ISO 13232-5:2005

Motorcycles - Test and analysis procedures for research evaluation of rider crash protective devices fitted to motorcycles - Part 5: Injury indices and risk/benefit analysis

ISO 13232-5;2005 provides: performance indices which can be correlated with human injuries; formulae which relate injury indices to probable injury cost; a consistent means of interpreting impact test results; a means of relating the results obtained from film analysis and instrumentation of the dummy to injuries sustained in accidents; a means of assessing both the combined and relative effects of multiple injuries; an objective means of quantifying injury cost using a single index; a means of verifying the analysis; a means of doing risk/benefit analysis of protective devices fitted to motorcycles, based upon the population of impact conditions identified in ISO 13232-2. ISO 13232 specifies the minimum requirements for research into the feasibility of protective devices fitted to motorcycles, which are intended to protect the rider in the event of a collision. ISO 13232 is applicable to impact tests involving: two-wheeled motorcycles; the specified type of opposing vehicle; either a stationary and a moving vehicle or two moving vehicles; for any moving vehicle, a steady speed and straight-line motion immediately prior to impact; one helmeted dummy in a normal seating position on an upright motorcycle; the measurement of the potential for specified types of injury, by body region; and evaluation of the results of paired impact tests (i.e. comparisons between motorcycles fitted and not fitted with the proposed devices). ISO 13232 does not apply to testing for regulatory or legislative purposes.

Motocycles — Méthodes d'essai et d'analyse de l'évaluation par la recherche des dispositifs, montés sur les motocycles, visant à la protection des motocyclistes contre les collisions — Partie 5: Indices de blessure et analyse risque/bénéfice

General Information

• Status: Published
• Publication Date: 07-Dec-2005
• ICS: 43.140 - Motorcycles and mopeds
• Technical Committee: ISO/TC 22/SC 38 - Motorcycles and mopeds
• Drafting Committee: ISO/TC 22/SC 38 - Motorcycles and mopeds
• Current Stage: 9060 - Close of review
• Completion Date: 02-Dec-2030

Relations

• Amended By: ISO 13232-5:2005/Amd 1:2012 - Motorcycles - Test and analysis procedures for research evaluation of rider crash protective devices fitted to motorcycles - Part 5: Injury indices and risk/benefit analysis - Amendment 1: Ground impact and injury costs
• Effective Date: 27-Nov-2021
• Revises: ISO 13232-5:1996 - Motorcycles - Test and analysis procedures for research evaluation of rider crash protective devices fitted to motorcycles - Part 5: Injury indices and risk/benefit analysis
• Effective Date: 15-Apr-2008

Overview

ISO 13232-5:2005 - “Motorcycles - Test and analysis procedures for research evaluation of rider crash protective devices - Part 5: Injury indices and risk/benefit analysis” - defines methods to quantify and interpret the injury potential and societal cost of rider protective devices fitted to motorcycles. The standard provides injury indices, probability models, and formulae to relate dummy instrumentation and film analysis to probable human injury and injury cost. It supports consistent interpretation of impact test results and enables objective risk/benefit analysis based on the impact conditions identified in ISO 13232-2. This part is intended for research evaluation and is explicitly not for regulatory or legislative testing.

Key topics and requirements

• Injury variables and indices: Defines the injury assessment variables (head, thorax, abdomen, neck, lower extremities) and how to convert measured signals into injury indices.
• Injury severity probabilities: Specifies probability functions that map measured variables (e.g., accelerations, compressions, penetrations, neck loads) to AIS injury severity probabilities.
• Injury cost model: Provides formulae and normative annexes to estimate probable medical/ancillary costs and to compute a single normalized injury cost index.
• Risk/benefit analysis: Procedures to assess population-level benefits and risks of protective devices across the ISO 13232-2 impact condition set, including paired impact test comparisons (with and without device).
• Verification and documentation: Requirements for validating analyses, documenting inputs/outputs, and reproducibility; includes example computer code and data annexes (injury costs, mortality rates, probability distributions).
• Special topics: Guidance on frangible component damage classification, combined-multiple-injury assessment, and neck injury modelling (detailed in informative annexes).

Applications and users

ISO 13232-5 is primarily for:

• Motorcycle safety researchers and academic investigators conducting feasibility or comparative studies.
• Vehicle and protective-device designers evaluating the effectiveness of rider crash protection (airbags, fairings, framing, leg guards).
• Crash test laboratories and biomechanical analysts interpreting dummy instrumentation and high-speed film data.
• Insurance and risk analysts estimating societal or economic impact of protective-device adoption. Note: This standard is research-focused and should not be used as a regulatory compliance test protocol.

