Changelog#

AMMR 4.0 beta#

Warning

The default pelvis model used in all models have changed. The pelvis morphology now comes from trunk pelivs. The toplogy remain unchanged as the leg model pelvis is morphed to match the Trunk. See below how to control this behaviour.

Fixed:

Fixed the inclusion of the buckle segmental masses in the calculation of the TotalBodyMass variable.
Fixed the cervical spine axial rotation rhythm coefficients. The distribution between C2C1 and the rest of cervical spine was incorrect.

Added:

A new detailed thoracic model was addded. This model consists of the thoracic vertebral column and the ribcage, including individual ribs and a two part sternum. The many segments interconnected by joints replicates the physiological connection and load transfer mechanisms.

The detailed thoracic model can be enabled with the switch BM_TRUNK_THORACIC_MODEL:
```
#define BM_TRUNK_THORACIC_MODEL _THORACIC_MODEL_FLEXIBLE_
```
Note

The detailed thoracic model is not enabled by default. It adds many more segments to the body model so only use this new model if you need the added complexity.

The model is based on the work of Ignasiak, D (2016) and Shayestehpour (2023). See the documentaiton page for more info.
A new abdmoninal model was added to replace the old ‘buckle’ model. I uses a new kinematic volume measure from AnyBody 7.5 to model the abdominal pressure and includes new oblique, rectus and tranversus muscles. The new abdominal model is more robust and allows a bigger range of motion of the trunk. See the documentaiton page for the thoracic model for more info.

It is possible to revert ot the old buckle implmenation with switch _CAVITY_MODEL_BUCKLE_.
A new system for handling mass and inertia calculation for segments in the Trunk. Now we utilize the new inertia classes derived from AnyInertia. The new Abdominal and Thoracic model uses geometry based inertia. The old models keep the standard mass and inertia properties. The system also controls how mass is scaled when setting Main.HumanModel.Anthropometrics.BodyMass. It will distribute the mass to the different segments based on whether they are marked as being part of the distribution.
The cervical model now has linear stiffness coefficients. These can be enabled with the switch BM_TRUNK_CERVICAL_DISC_STIFFNESS:
```
#define BM_TRUNK_CERVICAL_DISC_STIFFNESS _DISC_STIFFNESS_LINEAR_
```
Only linear stiffness function is available for cervical discs currently.

Changed:

The default pelvis morphology is now the one from the trunk model, as oposed to the pelvis belonging to whatever leg model has been selected. This was done to get a consistent trunk model and considering all the recent improvements to the trunk. This option can be controlled with:
```
#define BM_LEG_TRUNK_INTERFACE _MORPH_LEG_TO_TRUNK_
```
In practice, this means that the morphology of the leg pelvis is moprhed to match the Trunk pelvis. Using _MORPH_TRUNK_TO_LEG_ instead will revert to the old behaviour.

AMMR 3.1.0 (2024-??-??)#

➕ Added:#

Introduced a new class template, CreateCoMRefNode, for generating a reference node at the center of mass of a segment, aligned with its principal axes of inertia.
Added the TRI(N) macro to create a lower triangular (NxN) matrix.
Added the TOTAL_POLYLINE_LENGTH(P) macro to compute the total length of a polyline defined by a set of points.

🩹 Fixed:#

Resolved an issue that prevented disabling the drawing of marker arrows in CreateMarkerDriverClass within MoCap models. The search string in Main.ModelSetup.Views.All_MarkerArrows.Objects has been updated to correctly identify the arrow drawing objects.
Corrected the PelvisGround rotation drivers in the Free Posture Static example. The X and Z rotation drivers were previously mixed up and are now properly assigned.
Fixed a spelling typo in the disc stiffness BM control statements. The BM_TRUNK_*_DISC_STIFNESS parameters have been renamed to BM_TRUNK_*_DISC_STIFFNESS. The mispelled parameter names have been deprecated.

🔧 Changed:#

Updated the insertion and origin points of the Gluteus Medius to ensure correct moment arms for external rotation in specific postures. The posterior Gluteus Medius now twists inside the anterior part and attaches more anteriorly on the femoral trochanter.
Modified the Human-Ground residual implementation in MoCap models to use rotational measures configured for angular velocities. This change enhances the robustness of the residuals and makes the residual output easier to interpret geometrically, without affecting the results.
Excluded force plates from the parameter identification study, as they were unnecessary. This change may slightly speed up the parameter identification process.
The wrapping surface for muscles at the wrist has been changed to an ellipsoid from a cylinder. This lowers the risk of muscle via points prenetrating the wrapping surface in postures involving both flexion/extension and abduction/adduction at the wrist.

AMMR 3.0.4 (2024-07-02)#

🩹 Fixed:#

Fixed an issue in the Bike Model example that included thoracic support in the full body model also.
Fixed an issue with the visualization of the marker coordinate system arrows. They now correctly update while running running parameter identification in the MoCap models.

AMMR 3.0.3 (2024-06-10)#

🩹 Fixed:#

Fixed a penetration warning for the pectoralis muscles when the thoracic segments are scaled very non-uniformly. The fix involves a small (5 deg) adjustment to the orientation of the pectoralis wrapping surface.
Fixed default limits in Range of Motion limits class template. The default limits for PelvisThoraxExtension, PelvisThoraxLateralBending, Right/LeftWristFlexion had the upper and lower limits flipped. This is now fixed and a check is added in the class template to catch this kind of error.
Fixed an issue where blinking Windows would appear when loading models stored in git repositories. This issue was caused by a python subprocess that queried the git repository for branch information.
Updated the foot marker position in the Xsens protocol to accommodate the changes made to the foot anatomical frame in the TLEM 2.2 leg model. The R/LTOE and R/LTOE2 markers have been moved upwards by 1.5 cm.

