) has

been implemented, which is significantly larger than quasi-static values reported by

Piziali & Rastegar (1977) and Markolf et al. (1976), but comparable to EEVC requirements (EEVC, 1994). The knee flexion/extension stiffness has been

implemented using volunteer data (Engin, 1979a; Ma et al. 1995). Inward rotation of

the foot with respect to the femur has been implemented as a combination of knee and

ankle joint rotation. Using data from Engin (1979b) for both joints an identical resistance has been implemented for axial rotation.

For knee lateral shear the EEVC (1994, 1998a) has defined an injury tolerance level

of 4 kN force and 6 mm displacement. This results in a linear stiffness of 6.7E5 N/m, which has been applied in the pedestrian model. For pedestrian applications,

forward/rearward shear is considered of minor importance and therefore the stiffness

selected for lateral shear has also been applied for forward/rearward shear. Results

from Piziali & Rastegar (1977) indicate that this is acceptable for conditions with an extended knee. A linear stiffness was implemented for knee axial compression based

on the initial displacement (1 mm) of PMHS data of Walker & Hajek (1972).

5.1.7 Upper and lower leg

In pedestrian impacts, leg bending and resulting bone fracture is commonly found. To

account for this in the pedestrian model, bending and fracture properties were

implemented at several locations in the femur and tibia using bending/fracture joints. In both the upper and lower leg spherical joints have been implemented in order to

model bending and fracture. In Figure 5.2 all joint locations in the leg are specified:

the large spots show the hip, knee and ankle joints, the small spots show the locations

of the bending and/or fracture joints. The location of the middle bending joint in the femur corresponds with the location of the femur loadcell in the Hybrid III dummy.

The locations of the upper and lower bending joints in the tibia correspond with the

locations of the tibia loadcells in the Hybrid III dummy.


63

Figure 5.2 Left leg with joints. The large spots are the physical joints: hip, knee and ankle.

The small spots are joints for modelling fracture and/or bending of femur and

tibia.

Cardan restraints have been implemented at all the bending joints to model the bending stiffness of femur and tibia. Angular stiffness functions were derived from

simulations of quasi-static bending tests of Yamada (1973). The angular stiffness is

assumed to be equal throughout one long bone. Therefore, the same characteristics have been used for all three cardan restraints within one segment.

In car-pedestrian collisions fracture most often occurs in the lower leg. Therefore,

fracture joints have been implemented at the middle upper leg joint and all three

lower leg joints. All fracture joints are spherical joints that are initially locked until a pre-defined fracture trigger signal exceeds the fracture tolerance level. Bending

moments and shear forces were used as fracture trigger signals.

Once the fracture tolerance is exceeded, the angular resistance in the fracture joint is set to zero and both parts of the fractured bone are free to rotate relative to each other.

Minor rotational damping was implemented in the fracture joints to avoid numerical

instabilities once fracture occurred.

An overview of the fracture tolerances found in literature is summarized in Table 5.2.

knee joint

lower leg joint 4: fracture & bending



hip joint

upper leg joint 3: fracture & bending

ankle joint

upper leg joint 2: bending

upper leg joint 4: bending


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Table 5.2 Summary of leg fracture tolerances found in literature.

Shear force (kN)

Bending moment

(Nm)

Reference

Femur

3.9 310 Messerer (Males) 1)

4.3 160 Strømsøe, et al. (1995) 1)

2.5 233 Weber (Males) 1)

2.6 224 Yamada (1973)

3.1 Kress et al. (1993)

6.3 430 Rodmell & Lawrence (1998)

10.0 at 4 ms 600 at 4 ms Liu (2003)

6.5 at 10 ms 300 at 10 ms

Tibia

3.3 207 Messerer (Males) 1)

5.0 328 Nyquist, et al. (1985)

3.0 165 Weber (Males) 1)

2.7 194 Yamada (1973)

3.3-4.3 2) Kramer (1973)

7.5 at 4 ms 450 at 4 ms Yang, et al. (1997)

4.0 at 10 ms 250 at 10 ms

1) Summarized by Nyquist (1985).

2) Depending on the size of the impactor (5.7 - 8.5 inch diameter).

Based on these values, the fracture tolerance levels for the mid-size male pedestrian model were chosen. The implemented fracture levels for the upper and lower leg are

based on 50% injury risk, see Table 5.3. These levels can be adapted in the model for

studying a specific population, like for instance elderly people, provided that these

tolerance levels are know for this specific population group. This can be done by changing the values for the DEFINE elements in the user file

(Leg[Up|Low]Fract[Force|Torque]Lat[Pos|Neg])


65

Table 5.3 Fracture levels for the upper and lower leg, based on 50% injury risk.