Related standards

• ISO 13232 series (other Parts 1–4 and Part 2 for impact condition population) - use in combination to define full test protocols, impact scenarios, and dummy setup.
• Referenced normative annexes within ISO 13232-5 for injury costs, mortality data, and example calculation code.

Keywords: ISO 13232-5, motorcycle protective devices, injury indices, risk/benefit analysis, impact testing, dummy instrumentation, injury cost model, motorcycle safety research.

Standards Content (Sample)

INTERNATIONAL ISO
STANDARD 13232-5
Second edition
2005-12-15
Motorcycles — Test and analysis
procedures for research evaluation of
rider crash protective devices fitted to
motorcycles —
Part 5:
Injury indices and risk/benefit analysis
Motocycles — Méthodes d'essai et d'analyse de l'évaluation par la
recherche des dispositifs, montés sur les motocycles, visant à la
protection des motocyclistes contre les collisions —
Partie 5: Indices de blessure et analyse risque/bénéfice

Reference number
©
ISO 2005
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ii © ISO 2005 – All rights reserved

Contents Page
Foreword. vii
Introduction. viii
1 Scope.1
2 Normative references.2
3 Definitions and abbreviations .2
4 Requirements.3
4.1 Injury variables .3
4.2 Lower extremity injuries .4
4.3 Injury severity probabilities.4
4.4 Injury indices.5
4.5 Risk/benefit analysis .5
5 Procedures .5
5.1 Injury variables .5
5.2 Frangible component damage .10
5.3 Injury severity probabilities.10
5.4 Probability of discrete AIS injury severity level .15
5.5 Injury costs.17
5.6 Probability of fatality .18
5.7 Probable AIS .21
5.8 Normalized injury costs .22
5.9 Risk/benefit analysis .23
6 Documentation.27
Annex A (normative) Injury costs.28
Annex B (normative) Mortality rate .30
Annex C (informative) ICM Variable and subscript definitions .31
Annex D (informative) Example computer code of the injury cost model.34
Annex E (informative) Comparison of results to reference risk and benefit values .56
Annex F (informative) Example probable injury cost data.57
Annex G (informative) Probability distribution curves.69
Annex H (informative) Example cumulative distribution function plots.73

Annex I (informative) Example computer code for calculations of head contacts .74
Annex J (informative) AO/C1/C2 upper neck injury probabilities and injury cost.97
Annex K (informative) Estimated distribution of neck AO/C1/C2 injury severities in the LA/Hannover
database .120
Annex L (informative) Distribution of maximum neck forces and moments from computer simulations
of 498 LA/Hannover cases and 67 fatal USC cases .122
Annex M (informative) Injury criteria coefficient search algorithm used for neck injury criteria
identification.124
Annex N (informative) Dummy neck computer simulation validation .131
Annex O (informative) Rationale for ISO 13232-5 .144
Figures
Figure 1 — Chest potentiometer geometry shown for the upper sternum .8
Figure 2 — Risk of life threatening brain injury for HIC for t - t ≤ 0,015 s.21
2 1
Figure D.1 — Flow diagram of the injury cost model.55
Figure G.1 — Probability distribution of head injuries as a function of G (Kramer & Appel, 1990).70
max
Figure G.2 — Probability distribution of thoracic injury as a function of maximum resultant upper (or lower) sternum
compression (Kroell, et al., 1974).70
Figure G.3 — Probability distribution of thoracic injuries as a function of maximum resultant upper (or lower)
sternum velocity-compression (Lowne & Janssen, 1990).71
Figure G.4 — Probability distribution of human abdominal injuries as a function of maximum human abdominal
penetration (Rouhana, et al., 1990).71
Figure G.5 — Probability distribution of neck injury as a function of NII .72
max
Figure H.1 — Example of a continuous cumulative distribution function graph for change in an injury assessment
variable .73
Figure H.2 — Example of a discrete cumulative distribution function graph for change in an injury index.73
Figure J.1 — Forces and moments at t from computer simulations of 67 USC fatal cases and the best step-
max
wise fit envelopes of constant NII , providing the basis for the envelope shape.108
max
Figure J.2 — Forces and moments at t from computer simulations of 498 LA and Hannover cases and
max
envelopes of constant NII , providing the basis for the NII vs 50% injury probability .110
max max
Figure J.3 — Critical tension force vs the α coefficient, providing the basis for the α =3.1 .111
Figure J.4 — Neck AO/C1/C2 injury risk curves for the new MATD neck.112
Figure J.5 — Distribution of observed and predicted computer simulations .113
Figure J.6 — Comparison of the general shape and axes of the injury criteria for the new MATD neck to the
allowable limits proposed by NHTSA for the HIII 50 PAM neck (recognizing that the necks have very different
stiffnesses) .116
Figure J.7 — Neck AIS 3 + injury risk vs tension for the Hybrid III P50 male neck (Mertz & Prasad 2000) . 117
Figure J.8 — Neck AIS 3 + injury risk vs combined tension and extension for the Hybrid III P50 male neck (Mertz &
Prasad 2000) . 118
iv © ISO 2005 – All rights reserved