AMMR 3.0.1 (2024-02-13)#

This minor release of AMMR contains no updates to the models compared to the major AMMR 3.0.0 released the previous month. It only has a few minor changes to the documentation and new tolerances in the FDK models.

🔧 Changed:#

Finer FDK tolerances for the Knee Simulator example, to take avantage of the improved robustness of the AnyBody FDK solver in version 8.0.1.

AMMR 3.0 (2024-02-13)#

✨ Highlights#

Integrated pelvis, lumbar, and thorax models into a consistent trunk model in preparation for a full thoracic model in AMMR 4.
Updated the leg model (TLEM 2.2) with improvements to the ankle complex, shank orientation, and alignment of the patella tendon.
Added new wrapping surfaces to the Achilles tendon around the ankle in the TLEM 2.2 leg model.
Made numerous improvements and fixes to the Body models, MoCap models, and application examples.

Warning

Care must be taken when porting existing MoCap models to the new AMMR. Changes to the pelvic tilt, and changes to the foot anatomical frame can cause MoCap markers on Pelvis and feet to have moved slightly.

If migrating models from AMMR 2.4, be sure to check markers on pelvis and the foot segments. The Y component may need to be adjusted to achieve same marker position and joint angle output.

🩹 Fixed:#

Fixed a couple of bugs in the Seated Human model:
- Reactions for subtalar joint driver are switched off.
- GHDriverLeft was using velocity value from GHExternalRotation instead of GHAbduction. This is now fixed.
The Main.ModelSetup.CreateVideo operation was missing in some of the MoCap examples. This has been fixed. If you have this problem update the CreateVideo.any file in your application.
Fixed a wrapping problem with the posterior deltoid muscle in the 2-parameter shoulder calibration.
Fixed a bug in the LegPressMachine example that caused the model view to zoom to infinity.
Improved the robustness of muscle recruitment for abdominal muscles (buckle support) by increasing the strength of recruited reactions on buckle segment balance.
Updated scaling functions (Scale) for segments in trunk model (lumbar, thoracic and cervical) to account for pelvis segment morphing into leg pelvis coordinate system using BM_LEG_TRUNK_INTERFACE setting.
Fixed a bug in the AnatomicalFrame of TLEM 2.2 foot and talus that caused the ARel to be constructed from unscaled landmarks.
Fixed small inaccuracy in the mass scaling of the shank. It did not account for the mass of the patella segment which uses the same scaling coefficient as the shank.
Visualizaiton of muscles in AMMR now use the builtin .viewMuscle drawing objects in the muscle class. Hence, all manually created AnyDrawMuscle objects, usually named DrwMus have been removed.
The kinematic start guess for left patalla joint has been adjusted to improve robustness of the kinematic solver. This does not changed the result of models.

➕ Added:#

Added two small helper code macros: NON_UNIQUE_VALUES()/NON_UNIQUE_POINTERS() for finding duplicate (non-unique) entries in arrays of values and pointers.
Added new set of hip joint measures (Interface.Right.HipISB) that strictly follow the International Society of Biomechanics’ (ISB) definitions. These measures are similar to existing angles but do not have zero hip-flexion in neutral position due to different definition of pelvis coordinate system with respect to a plane defined by ASIS-PSIS points.
Segments in trunk model (lumbar, thoracic and cervical) now explicitly define a ScalingNode node indicating coordinate system for segment scaling.
When using the _THORACIC_MODEL_FLEXIBLE_ The sternum mass is now distributed over the the sternum segments.
Add an option to override the default kinematic joint limits in the MoCap framework