Model part Torque [Nm] Reference Shear force [N]

Reference

3-year-old child:

Upper leg 55 scaled 1560 Scaled

Lower leg 50 scaled 1040 Scaled

6-year-old child:



Small female:



Mid-size male:

Upper leg 430 EEVC WG17 6000 Based on EEVC WG17

Lower leg 285 Nyquist et al. (1985) 4000 Yang et al. (2000)

Large male:



5.1.8 Ankle, foot and shoe

For the ankle and foot a MADYMO model of the ‘soft stop foot’ of the Hybrid III is

adopted. In this model the shoes of the Hybrid III have been added as separate bodies

allowing some relative motion between feet and shoes. The shoe model is also

included in the pedestrian model.

Since the ankle rotation stiffness of the Hybrid III is still not biofidelic and

mechanical failure has been observed (Crandall et al., 1996), the ankle joint resistance

parameters of the pedestrian model were adapted using biomechanical data. In volunteer and PMHS experiments the ankle dorsiflexion stiffness is found to depend

on the knee flexion angle. The rotational stiffness for ankle dorsiflexion was derived

from volunteer tests with extended knees (Crandall et al., 1996). The rotational

stiffness for inversion/eversion was also derived from volunteer data (Crandall et al., 1996). Inward rotation of the foot has been implemented as a combination of knee

and ankle rotation using data from Engin (1979b).


66


The human pedestrian model has been validated extensively. First, one series of leg shear and bending tests has been used (Kajzer, 1997). The contact characteristics

(stiffness, hysteresis, damping) with the various other body parts have been based on

data found in literature and optimized in simulations of a large range of PMHS

impactor tests on various body parts. Furthermore, three different sets of PMHS pedestrian-vehicle impact tests have been simulated to verify the biofidelity of the

pedestrian model. An overview of the validation is described below. An extended

description of the validation simulations and results can be found in Hoof et al. (2003). The implementation of a typical car-pedestrian test is described in the

‘examples’ section.

From the extended validation of the pedestrian models it can be concluded that:

The models accurately predict the global kinematics.

The models accurately predict the impact points on the vehicle, especially for

the head.

The models can reasonably predict the occurrence of fractures in the upper

and lower legs during the impact between the pedestrian and the vehicle.

The models can predict the shape and trends of the head, chest and pelvis

accelerations and the bumper forces.

5.2.1 Blunt impact tests

The blunt impact tests used for the validation of the pedestrian models are

summarised in Table 5.4. The different impactor test configurations simulated are

presented in Figure 5.3.


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Figure 5.3 Different impactor test configurations used for model validation.

Table 5.4 Blunt impact tests used for validation of the pedestrian models.

Segment Test Reference

description test object specifications

Lower extremities shear loading impact

PMHS lower extremities

15, 20 km/h, 40 kg Kajzer et al. (1990), Yang et al. (1995)

Lower extremities bending impact PMHS lower extremities

16, 20 km/h, 40 kg Kajzer et al. (1993), Yang et al. (1995)

Pelvis lateral impact 10 PMHSs 23.4 kg, 3.4 m/s Bouquet (1994)

lateral impact 10 PMHSs 23.4 kg, 6.6 m/s Bouquet (1994)

lateral impact 4 PMHSs 23.4 kg, 5.2 m/s Viano (1989)

lateral impact 4 PMHSs 23.4 kg, 9.8 m/s Viano (1989)

Abdomen oblique impact 6 PMHSs 23.4 kg, 4.8 m/s Viano (1989)

oblique impact 4 PMHSs 23.4 kg, 6.8 m/s Viano (1989)


Thorax lateral impact 6 PMHSs 12 kg, 5.3-8.5 m/s Talantikite (1998)


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lateral impact 5 PMHSs 16 kg, 5.7-7.2 m/s Talantikite (1998)




Shoulder lateral impact 7 PMHSs 23.4 kg, 5.5 m/s Meyer (1994)

lateral impact 5 PMHSs static Meyer (1994)

5.2.2 Car-pedestrian tests

The car-pedestrian tests used for the validation of the pedestrian models are

summarised in Table 5.5. Since PMHS subjects of different anthropometries were used in the tests, the pedestrian model was scaled to the specific body dimensions of

each PMHS subject prior to simulating the corresponding test.

Table 5.5 Full body car-pedestrian impact tests used for validation of the pedestrian

models.