Figure L.1 — Maximum neck force and moment distributions for the new MATD neck (498 LA/Hannover cases and
67 USC fatal cases). 123
Figure M.1 — Convergence of the global search algorithm . 129
Figure M.2 — Convergence of the local search algorithm . 130
Figure N.1 — Laboratory test and computer simulation of forward neck flexion at 0,1 s. 133
Figure N.2 — Forward neck flexion response of laboratory test and computer simulation. 134
Figure N.3 — Laboratory test and computer simulation of rearward neck extension at 0,1 s. 135
Figure N.4 — Rearward neck extension response of laboratory test and computer simulation . 136
Figure N.5 — Laboratory test and computer simulation of lateral neck flexion at 0,1 s . 137
Figure N.6 — Lateral neck flexion response of laboratory test and computer simulation . 138
Figure N.7 — Computer simulation of neck torsion test at 0,1 s . 139
Figure N.8 — Neck torsion response of laboratory test and computer simulation . 140
Figure N.9 — Neck axial force response of laboratory impact test and computer simulation. 141
Figure N.10 — Full scale test and computer simulation of impact configuration 413-0/30 0,1 s after initial contact
.......................................................................................................................................................................... 142
Figure N.11 — Full scale test and computer simulation of 413-0/30 with new MATD neck. 143

Tables
Table 1a — Closed head injury severity probability as a function of G .12
max
Table 1b — Closed head injury severity probability as a function of HIC.12
Table 2 — Thoracic compression injury severity probability as a function of C and C .13
us,max ls,max
Table 3 — Thoracic injury velocity-compression severity probability as a function of VC and VC .13
us,max ls,max
Table 4 — Intra-abdominal penetration injury severity probability as a function of P .14
A,max
Table 5 — Neck combined loading injury severity probability as a function of NII.14
Table 6 — AIS injury severity level for frangible component damage.15
Table 7 — Example PlE,j determination.16
Table 8 — Permanent partial incapacity determination.16
Table 9 — Injury probability and probable AIS .19
Table 10 — Injury assessment variables, change in head injury potential, and injury indices to be calculated for
each impact configuration.24
Table 11 — Example table used to calculate the weighted cumulative distribution of change in maximum head
acceleration due to a protective device.26
Table A.1 — Medical costs.28
Table A.2 — Ancillary costs.29
Table B.1 — Mortality rates for all AIS combinations .30
Table C.1 — Variable definitions .31
Table C.2 — Body region subscript definition .32
Table C.3 — Other subscripts .32
Table F.1 — Legend for Table F.2 .57
Table F.2 — Example probable injury cost input/output results.58
Table J.1 — Summary of Accident Databases.99
Table J.2 — Distribution of neck AO/C1/C2 injuries in the USC fatal motorcycle accident database .103
Table J.3 — Distribution of neck AO/C1/C2 injuries in the LA/Hannover database.105
Table J.4 — Number of cases with observed and predicted injuries .105
Table J.5 — Force and moment normalizing coefficients for the new MATD neck.106
Table J.6 — Injury threshold coefficients for the 67 USC fatal cases with the new MATD neck .106
Table J.7 — Comparison of number of observed and predicted injuries by injury severity and direction.107
Table J.8 — Injury severity risk coefficients for the new MATD neck.109
Table J.9 — Comparison of neck injury criteria for a 50th percentile male.115
Table K.1 — Distribution of neck AO/C1/C2 injury severities in the LA/Hannover and USC Fatal Accident
Databases .121