🔧 Changed:#

The trunk joint reaction force in SelectedOutputs is now expressed in new reference nodes that are aligned with the vertebral body. Therefore, the names of the outputs now include CompressionForce and ShearForce. The new reference nodes are created inside the joint node on the proximal segment. The implementation from AMMR 2.4 can be enabled by using the compatibility switch: #define BM_COMPATIBILITY_24_TRUNK_SELECTED_OUTPUTS_JRF ON
Adjustments to pelvic tilt have changed the position of MoCap markers on the pelvis segment. This mostly affects markers with hardcoded positions. Particularly PSIS markers furthest posterior from the origin between ASIS. When migrating from AMMR 2.4 models without adjusting marker positions, PSIS markers may move 2 cm lower.
- Most non-MoCap model examples have been updated to account for the new pelvic tilt value. Either by using the AnatomicalFrameTrunk reference frame in the pelvic driver or by adjusting the Pelvis-Thorax Extension slightly.
The Twente Lower Extremity Model (TLEM) 2 leg model has several updates and is now designated as TLEM 2.2.
- The ankle complex and the knee joint axis have been redefined to compensate for the non-neutral position in which the cadaver was scanned. This improves the alignment of the tibia, talus, and calcaneus bones. The updated knee joint ensures that the patella tendon is straight in the neutral position. The net effect is rotation of the tibia about its long axis with the feet still pointing in the same direction in the neutral position.
- Wrapping surfaces have been added to the Achilles tendon around the ankle in the TLEM 2.2 leg model, giving a more even ratio of moment arms between the soleus and gastrocnemius muscles. Hence, gastrocnemius is recruited less, especially during downhill walking and stair descent, solving the tendency of the model to over-predict the knee contact forces at toe off. This is the first of a number of improvements to the leg model by Dr. Enrico De Pieri, who is working on a publication on improvements and validation of the TLEM 2 leg model.
- The foot and talus models in TLEM 2.2 leg model have several updates in preparation for the release of advanced multi-segment foot models in the future:
  - The coordinate system of the talus is updated to be coincident with the foot coordinate system. A new reference node, TalusCompatibilityFrameAMMR24, is created in the talus segment to be consistent with the previous coordinate system for backwards compatibility.
  - Subtalar and ankle joint parameters for the talus have been updated to be expressed in the new coordinate system. The implementation of the joints is still consistent with the previous implementation.
  - The anatomical frames of the foot and talus are updated and defined using bony landmarks on the foot. This updates the neutral position of the foot and talus. This will also update the ankle plantarflexion and subtalar joint angles.
  - The malleoli coordinates in the foot coordinate system have been fixed to match the malleoli on the shank in the neutral position.
  - The model tree has been updated. The talus segment is moved inside the foot segment. For backwards compatibility, a pointer to the talus segment still exists outside the foot segment.
- The implementation of the TLEM model has been split into two separate folders, LegTLEM/ and LegTLEM1/. All references to TLEM 1 code have been removed in the code implementing the TLEM 2 model.
- The TLEM 1 model now triggers a deprecation warning suggesting using TLEM 2.
The InverseDynamics analysis in MoCap models now uses the first step of Marker tracking as a start guess (initial conditions)
for the kinematic solver. This improves robustness in certain cases.
The marker protocol in the “ADL gait (MoCap model)” was updated/tweaked to improve the robustness of the model. Some special exceptions were added to trials where we discovered that some markers were swapped by accident in the original open access dataset.
Scaling laws defined by the BM_SCALING setting have been updated to calculate offsets between different scaling regions and apply them at load time. Scaling remains the same, but users can now create scaling functions that account for offsets between regions with different scaling.
Glenoid reaction forces are now expressed in the coordinate system of the glenoid cup instead of the general scapula coordinate system. Variables GlenoHumeral_DistractionForce, GlenoHumeral_InferoSuperiorForce, GlenoHumeral_AnteroPosteriorForce represent three directions given by the glenoid cup. Variables may differ slightly even if the force remains the same.
Resolved inconsistencies in arm muscle parameters. The same underlying parameters are now used for both simple and 3-element muscle models.
MoCap: The marker driver class template now adds a “*_Marker” postfix to the reference nodes in creates on the models. This prevents name conflicts when adding a markers with the same name as a reference frame/node already in the model.
A new AnatomicalFrameTrunk reference frame has been added to the pelvis segment. The frame is consistent with the anatomical frames in the rest of the trunk model. Also, all joint angles in relative to the pelvis segment now uses this frame. This implies that the neutral position of the model is identical to the neutral position of the trunk dataset.
MoCap marker protocols: Users must now explicitly specify a coordinate system relative to which markers are placed on the segment using the PlaceMarkerAt argument in the class template. Previously, this defaulted to the AnatomicalFrame of the segment.
The organization of segmental scaling functions was reworked and now configured slightly simpler. This modification is expected not to affect users working with default and non-default scaling laws and patient-specific morphing. Additionally, all spinal segments share a scaling reference frame.
We updated how the class AnySurfCylinderFit is used in the Knee Simulator example. The deprecated way of using the AnySurfCylinderFit has been changed. Since AnySurfCylinderFit is now a subclass of AnyRefNode, it should no longer be nested inside another parent reference frame to provide the pos sRel and orientation ARel. This fixes a number of deprecated warnings that would have triggered with AnyBody version 8.
Added the new AnatomicalFrameTrunk reference frame to the pelvis segment consistent with anatomical frames in the rest of the trunk model. All joint angles relative to the pelvis segment now use this frame. This aligns the neutral position of the model with the neutral position of the trunk dataset and results in more pelvic tilt in the neutral position, better reflecting reported values in literature. Existing PelvisSeg.AnatomicalFrame defined by the ASIS and pubic bony landmarks remains unchanged.
Updated trend validation in “Wilke Spine Pressure validation models” to reflect changes to the thoracic model and the pelvis frame. Although absolute pressures in the spine have changed, trends (relative changes in spine pressure between models) remain the same.
Reduced discretization (number of elements) of the pectoralis major and semispinalis muscles for consistency with textbook anatomy. Pectoralis no longer has its origin on rib 2, and semispinalis no longer inserts on the lumbar region.
Refactored the implementation of muscle parameters in the arm model. All parameters are now given as muscle volume, optimal fiber length, and tendon slack length. Physiological cross-sectional area (PCSA), previously a hardcoded parameter, is now an intermediate value used for calculating muscle strength from muscle volume and optimal fiber length.

This new structure allows for overwriting the complete set of muscle volumes with an alternative dataset.
The MarkerName argument in the CreateMarkerDriver template for MoCap models is no longer necessary. The argument can still be used if the marker class and data entry in the C3D file differ.
Updated the implementation of muscle parameters section in models to use the new ??= (optional assignment) operator introduced in AnyBody 7.4.1. This allows for direct overriding/redefinition of muscle parameters and volumes.

For example, muscle volumes can be overridden with new data.
```
Main.HumanModel.BodyModel.Right.Leg.ModelParameters.Muscles = {
   SoleusMedialis.MuscleVolume = 540; //ml
   SoleusLateralis.MuscleVolume = 450; //ml
};
```
Updated methods for distributing muscle volume among discretized muscle elements. This allows for different optimal fiber lengths among elements of a muscle. If one element has a smaller optimal fiber length (e.g., through calibration), the volume of muscle elements is redistributed, and PCSA remains constant across elements.

If the optimal fiber length of different elements is the same, this method yields the same result as before.
Renamed the folders holding muscle models from MusPar to MuscleModels for better clarity.
The CameraClassTemplate.any include file in model utilities has been renamed to VideoLookAtCamera.any to have the same name as the class template it contains.

🧹 Removed:#

The template DEFAULT_PARAMETER_FOLDER has been removed. It is no longer needed since the same functionality is now provided by the ??= operator.
The three scaling laws _SCALING_UNIFORM_EXTMEASUREMENTS_, _SCALING_LENGTHMASS_EXTMEASUREMENTS_, _SCALING_LENGTHMASSFAT_EXTMEASUREMENTS_ have been deprecated. They are superseeded by the “Statistical Scaling Plugin” which cover the same functionality. The AMMR guide on scaling have been updated to reflect this change.