Description Test object

specifications

Mid-size male scaled to PMHS size

5 tests, large

family car and optimized car

5 PMHSs 32-39.8 km/h,

deceleration 4.7-5.7 m/s2

EEVC (1998b)


10 tests, 3 different cars

10 PMHSs 25, 32, 39, 40 km/h

Ishikawa et al. (1993)


3 tests, small family car

3 PMHSs 25, 32, 39 km/h Yang et al. (2000)



The recommended integration method and minimum integration time step for the

pedestrian models is given in Table 5.6. The time step of 1.0E-05 s is sometimes required during fracture of the leg. If the fracture joints are not used, the time step can

be set to 2.5E-05.


69

Table 5.6 Recommended integration method and time step for the pedestrian models.


3-year-old child EULER ≤1.0E-05

6-year-old child EULER ≤1.0E-05

Small female EULER ≤1.0E-05

Mid-size male EULER ≤1.0E-05

Large male EULER ≤1.0E-05

5.3.2 Positioning

Positioning of the pedestrian model in MADYMO is done in three steps:

1. The complete pedestrian model is positioned and orientated correctly with respect

to its environment by initialising the position and orientation of the human joint (‘Human_jnt’), which is a free joint connecting the pedestrian model to its

environment. The pedestrian model must be placed at a position such that the

shoes touch the ground.

2. The extremities and other pedestrian model segments are orientated with respect

to the parent segment by changing the orientation of the corresponding bodies in

the positioning element (JOINT_DOF). The pedestrian model can for example be

put in a walking position.

3. Contact has to be defined between the pedestrian shoes and the ground. An

equilibrium between the gravitational force and the ground contact force acting

on the pedestrian model will have to be obtained. This can be done by performing short simulations the pedestrian in a gravitational field and change the initial

position of the Human_jnt, until the pedestrian stands still.

When all joints in INITIAL.JOINT_POS are set to zero (except for the ankles), the pedestrian model is in an erect standing position as is shown in Figure 5.4. This

position is called the reference position. In this position the joint translations and

rotations are defined as shown in Figure 5.4.

The orientations of the translational (D) and rotational (R) DOF of the pedestrian model positioning joints are given in Table 5.7. The positioning joints are

schematically drawn in Figure 5.5.


70

The fracture joints in the legs can be switched off by disabling the STATE.JOINT element in the user-file.

Figure 5.4 Definition of joint translations and rotations of the pedestrian models. The pedestrian is in its reference position.

x

y

z

roll right

pitch down

yaw left


71

Figure 5.5 Locations of the positioning joints of the pedestrian model.

Shoulder

Elbow

NeckUp-Head

LumbarUp-TorsoUp

Human joint Hip

Wrist

Knee

Ankle

LumbarLow-LumbarUp

TorsoUp-NeckLow NeckLow-NeckUp


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Table 5.7 Positioning joints of the pedestrian models.

Joint description

Identifier Degree of freedom

D1 / R1 D2 / R2 D3 / R3


Lower lumbar joint LumbarLow-LumbarUp_jnt Yaw right Pitch down Roll right

Upper lumbar joint LumbarUp-TorsoUp_jnt Roll right Pitch down Yaw left

T1 TorsoUp-NeckLow_jnt Pitch down

Neck joint NeckLow-NeckUp_jnt Roll right Pitch down Yaw left

Head OC NeckUp-Head_jnt Roll right Pitch down Yaw left

Hip HipS_jnt Roll right Pitch down Yaw left

Knee KneeS_jnt1) Pitch down Roll left Yaw left

Ankle AnkleS_jnt Yaw left Roll right Pitch down

Shoulder ShoulderS_jnt Pitch down Roll right

Elbow ElbowS_jnt Yaw left Pitch down

Wrist WristS_jnt Yaw left Roll right

1) S = L or R, stands for left and right side, respectively.

5.3.3 Contacts

The available contact groups (in the include-file) that can be used to define contact

between the pedestrian and its environment in the user-file are summarised in Table

5.8.

Since a lot of ellipsoids are defined for the legs and the thorax, it is very important to

carefully choose the contact between the ellipsoids of the pedestrian and the

contacting surface of the vehicle or the road.

It is recommended to very carefully use the EVALUATIONS option for ellipsoid-

ellipsoid contact. If this option is used, the complete contact force can switch from

one ellipsoid to another and back depending on the ellipsoid that is most penetrated.

With this switching of the contact force, large unrealistic vibrations can be introduced.


73

Table 5.8 Available contact groups in the pedestrian models to define contact with their

environment.