vi © ISO 2005 – All rights reserved

Foreword
ISO (the International Organization for Standardization) is a worldwide federation of national standards bodies (ISO
member bodies). The work of preparing International Standards is normally carried out through ISO technical
committees. Each member body interested in a subject for which a technical committee has been established has
the right to be represented on that committee. International organizations, governmental and non-governmental, in
liaison with ISO, also take part in the work. ISO collaborates closely with the International Electrotechnical
Commission (IEC) on all matters of electrotechnical standardization.
International Standards are drafted in accordance with the rules given in the ISO/IEC Directives, Part 2.
The main task of technical committees is to prepare International Standards. Draft International Standards adopted
by the technical committees are circulated to the member bodies for voting. Publication as an International
Standard requires approval by at least 75 % of the member bodies casting a vote.
ISO 13232-5 was prepared by Technical Committee ISO/TC 22, Road vehicles, Subcommittee SC 22, Motorcycles.
This second edition cancels and replaces the first version (ISO 13232-5:1996), which has been technically revised.
ISO 13232 consists of the following parts, under the general title Motorcycles — Test and analysis procedures for
research evaluation of rider crash protective devices fitted to motorcycles:
⎯ Part 1: Definitions, symbols and general considerations
⎯ Part 2: Definition of impact conditions in relation to accident data
⎯ Part 3: Motorcyclist anthropometric impact dummy
⎯ Part 4: Variables to be measured, instrumentation and measurement procedures
⎯ Part 5: Injury indices and risk/benefit analysis
⎯ Part 6: Full-scale impact-test procedures
⎯ Part 7: Standardized procedures for performing computer simulations of motorcycle impact tests
⎯ Part 8: Documentation and reports
Introduction
ISO 13232 has been prepared on the basis of existing technology. Its purpose is to define common research
methods and a means for making an overall evaluation of the effect that devices which are fitted to motorcycles
and intended for the crash protection of riders, have on injuries, when assessed over a range of impact conditions
which are based on accident data.
It is intended that all of the methods and recommendations contained in ISO 13232 should be used in all basic
feasibility research. However, researchers should also consider variations in the specified conditions (for example,
rider size) when evaluating the overall feasibility of any protective device. In addition, researchers may wish to vary
or extend elements of the methodology in order to research issues which are of particular interest to them. In all
such cases which go beyond the basic research, if reference is to be made to ISO 13232, a clear explanation of
how the used procedures differ from the basic methodology should be provided.
ISO 13232 was prepared by ISO/TC 22/SC 22 at the request of the United Nations Economic Commission for
Europe Group for Road Vehicle General Safety (UN/ECE/TRANS/SCI/WP29/GRSG), based on original working
documents submitted by the International Motorcycle Manufacturers Association (IMMA), and comprising eight
interrelated parts.
This revision of ISO 13232 incorporates extensive technical amendments throughout all the parts, resulting from
extensive experience with the standard and the development of improved research methods.
In order to apply ISO 13232 properly, it is strongly recommended that all eight parts be used together, particularly if
the results are to be published.

viii © ISO 2005 – All rights reserved

INTERNATIONAL STANDARD ISO 13232-5:2005(E)

Motorcycles — Test and analysis procedures for research
evaluation of rider crash protective devices fitted to
motorcycles —
Part 5:
Injury indices and risk/benefit analysis
1 Scope
This part of ISO 13232 provides:
⎯ performance indices which can be correlated with human injuries;
⎯ formulae which relate injury indices to probable injury cost;
⎯ a consistent means of interpreting impact test results;
⎯ a means of relating the results obtained from film analysis and instrumentation of the dummy to injuries
sustained in accidents;
⎯ a means of assessing both the combined and relative effects of multiple injuries;
⎯ an objective means of quantifying injury cost using a single index;
⎯ a means of verifying the analysis; and
⎯ a means of doing risk/benefit analysis of protective devices fitted to motorcycles, based upon the population of
impact conditions identified in ISO 13232-2.
ISO 13232 specifies the minimum requirements for research into the feasibility of protective devices fitted to
motorcycles, which are intended to protect the rider in the event of a collision.
ISO 13232 is applicable to impact tests involving:
⎯ two-wheeled motorcycles;
⎯ the specified type of opposing vehicle;
⎯ either a stationary and a moving vehicle or two moving vehicles;
⎯ for any moving vehicle, a steady speed and straight-line motion immediately prior to impact;
⎯ one helmeted dummy in a normal seating position on an upright motorcycle;
⎯ the measurement of the potential for specified types of injury, by body region;
⎯ evaluation of the results of paired impact tests (i.e. comparisons between motorcycles fitted and not fitted with
the proposed devices).
ISO 13232 does not apply to testing for regulatory or legislative purposes.
2 Normative references
The following referenced documents are indispensable for the application of this document. For dated
references, only the edition cited applies. For undated references, the latest edition of the referenced
document (including any amendments) applies.
ISO 13232-1, Motorcycles — Test and analysis procedures for research evaluation of rider crash protective devices