AMMR 2.4.4 (2023-04-03)#

This version of AMMR adds a number fixes and tweaks to the body models which improves robustness of various kinematic and recruitment solvers.

Added:

Added kinematic joint angle limits in MoCap models for elbow and wrist joints to prevent the kinematic solver from finding postures that are physiologically impossible, such as bending the elbow backwards. These limits are active where marker tracking solver would occasionally find a local minima with unphysiological posture.
Tables with body model configuration parameter in the AMMR documentation now contain links showing their options. For example, see the page on Leg model parameter.

Fixed:

Fixed an issue with wrist joint segment’s load time position (start guess). This greatly improves kinematic robustness of all models with arms as it creates a ‘universal-joint’ mechanism for wrist movement.
Further fixes made to pectoralis wrapping segment’s robustness by optimizing initial load time positions to ensure model kinematics can more easily solve.
Fixed missing LoadParameters operation in LoadAndReplay operation in MoCap examples.
Fixed a problem with oblique muscles introduced in AMMR 2.4. A weak residual force was added to Y rotation of buckle to eliminate this problem.
Corrected wrong order of nonlinear intervertebral disc stiffness polynomial coefficients (affects only those who used polynomial disc stiffness).
Corrected small asymmetry in function for nonlinear intervertebral disc stiffness in coronal plane (affects only those who used polynomial disc stiffness).

AMMR 2.4.3 (2023-01-27)#

Added:

Added a few utility helper class templates
- Template_OperationSaveValues
- Template_OperationLoadValues
- Template_OperationUpdateValues
to make it easier to do common class operations without manually having to create the operations with macros.

To create an operation which loads a file, do:
```
Template_OperationLoadValues LoadAnySetFile = {
   FileName= "MyFile.anyset";
};
```
A more helpful error message is now printed when MoCap markers in the marker protocol are missing the C3D file.

Changed:

The load-time position of the box in the BVH_BoxLift model is now calculated using the position of the hands. Also, Main.ModelSetup.EnvironmentParameters.GravityDirection defined in the box.any file is now calculated automatically from Main.ModelSetup.LabSpecificData.Gravity defined in the LabSpecificData.any file. These changes should make the model more robust when dealing with different BVH files.
It is no longer necessasry to supply the MarkerName argument in the CreateMarkerDriver template MoCap models. The argument can still be used if the marker name and the data entry in the c3d file are different.
The references to muscle models in the joint muscles of the detailed hand have been renamed to avoid future naming conflicts.
The “via-points” for the Psoas Major muscle have been adjusted to ensure that the muscles can better act the role of stabilizing muscle for the lumbar spine.

Fixed:

The Main.ModelSetup.CreateVideo operation was missing in some of the MoCap examples. This has been fixed. If you have this problem please update the CreateVideo.any file in your application.
Fixed a wrapping problem with the posterior deltoid muscle in the two-parameter shoulder calibration.
Fixed a bug in the LegPressMachine example that caused the model view to zoom to infinity.
The robustness of muscle recruitment with the abdominal muscles (buckle support) was futher tweaked by increasing the the strength of the recruited reactions on the balance of the buckle segment.

AMMR 2.4.2 (2022-07-08)#

AMMR version 2.4.2 contains only a few minor changes and fixes compared to version 2.4.1.

Changed:

Changed defintion (sign) of the SkullThoraxRotation and SkullThoraxLateralbending variable in the interface folder. They are now consistent with similar difinitions in the rest of the spine.
The location of the foot drawing generated by the OptimizeBVH_Origin class template for visualization of the target location and orientation of “LFOOT” and “RFOOT” has been updated to better match the expected actual foot location.

Fixed:

Fixed the Evaluate moments arms example where a few branches of the latisimus dorsi, pectoralis major and trapezius muscles were not included.
Fixed a problem that caused the OptimizeBVH_Origin class template to fail to load if the same human segment was used more than one time in the same model.

AMMR 2.4.1 (2022-05-30)#

New example models:

Added a model using a new class template to optimize the origin of BVH model. This model shows how to optimize the origin of the BVH model such that a target segment of the human model (Left/Right Foot/Hand) hits a known position and orientation in a given time interval while following the recorded motion from the trial. <See more>

Fixed:

Fixed a small syntax error which caused the BVH example S1/S01_Trial02/ to fail loading.
Fixed a problem with the “interface” morphing between the TLEM2 pelvis and Trunk Pelvis at the tip of the scarum bone. This bug was visible when using #define BM_LEG_TRUNK_INTERFACE _MORPH_LEG_TO_TRUNK_, (i.e. when using the trunk pelvis morphology with the TLEM2 model), which is not the default.
Fixed missing calibration for the new latissimus dorsi elements introduced in AMMR 2.4. This fix also ensures that all latissimus dorsi elements are calibrated in the same arm posture.

Changed:

The anyscript implemenatation of the acromio-clavicuala, sterno-clavicular, gleno-humeral, and elbow joints have been refactored. They now use explicit AnyScript joint classes (e.g. AnySphericalJoint) instead of implementing the joints directly with measures and constraints. This simplifies the implementation, but also changes the structure of the model tree. However, it has no influence the kinematics of the model, which remains identical.

The new names of the explicit joint objects in ShoulderArm.Jnt are:
- SternoClavicularJoint (-3 DOF)
- AcromioClavicularJoint (-3 DOF)
- GlenoHumeralJoint (-3 DOF)
- HumeroUlnarJoint (-5 DOF)
- HumeroRadialJoint (-1 DOF)
- ProximalRadioUlnarJoint (-2 DOF)
- DistalRadioUlnarJoint (-2 DOF)

The HumeroUlnarJoint is the elbow flexion extension, and together HumeroRadialJoint, ProximalRadioUlnarJoint and DistalRadioUlnarJoint adds 5 constraints leaving the forearm rotation degree of freedom.