Contact description Identifier Ellipsoid / plane model

Head Head_gmb Head_ell

Upper arms ArmUpS_gmb1) ArmUpS_ell

Lower arms ArmLowS_gmb ArmLowS_ell HandS_ell

Shoulders Shoulders_gmb Collar_ell ShoulderL_ell ShoulderR_ell

Thorax sides ThoraxLateral_gmb RibsAllLateral_ell

Abdomen sides AbdomenLateral_gmb AbdomenMidLateral_ell

Pelvis Pelvis_gmb TorsoLowLateral_ell

PelvisLateral_ell HipL_ell HipR_ell

Upper legs LegUpS_gmb LegUp1S_ell LegUp2S_ell LegUp3S_ell

Lower legs LegLowS_gmb LegLow1S_ell LegLow2S_ell LegLow3S_ell LegLow4S_ell

Shoes ShoeS_gmb ShoeS_ell FrontShoeS_ell HeelShoeS_ell

Upper torso TorsoUp_gmb TorsoUpL_ell TorsoUpR_ell

Front part of shoes FrontShoeS_gmb FrontShoeS_ell

Inner part of shoe soles ShoeInrSoleS_gmb ShoeInrSoleS_pln

Heels HeelS_gmb HeelS_ell

Toes ToesS_gmb ToesS_ell

1) S = L or R, stands for left and right side, respectively.

5.3.4 Output

The pedestrian model output signals, defined in the include-file, are summarised in

Table 5.9 and Table 5.10. The pedestrian model injury criteria, defined in the include-

file, are summarised in Table 5.11. Note that the output in specified directions is in the injury output file.


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Table 5.9 Ellipsoid pedestrian models output.


D1 / R1 D2 / R2 D3 / R3

Head CG vel. w.r.t. IS6) HeadCG_lvl x y z CFC180

Head CG disp. w.r.t. IS HeadCG_lds x y z CFC180

Sternum relative vel. w.r.t. upper torso

Sternum_dvl x y z CFC180

Sternum disp. w.r.t. IS Sternum_lds x y z CFC180

Pelvis position w.r.t. IS Pelvis_pos x y z CFC180

Knee position w.r.t. IS KneeS_pos x y z CFC180

Foot position w.r.t. IS FootS_pos x y z CFC180

Head CG acc. HeadCG_lac x y z CFC1000

Sternum acc. Sternum_lac x y z CFC1000

Upper torso acc. TorsoUp_lac x y z CFC1000

Lower torso acc. TorsoLow_lac x y z CFC1000

Upper leg 2 acc. LegUp2S_lac1) x y z CFC1000

Lower leg 3 acc. LegLow3S_lac x y z CFC1000

Hip cardan output2) HipS Roll right Pitch down Yaw left

Knee cardan output KneeS Roll right Pitch down Yaw left CFC180

Knee shear KneeShearS Frontal shear

Lateral shear

Axial CFC180

Ankle cardan output AnkleS Roll right Pitch down Yaw left

Lower torso force TorsoLow-LumbarLow_Force3)

x y z CFC1000

Lower torso torque TorsoLow-LumbarLow_Torque3)

Roll right Pitch down Yaw left CFC1000

Lower neck force NeckLow_Force3) x y z CFC1000

Lower neck torque NeckLow_Torque3) Roll right Pitch down Yaw left CFC600

Upper neck forces NeckUp_Force3) x y z CFC1000

Upper neck torque NeckUp_Torque3) Roll right Pitch down Yaw left CFC600

Upper leg 3 forces LegUp3S_Force3) x y z CFC600

Upper leg 3 torque LegUp3S_Torque3) Yaw left Pitch up Roll left CFC600

Lower leg n force LegLownS_Force3,4) x y z CFC600

Lower leg n torque LegLownS_Torque3) Roll right Pitch down Yaw left CFC600


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D1 / R1 D2 / R2 D3 / R3

Upper leg 3 lateral torque5) LegUp3S_TorqueLat Yaw left Pitch up Roll left CFC600

Lower leg n lateral torque5) LegLownS_TorqueLat Roll right Pitch down Yaw left CFC600

Upper leg 3 lateral force5) LegUp3S_ForceLat x y z CFC600

Lower leg n lateral force5) LegLownS_ForceLat x y z CFC600

1) S = L or R, stands for left and right side, respectively. 2) Note that the cardan output is given in successive rotations. The cardan output can be found in the

CAN file. 3) These output signals are used for calculation of the neck, torso and leg output specified in directions.

The forces can be found in the FRC file, and the torques in the RTT file. It is recommended to use the specified neck, torso and leg output, see Table 5.10.

4) n = 2, 3 or 4, see Figure 5.2. 5) Used as trigger signals for the fracture joints 6) IS=Inertial System

Table 5.10 Pedestrian models load cell output of torso, lower and upper neck and legs in specified directions.