fitted to motorcycles — Part 1: Definitions, symbols and general considerations
ISO 13232-2, Motorcycles — Test and analysis procedures for research evaluation of rider crash protective devices
fitted to motorcycles — Part 2: Definition of impact conditions in relation to accident data
ISO 13232-4, Motorcycles — Test and analysis procedures for research evaluation of rider crash protective devices
fitted to motorcycles — Part 4: Variables to be measured, instrumentation, and measurement procedures
ISO 13232-7, Motorcycles — Test and analysis procedures for research evaluation of rider crash protective devices
fitted to motorcycles — Part 7: Standardized procedures for performing computer simulations of motorcycle impact
tests
ISO 13232-8, Motorcycles — Test and analysis procedures for research evaluation of rider crash protective devices
fitted to motorcycles — Part 8: Documentation and reports
AIS-90, Association for the Advancement of Automotive Medicine (AAAM), Des Plaines, IL, USA, The abbreviated
injury scale. 1990 revision
SAE J211, Instrumentation for impact tests, Warrendale, Pennsylvania, USA
SAE J885, Human tolerance to impact conditions as related to motor vehicle design, Warrendale, Pennsylvania,
USA
3 Definitions and abbreviations
The following terms are defined in ISO 13232-1. For the purposes of this part of ISO 13232, those definitions apply.
Additional definitions which could apply to this part of ISO 13232 are also listed in ISO 13232-1:
⎯ abbreviated injury scale (AIS);
⎯ abdomen maximum residual penetration (p );
A,max
⎯ ancillary costs (AC);
⎯ cost of fatality (CF);
⎯ entire impact sequence;
⎯ generalized acceleration model for brain injury tolerance (GAMBIT, G);
⎯ head injury criterion (HIC);
⎯ injury assessment function;
2 © ISO 2005 – All rights reserved

⎯ injury assessment variable;
⎯ injury costs (IC);
⎯ injury index;
⎯ injury potential variable;
⎯ injury severity probability (ISP);
⎯ lower extremities (lE);
⎯ maximum PAIS;
⎯ medical costs (MDC);
⎯ normalized injury cost (IC );
norm
⎯ permanent partial incapacity (PPI);
⎯ primary impact period;
⎯ probability of fatality (PF);
⎯ probable AIS (PAIS);
⎯ secondary impact period;
⎯ total PAIS;
⎯ upper (or lower) sternum maximum normalized compression (C or Cl );
us,max,norm s,max,norm
⎯ upper (or lower) sternum maximum velocity-compression (VC or VCl );
us,max s,max
⎯ upper (or lower) sternum velocity (V or V ).
us ls
4 Requirements
4.1 Injury variables
4.1.1 Injury assessment variables
The following injury assessment variables shall be evaluated over the primary impact period and also over the
entire impact sequence using the calculations presented in 5.1 and the measurement methods given in 5.2.1 and
5.2.3.3 of ISO 13232-4:
⎯ head maximum GAMBIT (G );
max
⎯ head injury criterion (HIC);
⎯ head maximum resultant linear acceleration (a );
r,H,max
⎯ neck injury index (NII);
⎯ upper sternum maximum normalized compression (C );
us,max,norm
⎯ lower sternum maximum normalized compression (C );
ls,max,norm
⎯ upper sternum maximum velocity-compression (VC ) for V ≥ 3 m/s;
us,max us
⎯ lower sternum maximum velocity-compression (VC ) for V ≥ 3 m/s;
ls,max ls
⎯ abdomen maximum residual penetration (p ).
A,max
4.1.2 Injury potential variables
The following injury potential variables shall be determined by evaluating them using the methods described in
5.2.4.2 of ISO 13232-4. The variables shall be evaluated over the interval from 0,050 s before first MC/OV contact
until first helmet/OV contact, or until the helmet leaves the field of view, whichever occurs sooner, unless otherwise
stated. In order to calculate velocities, the results shall be differentiated according to 5.1.7 of this part of ISO 13232,
over this same time interval. The specific values listed below shall be identified from the velocity time histories:
⎯ helmet trajectory in initial longitudinal-vertical plane of MC travel (z versus x );
h h
⎯ helmet resultant velocity at first helmet/OV contact (V );
r,h,fc
⎯ helmet longitudinal velocity at first helmet/OV contact (V );
x,h,fc
⎯ helmet lateral velocity at first helmet/OV contact (V );
y,h,fc
⎯ helmet vertical velocity at first helmet/OV contact (V ).
z,h,fc
4.2 Lower extremity injuries
The following lower extremity injuries shall be evaluated, based on observations and measurements of the frangible
components, as described in 5.2.3 of ISO 13232-4:
⎯ non-displaced bone fractures;
⎯ displaced bone fractures;
⎯ knee partial dislocations;
⎯ knee complete dislocations.
4.3 Injury severity probabilities
The following injury severity probabilities (ISP) shall be determined for each severity level, AIS ≥ 1 through the
highest level, using the methods described in 5.3:
closed head ISP ;
H
upper neck combined loading ISP ;
n
upper sternum compression ISP ;
C,us
lower sternum compression ISP ;
C,ls
4 © ISO 2005 – All rights reserved