Added:

A few previously renamed nodes in pelvis were added back to improve backwards compatibility when loading old seating models.

Changed:

The trunk segment folders was combined to one Segments folder. This might require updating references to the trunk segments in user defined models.

Added:

The complete set of trunk segments was added to the trunk segment folder regardless of rigid or flexible trunk configuration. This ensures that all segments are present in the trunk segment folder. no matter what the configuration is.

AMMR 2.4 (2022-04-28)#

New example models:

Added a new trunk exoskeleton concept model for simulating assistance at the trunk in a box lifting task. This simple example shows how to apply assistive torque directly to the human model. <See more>
Added a new exoskeleton concept model for simulation-driven conceptual design of exoskeletons. The model was developed by Prof. John Rasmussen from Aalborg University. Please see the web cast for more details. <See more>
Added a new femoral torsion tool to apply femoral torsion to the TLEM2.0 leg model. This model tool was developed by Dr. Enrico De Pieri from University of Basel Children’s Hospital (UKBB). Please see the documentation or the web cast by Enrico on his work and publication on femoral torsion. <See more>
Added a new knee force model example. The model shows how to calculate a simple estimate of the medial and lateral knee force. <See more>
A new box lifting motion capture model has been added. The model is based on data from an inertial measurement unit based suit (Xsens), and illustrates how to connect MoCap models with objects in the environment. <See more>

New features:

Many AnyScript example models now include an option to automatically create a video from the model. To use this functionality find and run the new VideoTool.CreateVideo operation under the Study folder. This will automatically run the example model, output still frames, and combine them into a video afterwards. The script can easily be adapted and moved to other examples.
Two new utility macros, which make it easier to create 3D grid arrays, have been added to the model repository. MESHTRIPLES(xarr, yarr, zarr) and MESHGRID(xarr,yarr,zarr). i.e. for creating arrays of all points in a 3D grid array. More information in the file: Body ‣ AAUHuman ‣ BodyModels ‣ GenericBodyModel ‣ Helper.ClassTemplates.any
Added a warning when the glenohumeral flexion/abduction in the mannequin values can cause problems as start guess for the kinematic solver. A small automatic pertubation of the Humerus orientation (Axes0) is also added in these cases so the shoulder rhythm will work as expected.
There is a new option to override more settings in the DefaultMannequinDrivers section. Now the driver type (CType=Hard/Soft), can be overridden directly by the users.
Fixed a lack of robustness with muscle recruitment of the abdominal muscles (buckle support). Muscle recruitment could previously fail with high lumbar flexion. A small support “artificial muscle” has beeen added to the buckle segment, preventing muscle recruitment from failing.

Fixed:

Improved the selected output by adding the m. Semimembranosus and m. Semitendinosus contributions to the knee flexor group for both muscle activity (KneeFlexorMuscleActivity) and muscle force (KneeFlexorMuscleForce).
Updated and improved origin of the hamstring muscles. The muscles biceps femoris, semitendinosus and semimembranosus have been updated to improve their moment arms in certain lunge movements. The origin points at pelvis has been moved down a bit to ensure the muscles wraps correctly in lunge movements, while maintaining the same moment arm in gait etc.
Fixed a bug in scaling where the mass of the trunk model pelvis was used in some cases instead of the pelvis mass from the leg model. This could cause a slightly incorrect mass to be used for the pelvis segment.
Fixed wrong sign for the WristJoint flexion variable. The values users provided in the mannequin section was incorrectly interpreted as wrist extension.
Fixed a problem where custom scaling and _SCALING_XYZ_ would prevent the model from loading.
Fixed some logical issues with the ContactSurfaceDistanceAndVelocityDepLinPush.any file.
- Fix length calculation and drawing of the normal force
- Fixed an extrapolation error when changing the internal setting _SMOOTHING_FUNCTION_PROFILE_ to FUNC_PROFILE_BSPLINE. We now cap the height ratio to only be in the interpolation area. Values outside this area infer that no contact is present.
Refactored the way Trunk nodes are mirrored between left and right. This is more consistent with the remaining body parts and handled in the cadaver data files.
Fixed a problem in MoCap models where calibration studies were not run automatically in models that only had 3-element muscles on the upper body.
The example to evaluate moments arms now works when the shoulder rhythm is enabled.

Changed:

Improve the trunk model’s strength for trunk external rotation. This change improves the implementation of the internal/external obliques and latissimus dorsi muscles. More branches are added to the internal obliques and the geometry is updated to better match anatomical text books. Likewise, the latissimus dorsi muscles is discretized into more branches so it has branches inserting on every vertebra.
The clavicle entry in the Anthropometric.SegmentMasses folder have been renamed to shoulder. This makes it consistent with the rest of varaibles in the folder, and correctly reflect that the mass is assigned to both the scapula and clavicle segment.
The OptimalFiberLength and TotalTendonLength in the TLEM leg models are no longer ‘DesignVar’ when the parameters are also calibrated. This prevents the huge amount of warnings when calibrating the leg muscles.
The L5LContactNode,L4LContactNode,L3LContactNode, L4LContactNode,L1LContactNode nodes were scaled using the Right node Z-axis. This is now changed to use the Left node Z-axis.
The trunk model has been restructured in preparation for a full Thoracic model. This means that all the vertebra and ribs have been created in the model structure, but only as AnyFolder& references to the single rigid thorax segment.

Note

A number of nodes have been renamed in the process. If you have problems loading old model due to missing nodes, please consult the new model examples to find the new names.
Updated the neutral scapula position and scapula sliding. The default neutral scapula position (medial rotation) has been updated to a more realistic position. Additionally, the node at scapula TS point, on which the scapula slides, has been moved to provide a more realistic clearance between the scapula and the ellipsoid sliding surface representing thorax.
Thanks to Johanna Menze (@menzejo) from the University of Bern for updating the model.
Renamed a few variables named r which could collide with built-in r variable.