D1 / R1 D2 / R2 D3 / R3

Spec. lower torso force:

Resultant TorsoLow-LumbarLow_FRES

CFC 1000

For-rearward shear TorsoLow-LumbarLowFX_SHEAR

x CFC 1000

Lateral shear TorsoLow-LumbarLowFY_SHEAR

y CFC 1000

Axial TorsoLow-LumbarLowFZ_AXIAL

z CFC 1000

Spec. lower torso torque:

Resultant TorsoLow-LumbarLow_MRES

CFC 1000

Lateral TorsoLow-LumbarLowMX_ROLL

Roll right CFC 1000

For-rearward TorsoLow-LumbarLowMY_PITCH

Pitch down CFC 1000

Axial TorsoLow-LumbarLowMZ_YAW

Yaw left CFC 1000


76


D1 / R1 D2 / R2 D3 / R3

Spec. lower neck force: CFC 1000

Resultant NeckLowFRES CFC 1000

For-rearward shear NeckLowFX_SHEAR x CFC 1000

Lateral shear NeckLowFY_SHEAR y CFC 1000

Axial NeckLowFZ_AXIAL z CFC 1000

Spec. lower neck torque:

Resultant NeckLowMRES CFC 600

Lateral NeckLowMX_ROLL Roll right CFC 600

For-rearward NeckLowMY_PITCH Pitch down CFC 600

Axial NeckLowMZ_YAW Yaw left CFC 600

Spec. upper neck force:

Resultant NeckUpFRES CFC 1000

For-rearward shear NeckUpFX_SHEAR x CFC 1000

Lateral shear NeckUpFY_SHEAR y CFC 1000

Axial NeckUpFZ_AXIAL z CFC 1000

Spec. upper neck torque:

Resultant NeckUpMRES CFC 600

Lateral NeckUpMX_ROLL Roll right CFC 600

For-rearward NeckUpMY_PITCH Pitch down CFC 600

Axial NeckUpMZ_YAW Yaw left CFC 600

Spec. upper leg 3 force:

Resultant LegUp3S_FRES1) CFC 600

For-rearward shear LegUp3S_FX_SHEAR1) x CFC 600

Lateral shear LegUp3S_FY_SHEAR1) y CFC 600

Axial LegUp3S_FZ_AXIAL1) z CFC 600

Spec. upper leg 3 torque:

Resultant LegUp3S_MRES1) CFC 600

Lateral LegUp3S_MX_ROLL1) Roll right CFC 600

For-rearward LegUp3S_MY_PITCH1) Pitch down CFC 600

Axial LegUp3S_MZ_YAW1) Yaw left CFC 600

Spec. lower leg n force:


77


D1 / R1 D2 / R2 D3 / R3

Resultant LegLownS_FRES1,2) CFC 600

For-rearward shear LegLownS_FX_SHEAR1,2) x CFC 600

Lateral shear LegLownS_FY_SHEAR1,2) y CFC 600

Axial LegLownS_FZ_AXIAL1,2) z CFC 600

Spec. lower leg n torque:

Resultant LegLownS_MRES1,2) CFC 600

Lateral LegLownS_MX_ROLL1,2) Roll right CFC 600

For-rearward LegLownS_MY_PITCH1,2) Pitch down CFC 600

Axial LegLownS_MZ_YAW1,2) Yaw left CFC 600

1) S = L or R, stands for left and right side, respectively. 2) n = 2, 3 or 4, see Figure 5.2.

Table 5.11 Injury criteria of the pedestrian models.


Head Injury Criterion 15 ms HIC_inj1) CFC1000


Head Con3msHeadCG_inj1) CFC1000

Torso Con3msTorsoUp_inj1) CFC1000


Head Cum3msHeadCG_inj1) CFC1000

Torso Cum3msTorsoUp_inj1) CFC1000

Viscous Injury Response Criterion for sternum

VCSternum_inj1) CFC180

1) The injury output can be found in the PEAK file.

5.4 Example

5.4.1 Car-pedestrian impact

The example application file of a car-pedestrian impact ‘e_ped50el.xml’ can be found

in $MADHOME/share/appl/3d.


78

In this example a 32 km/h impact of a car against a pedestrian has been simulated. The vehicle model represents a 880 kg small family car and consists of six ellipsoids.

The bumper, the hood, the hood-edge and the windscreen are represented by one

ellipsoid each, and the wheels by two ellipsoids. The location of the center of gravity and moments of inertia of the car model were approximated, based on the one-

dimensional nature of the car motion. The dynamic characteristics of the bumper

system (force-penetration for the contact) were based on results from legform to

bumper impact tests by Schueler and Glasson (1998). The mechanical properties of the windscreen were based on the static data published by Yang et al. (2000).


79

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