upper sternum velocity-compression ISP ;
VC,us
lower sternum velocity-compression ISP ;
VC,ls
intra-abdominal penetration ISP .
A
4.4 Injury indices
The probability of each discrete AIS injury severity level shall be calculated for each of the five body regions: the
head, upper neck, thorax, abdomen, and lower extremities, using the procedures described in 5.4.
The medical and ancillary costs associated with injuries to each of the five body regions shall be calculated using
the procedures described in 5.5.1 and 5.5.2, respectively. The cost of fatality shall be determined as defined in
Annex A.
The probability of fatality shall be calculated using the procedures described in 5.6.
The risk of life threatening brain injury shall be calculated from HIC using the procedures described in 5.6.4.
The probable AIS (PAIS) shall be determined by body region, using the procedures described in 5.7.1. The
maximum PAIS and total PAIS shall be determined across all body regions using the procedures described in 5.7.2
and 5.7.3, respectively.
The normalized injury costs of survival and fatality and the total normalized injury cost shall be determined using
the procedures described in 5.8.
NOTE The term "cost" is used in this subclause in a specific and limited sense, and for test comparison purposes only (see
def 3.5.7 of ISO 13232-1 for specific cost definitions). The "costs," as used here, represent average costs based on a simplified
model of samples of bioeconomic data; collected over a particular time period and region; and for a limited range of specific
injury types, severities, and body regions, which are able to be monitored in crash tests, and which can exclude the majority of
the types, severities, and locations of human body injuries, and some types of cost components. In no way do such injury costs
consider, nor are they intended to consider, the market level costs of a proposed protective device. The "costs" described herein
are only intended to provided a convenient, common basis for combining and comparing across body regions and crash tests
and on a relative basis, different types, locations, and severities of injuries. For the foregoing reasons, such costs have limited
applicability and are not intended nor appropriate for calculating, for example, the actual cost of a specific real accident, or the
total societal or economic cost of a given device or design.
4.5 Risk/benefit analysis
Any risk/benefit analysis of a proposed rider crash protective device fitted to a motorcycle, which forms a part of the
overall evaluation described in ISO 13232-2 or which may be used to identify potential failure modes of a proposed
device for purposes of further testing, shall use the methods described in 5.10.
5 Procedures
5.1 Injury variables
Compute the maximum values of the variables over time, for example, G .
max (t)
5.1.1 Resultants
Calculate the head resultant linear and angular accelerations, using the time histories of the linear and angular
accelerations as calculated in 5.2.1 of ISO 13232-4, and shown in the example for the resultant linear acceleration,
given below:
1/ 2
2 2 2
a =()a + a + a
r x y z
where
a is the resultant linear acceleration, in g units;
r
a is the linear acceleration in the x direction, in g units;
x
a is the linear acceleration in the y direction, in g units;
y
a is the linear acceleration in the z direction, in g units.
z
Where only two components are included in a resultant, calculate the resultant of those two components, as shown
in the example for the resultant shear force, given below:
1/ 2
2 2
F =()F + F
xy x y
where
F is the resultant force, in kilonewtons;
xy
F is the force in the x direction, in kilonewtons;
x
F is the force in the y direction, in kilonewtons.
y
5.1.2 GAMBIT
Calculate GAMBIT using the equation given below:
1/ 2
2 2
⎛ ⎞
⎛ a ⎞ ⎛ a ⎞
⎜ r,H r,H ⎟
⎜ ⎟ ⎜ ⎟
G = +
⎜ ⎟ ⎜ ⎟
⎜ ⎟
⎜ 250 25000 ⎟
⎝ ⎠ ⎝ ⎠
⎝ ⎠
where
⎯ G is GAMBIT
⎯ a is the head resultant linear acceleration, in g units;
r,H
⎯ α is the head resultant angular acceleration, in radians per second squared.
r,H
⎯ 250 is the normalization factor for linear acceleration in GAMBIT, in g units;
⎯ 25 000 is the normalization factor for angular acceleration in GAMBIT, in radians per second squared.
⎯ Identify the maximum value of GAMBIT, G
max
5.1.3 HIC
1)
Calculate HIC using the equation given below :