Removed:

The previously deprecated BM keyword _LEG_MODEL_Leg_ has been completely removed.
The special mannequin driver switches for the old leg model (BM_MANNEQUIN_DRIVER_ANKLE_EVERSION_RIGHT/LEFT) have been deprecated. Instead the switch used for the TLEM1/2 leg models (BM_MANNEQUIN_DRIVER_ANKLE_SUBTALAR_EVERSION_RIGHT) can now be used for all leg models.
Renamed all deprecated ligament class names. AnyViaPointLigament-> AnyLigamentViaPoint.

AMMR 2.3.4 (2021-07-05)#

Fixed:

Improved the intial guess for Latissimus dorsi wrapping, so the wrapping solutions becomes more robust to extreeme starting postions.
Fix a problem with <ANYBODY_PATH_MODELUTILS>/Reactions support files preventing models from loading correctly. Thanks to prof. Michael Skipper Andersen (Aalborg University) for finding this bug.

Added:

Add small helper class template DriverBasedOnLoadPos which makes it easy to add constraints between two segments based on their load time positions.
Refactor the way pelvis rotations are measured in the interface folder. This allows the user to override the default implicit global reference frame and thus output pelvis rotation relative to a custom frame.
Add a new ability to evaluate trunk strength into the built-in studies for joint strength evaluation.
New ligaments connecting the Sacrum and Pelvis segments are added. They are enabled togehter with the ligaments on the lumbar spine through the BM_TRUNK_LUMBAR_LIGAMENTS define statement.

Changed:

The “ADL gait (MoCap model)” has been updated with most recent improvements from our internal projects. The marker protocol has been adjust and a lot of small data problems (marker dropouts etc) has been fixed.
The posture of the standing lift example have been modified to make the example more robust.
The Tuber_ischiadicum node to Seat_contact as it was misaligned to the actual bony landmark position. New Tuber_ischiadicum nodes have been added at the bony landmark. The renaming also makes it easier to identify what the node is used for across the ammr models.
Changed the way the arm joint moment measures are calculated. This affect the output when no muscles are added to the model, and the
moments are now calculated and expressed in same way as when muscles are included. The moments are expressed in a fixed proximal reference frame instead of using the euler axis of rotation which may not be othogonal. All moment contribution also now found using search function which will be more robust.

AMMR 2.3.3 (2021-03-24)#

Fixed:

OptimizeAnthropometricsOnOff.any preventing models with only one leg

Fix a problem single leg models in AnyMocap. The file included from being loaded.
Removed two unused measures with references to thorax in the scapula and clavicula segments. The references could cause problems for ´AnyKinCOM` which uses search when including segments. Thanks to Handa Kensuke from Terrabyte helping fix this error.
Fix bug in initial wrapping guess for Triceps LH muscle wrapping. This bug could cause the left side Triceps LH muscle to wrap incorrectly at shoulder.
Fix calibration of of element 4 and 5 of the latissimus dorsi muscle. These two stands of the muscles where not included correctly in the calibration study when using the three element muscles model.

Changed:

The settings of the Knee Simulator example has been tweaked to make it run faster.

AMMR 2.3.2 (2021-01-21)#

Warning

Model results can change!

A bug related to scaling was fixed in AMMR 2.3.2. This affect models using the length-mass-fat and uniform scaling, when only Body Height is specified. The results can change as models more accurately match the requested body height.

Fixed:

Fixed tibialis anterior/posterior variables in the SelectedOutput section. The force values were represented as the max() of the muscle elements instead of the sum(). Thanks to Dr. Enrico De Pierie from University Children’s Hospital Basel for fixing this issue.
Fixed a bug when using _SCALING_LENGTHMASSFAT_ and _SCALING_UNIFORM_ and only specifying the body height as input. The segment lengths were set to slightly smaller values, which caused the total body height to be less than what was used as input. The bug occurred since a standard body height in some ‘AnyMan’ files was assumed to be 1.8 m instead of the correct 1.75 m. This fix aligns the results with _SCALING_XYZ_ (used in the MoCap models) and _SCALING_STANDARD_ (50 percentile) which were both correct.
Fixed a problem with foot support in the “Spine Pressure validation model” lying flat on the back. The foot is now supported in the right direction.
Fixed a problem with the Standing Model template which was using an alternate mode where foot constraints were disabled.
Fixed a problem with the ADL gait MoCap example, where the batch processing script would report some trials as failed even if they succeeded correctly.
Use correct times in the Xsens example MoCap (trial “S01-Trial2”). The model stopped walking after a number of time steps because tEnd was set after the last data point in the BVH data file.
Fixed/improved the wrapping surface for the subscapularis muscles. The muscles can no longer slide off its wrapping surface in extreme range of motions.
Fixed infraspinatus muscle wrapping for high arm positions. This fix adds a torus for infraspinatus wrapping on the humerus. It fixes a problem where infraspinatus could slide of its wrapping surface in high arm postures.
Fix problem with latissimus dorsi muscle wrapping in over-head arm postures. A new wrapping ellipsoid has been added at the humeral head.

Changed:

The rectus femoris muscle wrapping surface at the hip has been adjusted to prevent collision between the rectus femoris origin and the wrapping surface. Further, the surface is now used for both the straight and reflected head of the rectus femoris.
Increase the discretization (StringMesh) on approx 30 muscles to improve wrapping.
The results for the “Wilke Spine Pressure” validation model has been updated due to the fix for the _SCALING_UNIFORM_. The updated model improved the validation results slightly.
The new large scale “ MoCap model (ADL gait)” has been updated so the results of running all standing reference trials have been added to the model. This means that all the dynamic trials will work even if the user forgets to first run the standing reference trials. It is still necessary to run the standing reference trials again if any changes are made to the model.
The wrapping for the “Triceps Long Head” muscle has been updated at the humeral head to avoid the muscle wrapping incorrectly in over-head arm postures. This fix also adds a via point at the middle of the humerus to make the wrapping solution more robust.
The VideoLookAtCamera camera class template in the AMMR now saves videos as they look in the model view. I.e. if things are hidden in the model view they will not show up in the video. This feature is enabled by a new setting AnyCameraLookAt.RenderUserInterfaceViewState in AnyBody version 7.3.2. The old behavior can be restored by setting Camera.RenderUserInterfaceViewState=Off; in the class template.