1) SAE J885, July 1986.
6 © ISO 2005 – All rights reserved

2,5
⎛ ⎞
t
⎛ ⎞
⎜ ⎟
⎜ 1 ⎟
⎜ ⎟
HIC = max()t − t a ()t dt
2 1 r,H
⎜ ⎟
∫
⎜ t − t ⎟
⎜ 2 1 ⎟
⎜ t ⎟
⎝ 2 ⎠
⎝ ⎠
where
HIC is the head injury criterion;
a is the head resultant linear acceleration, in g units;
r,H
HIC values are only calculated during periods of head contact as defined by head engagement (t ) and head
e
disengagement (t ) times determined according to ISO Technical Report TR 12351.
d
t and t (in seconds) are all possible initial and final times for each contact interval which are separated by not
1 2
more than 0,015 s, and where t > = τ and t < = t .
1 ε 2 d
An example computer code for the calculation of head contacts is found in Annex I.
5.1.4 Upper and lower sternum compression
Use the upper and lower sternum displacement time histories recorded and reduced as described in 4.4.1.3 and
5.2.1 of ISO 13232-4. Calculate the upper and lower sternum deflections and compressions, as shown in the
example equations for the upper sternum, given below and referring to Figure 1:
2 2
()l + ∆l −(l + ∆l)
uL uL uR uR
D =
y,us
2W
L,R
1/ 2
⎛ ⎞
W
⎛ ⎞
⎜ 2 L,R ⎟
⎜ ⎟
D =()l + ∆l − − D − d
x,us uR uR y,us us
⎜ ⎜ ⎟ ⎟
⎜ ⎟
⎝ ⎠
⎝ ⎠
−D
x,us
C = ×100
us,norm
187,5
where
D is the upper sternum deflection in the y direction, in millimetres;
y,us
l is the cable length of the upper left string pot, in millimetres;
uL
∆l is the change in cable length of the upper left string pot (positive is longer), in millimetres;
uL
l is the cable length of the upper right string pot, in millimetres;
uR
∆l is the change in cable length of the upper right string pot (positive is longer), in millimetres;
uR
W is the lateral distance between the left and right string pots, in millimetres;
L,R
D is the upper sternum deflection in the x direction, in millimetres;
x,us
d is the undeformed perpendicular distance from the plane containing the string pot pivot axes to the upper
us
sternum, at the centre of rib 2 where the strings are attached, in millimetres;
187,5 is the dimensional factor used to normalize compression of the Hybrid III chest, in millimetres;
C is the normalized upper sternum compression for a Hybrid III dummy, expressed as a percentage.
us,norm
Identify the maximum normalized upper and lower sternum compressions, C and Cl , respectively.
us,max s,max
If at any time D or D exceeds 75 mm, document this result in accordance with ISO 13232-8.
x,us x,ls
Figure 1 — Chest potentiometer geometry shown for the upper sternum

5.1.5 Upper and lower sternum velocity
Calculate the upper and lower sternum compression velocities by differentiating the upper and lower sternum
deflections, respectively, using the trapezoidal rule, as shown below for the upper sternum. Filter the velocities
using the SAE J211 Class 60 and convert the velocities to metres per second.
⎛ ⎞
⎜ ⎟
⎜ d ⎟
D
x,us
⎜ ⎟
⎝ dt ⎠
V =
us
1 000
8 © ISO 2005 – All rights reserved