AMMR 2.3.1 (2020-09-30)#

Added:

All models now run with the new wrapping solver by default, which makes all models with wrapping muscles run much faster. Hence the AnyBody73_ExperimentalShortestPathSolver setting is deprecated and no effect. The old wrapping algorithm can be enabled (not recommended) by setting:
```
System.Compatibility.ShortestPathSolverVersion = 2; // 4 is default (new wrapping)
```
New dedicated wrapping ellipsoid for Triceps at the glenohumeral head. This addition solves a few problems with overhead arm postures.

Changed:

Improvements to the new “ADL Gait” example. The model now has muscles enabled and the marker protocol has been adjusted for a better shoulder posture. Also, the batch processing script now runs all trials without hickups.
Improve the shoulder rhythm. Scapula position when using the shoulder rhythm is now determined by the Conoideum ligament driver, like how scapula kinematic is controlled with no shoulder rhythm. The rhythm is now controlled based on the plane of elevation and humerus elevation from the ‘ThoraxHumerus’ measures in the interface folder. This tracks the original specification of the shoulder rhythm in “De Groot, J. H. The shoulder: a kinematic and dynamic analysis of motion and loading. (1998)”. One difference is still shoulder protraction/retraction where regression coefficients needed to be tweaked for the shoulder to work in the full range of motion. De Groot et al (1998) had only based their shoulder rhythm on arm position in front of the body (e.i. positive elevation planes).
Removed metabolic power (Pmet) contributions from artificial muscles defined as AnyMuscle derived classes. Pmet contributions from tools, such as GRF prediction, modelled as AnyGeneralMuscles will no longer be part of studies’ Pmet calculations.
Adjusted the wrapping segments for deltoid posterior so it doesn’t affect the muscle in overhead arm posturess.
Teres minor now uses a torus for wrapping at the humeral head.

Fixed:

Fixed incorrect values in “SelectedOutput” for four reaction moments variables, which were wrong due an implementation change of AnyRevoluteJoint. The following variables in SelectedOutput.Trunk.JointReactionForce were incorrect.
- C2C1FlexionExtensionMoment
- C2C1LateralMoment
- C1C0AxialMoment
- C1C0LateralMoment
The values were wrong because they referered to the internal generalized force output of AnyRevoluteJoint. (i.e. Constraints.Reactions.Fout). The values Fout[3] and Fout[4] can not be interpreted as real physical reaction moments because AnyRevoluteJoint is implemented using euler angles.

Warning

The use of generalized forces (Fout) is discouraged, and will be removed in the AMMR. Instead use the force and moment variables in AnyRefFrameOutput subfolder instead.
Fixed incorrect volume of Satorius muscle in TLEM1 and TLEM2. Thanks to Dr. Adam D. Sylvester from Johns Hopkins School of Medicine and Dr. Patricia A. Kramer from the University of Washington for pointing out the error. The error occurred since the satorius in the original TLEM1 paper was muscles in series with a pseudo insertion/origin on the femur. Both of these muscle elements were therefore listed with the full PSCA of Satorius. This detail was missed in the AnyBody TLEM1 and TLEM2 implementation where Satorius was implemented two parallel elements (TLEM1) and a single element (TLEM2). Hence the Satorius had twice the correct volume.
Fixed a problem when C3D files are malformed and doesn’t contain a FORCE_PLATFORM.ZERO variable. The C3D standard specifies that the variable should exist but since it not used in the models the reference could just be remvoed.
Fixed an problem which prevented the ANSUR scaling plugin example from working correctly 7.3.0
Fixed incorrect output of ThoraxHumerus interface measures. The mesure wasn’t used by other parts of the AMMR until now so the bug had no consequences in previous AMMR versions.
Fixed mass calculation of the foot and talus segments in the GaitVaughan validation model.

Removed:

Removed unused BM_TRUNK_CERVICAL_LIGAMENTS switch which had no effect since there were no ligaments defined in the neck model.

AMMR 2.3 (2020-07-07)#

Added:

Added a new Full Body “ADL Gait” MoCap Example based on the “Rehazenter Adult Walking Dataset” by Schreiber and Moissenet (2019). The model is configured to run all 50 subjects and 1145 trials in the data set. However, you must download the actual data separately from FigShare where it is hosted under a Creative Commons license.
New GUI plugin which uses statistical information from the ANSUR database to set anthropometric values in AnyBody. A small example model is added Examples/StatisticalScalingPlugin which shows how to use the plugin.
Added a new option to optimize “head width” / “head depth” / “neck length” / “Tibia torsion” / “hand breadth” as part of the OptimizeAnthropometricsOnOff class_template in the AnyMoCap framework.
Added new rotation vector based measures in the interface folder for the arm degrees of freedom. These measures (Interface.Right.RotVectorMeasures.*) for joint angles do not have a clinical meaning but are useful when exporting and importing joint angles.

Added a new option for setting custom muscle calibration. I.e. an option which disables calibration so the user can add their own code.

#define BM_CALIBRATION_TYPE _CALIBRATION_TYPE_CUSTOM_

#include "<ANYBODY_PATH_BODY>\HumanModel.any"

// Manually include calibration code.
Main.HumanModel.Calibration = {
  #include "<ANYBODY_PATH_BODY>/LegTLEM/Calibration/CalibrationSequenceRight.any"
  #include "<ANYBODY_PATH_BODY>/LegTLEM/Calibration/CalibrationSequenceLeft.any"
  #include "<ANYBODY_PATH_BODY>/Arm/Calibration/CalibrationSequenceRight.any"
  #include "<ANYBODY_PATH_BODY>/Arm/Calibration/CalibrationSequenceLeft.any"
};

Note

If you need to modify the calibration code, copy it to the application folder and include it from there.