where
V is the upper sternum velocity, in metres per second;
us
D is the upper sternum deflection in the x direction, in millimetres;
x,us
t is the time, in seconds;
1 000 is the conversion factor from millimetres to metres.
5.1.6 Upper and lower sternum velocity-compression
Calculate the upper and lower sternum velocity-compressions, as shown in the example equation for the upper
sternum, given below:
1,3 × V D
us x,us
VC =
us
where
VC is the upper sternum velocity-compression, in metres per second;
us
V is the upper sternum velocity, in metres per second;
us
D is the upper sternum deflection in the x direction, in millimetres;
x,us
1,3 is the factor to correct internally measured upper (or lower) sternum variables to external application;
229 is the dimensional factor used to normalize upper (or lower) sternum deflection for the VC calculation, in
millimetres.
Identify the maximum upper and lower sternum velocity-compressions, VC and VC for V and V ≥ 3 m/s,
us,max ls,max us ls
respectively, considering only cases where both V and D have negative values.
x
5.1.7 Helmet centroid point component velocities
Plot the helmet centroid point trajectory as described in 4.1.2. Evaluate V , V , and V relative to the
x,h,fc y,h,fc z,h,fc
inertial axis system and using the procedures described in Annex A of ISO 13232-4.
Calculate the helmet centroid point component velocities in the x, y, and z directions from the high speed film data,
as shown in the example for the x direction helmet centroid point velocity, given below:
x − x
h, j+1 h, j−1
V =
x,h,i
1000()t − t
i+1 i−1
where
V is the helmet centroid point velocity in the x direction at analysis frame i, in metres per second;
x,h,i
x is the position of the helmet centroid point in the x direction at analysis frame i+1, in millimetres;
h,i+1
t is the time of analysis frame i+1, in seconds;
i+1
1 000 is the conversion factor from millimetres to metres.
5.1.8 Neck injury index (NII)
Calculate NII using the equation given below:
1/ 2
⎛ ⎞
⎛ ⎞
⎜ 1/ 2 ⎟
⎛ ⎞
⎜ 2 2 2 ⎟
⎛ ⎞
⎜ ⎟
⎜ ⎟
⎛ ⎞ ⎛ ⎞ ⎛ ⎞ ⎛ ⎞
() ⎜ ⎟ ()
⎜ F t F ()t M ()t M ()t M ()t M ()t ⎟ F t F ()t
C T X E F Z C T
⎜ ⎟
⎜ ⎟ ⎜ ⎟ ⎜ ⎟
⎜ ⎜ ⎟ ⎟
NII()t = max + + + + + , 3,1 +
⎜ ⎟
⎜ ⎟
∗ ∗ ∗ ∗ ∗ ∗ ∗ ∗
⎜ ⎟ ⎜ ⎟ ⎜ ⎟ ⎜ ⎟
⎜ ⎟
⎜ ⎟
F F ⎜ M M M ⎟ M F F
C T ⎝ X ⎠ ⎝ E F ⎠ ⎝ Z ⎠ ⎝ C T ⎠
⎜ ⎟
⎜ ⎟
⎝ ⎠
⎜⎜ ⎟ ⎟
⎝ ⎠
⎜ ⎟
⎝ ⎠
⎝ ⎠
where
F (t) is the neck axial compression force (the minimum of F or 0 (never a positive number));
c z
∗ ∗
F is the normalization factor for compression ( F = -6,53 kN);
C C
F (t) is the neck tension force (the maximum of F or 0 (never a negative number));
T z
∗ ∗
F is the normalization factor for tension ( F = 3,34 kN);
T T
M (t) is the neck lateral flexion moment at the occipital condyle;
x
∗ ∗
M is the normalization factor for occipital condyle lateral flexion ( M = 62,66 Nm);
X X
M (t) is the neck extension moment at the occipital condyle (the minimum of M or 0 (never a positive
E y
number));
∗ ∗
M is the normalization factor for occipital condyle extension bending ( M = -58,0 Nm);
E E
M (t) is the neck flexion moment at the occipital condyle (the maximum of M or 0 (never a negative number));
F y
∗ ∗
M is the normalization factor for occipital condyle flexion ( M = 204,2 Nm);
F F
M (t) is the neck torsion moment;
z
∗ ∗
M is the normalization factor for torsion ( M = 47,1 Nm).
Z Z
Identify by means of time series analysis NII the maximum value of NII.
max
Note - Assumptions and limitations for predicting neck injuries are given in subclause O.3.1.5 and Annex J.
5.2 Frangible component damage
Record the number of displaced and non-displaced fractures for each femur and tibia frangible bone. Record partial
or complete dislocation or no injury for each knee. Record p . Use the evaluation methods described in 5.2.3 of
A,max
ISO 13232-4.
5.3 Injury severity probabilities
Insert the injury variable values into the following relationships to determine the injury severity probability (ISP) for
each AIS injury severity level, for each body region.
10 © ISO 2005 – All rights reserved

5.3.1 Head
Calculate the closed head GAMBIT ISP and the closed head HIC ISP as a function of G and HIC
Gmax,H HIC,H max
respectively, for each AIS > j injury severity level, using the injury assessment functions given in Tables 1a and 1b
respectively. If any of the head injury assessment values are less than the minimum required value for the injury
severity level, then the corresponding ISP value is 0.
The closed head ISP, ISP , for each AIS injury severity level, j, is defined as the larger of either ISP or
H Gmax,H,j
ISP .
HIC,H,j
5.3.2 Chest
For each AIS > j injury severity level, calculate the upper and lower thoracic compression ISPC,us and ISP as a
C,ls
function of C and C , respectively, and the upper and lower thoracic velocity-compression ISP and
us,max ls,max VC,us
ISP , as a function of VC and VC , respectively, using the injury assessment functions given Tables 2
VC,ls us,max ls,max
and 3, respectively. If any of the chest injury assessment values are less than the minimum required value for the
injury severity level, then the corresponding ISP value is 0.
The thoracic compression ISP for each AIS injury severity level, j, is defined as the larger of either ISP or
C C,us,j
ISP . The thoracic velocity-compression ISP for each severity level, j, is defined as the larger of either ISP
C,ls,j VC
VC,us,j
or ISP . The overall thoracic ISP, ISP , for each AIS injury severity level, j, is defined as the larger of either
VC,ls,j Th
ISP or ISP .
C,j VC,j
5.3.3 Abdomen
Calculate the intra-abdominal penetration ISP as a function of p for each AIS > j injury severity level using the
A A,max
injury assessment functions given in Table 4.
NOTE The researcher may choose to calculate ISP , the injury indices, and the injury costs by:
A
⎯ replacing the measured value of p with a zero;
A,max
⎯ calculating the injury indices and injury costs as described in this part of ISO 13232;
⎯ reporting both sets of values and the measured value of p in the documentation;
A,max
⎯ noting this deviation in the documentation.
Table 1a — Closed head injury severity probability as a function of G
max
Severity level Minimu
...