Changed:

All application examples use the new and fast experimental wrapping algorithmn in the AnyBody Modeling System 7.3.0. A notice is shown in the output window to remind the users that the algorithm is enabled. The experimental wrapping algorithm can be used in all models by setting:
```
System.Compatibility.AnyBody73_ExperimentalShortestPathSolver = On;
```
See also

The release notes for the AnyBoy Modeling System has more information on the new and faster experimental wrapping algorithm.
Split the SternoCleidomastoid muscle up into two muscle branches. This makes the two heads of the muscle able to work independent.
Add extra muscle-via points on for the Latissimus dorsi on the Thorax segment. This change fixes wrapping problems where the Latissimus dorsi muscle strands would slide off the wrapping surface representing the thorax segment.
Renamed all deprecated muscle class names. AnyViaPointMuscle-> AnyMuscleViaPoint and AnyShortestPathMuscle-> AnyMuscleShortestPath
The AnyMoCap framework now uses a more robust way of saving optimized parameters from the parameter optimization studies, when using AMS 7.3.
Pectoralis Major has been split from 5 into 10 branches to better represent the real fiber direction of the muscle. Similarly the origins of the new Pectoralis Major muscles have been moved to align with real anatomy of the muscle.
Changed the format used by the AnyMoCap models when transferring joint angles from the mrker tracking step to inverse dynamics simulation. The joint-angles for the arms and pelvis rotation are now written in terms of rotation vectors instead of Euler angles. This fixes potential singularity problems. The temporary joint angle files produced by the MoCap models have been renamed to indicate the data is no longer Euler angles.

Note

This means that the data in these temporary files can not easily be interpreted from a clinical point of view. Create your own output files with physiological joint angles if you need to export that data.
The body model configuration plugin have been updated. This fixes a number of smaller issues and bugs.
The via points of PeroneusLongus and PeroneusBrevis have been adjusted to ensure the muscles maintain moment arm in a larger range of motion.
Rectus abdominis muscle has been split into eight branches to better represent geometry, than what is possible with one branch. The strength between the new branches has been split evenly. Additionally, the PCSA has been increased from \(2.6 cm^2\) to \(7.9 cm^2\) according to McGill et al 1988, the \(2.6 cm^2\) originates from a study with elderly subjects, the McGill study used mid age subjects.
Adjusted the origin of Serratus Anterior 1 so it aligns with the geometry of the rib on which it originates.
Changed the way the deltoid wrapping surfaces move relative to humerus. This changes makes it wrapping more robust to deltoid flipping over to the wrong side of the wrapping surface in extreme postures.
The BVH virtual marker protocol have been adjusted. If older BVH models is used with AMMR 2.3 a warning/error is triggered to warn the user that the protocol needs to be updated.

Fixed:

Fixed problems with the following variables in the SelectedOuput folder: HipAbductorMuscleForce, HipExtensorMuscleActivity, HipExtensorMuscleForce, KneeFlexorMuscleActivity and KneeFlexorMuscleForce.
Markers on BVH stick-figure model in the AnyMoCap framework now respects the setting: Main.ModelSetup.BVHFileData.ModelDrawOnOff.
Fixed occasional kinematics problems with FullBody MoCap models during inverse dynamics simulation. This was fixed by changing the internal representation of the shoulder joint angles when transferring kinematics from marker tracking to the Inverse Dynamics simulations.
Fixed a problem with the Body Model configurator plugin showing reporting: “No Human Model” when a configuration file already exists.
Corrected the location of via points of Flexor_Digitorum_Superficialis_Digit2 to avoid wrapping surface collisions in certain hand positions.
Corrected the location of via points of Flexor_Digitorum_Superficialis_Digit3 and 4, Palmaris_Longus, Extensor_Carpi_Radialis_Brevis and Extensor_Digitorum_Digit2 to avoid wrapping surface collisions in certain hand positions.
The muscle via point representing the bicipital groove have been adjusted to ensure the Biceps Caput Longum wraps the humeral head correctly in
Fixed a bug in the FreePosture model, where input for the Left/Right arm drivers was switched in some places.
Fixed missing visual color indication of force plate forces for type 3 force plates in the MoCap models.
Fixed a bug with in the built-in studies to evaluate arm joint strength. The range of motion for the left arm elbow pronation/supination were not correct.
Fixed a bug preventing the model from loading with with _SCALING_XYZ_ and both legs excluded.
Fixed the load-time position of the head segment when neck scaling is changed.
Fixed a problem with visualization in GRF prediction class which prevented GRF prediction to be used with moving base frames (i.e. treadmills). Thanks to Marco Antonio Marra (University of Twente) for fixing this.
Fixed the marker node orientation for BVH (inertial based) MoCap models in the CreateMarkerDriver class template. Marker orientations are now handles identical to normal C3D based markers.```
Fixed incorrect wrapping of teres minor and teres major at extreme shoulder range of motion. New wrapping surfaces have been added. One in Humerus and one on scapula. The meet at the glenohumeral joint to prevent the muscles from sliding to the wrong side of the humerus.

Removed:

Removed unused support files for muscle contact. Tools/ModelUtilities/ContactMuscles/*

AMMR 2.2.3 (2019-11-13)#

Added:

Add new option to set the type of wrapping surface used in the deltoid wrapping implementation. The following will force the use of cylinders (which is faster) instead of ellipsoids.
```
#define BM_ARM_DELTOID_WRAPPING _DELTOID_WRAPPING_CYLINDERS_
```
See BM_ARM_DELTOID_WRAPPING for possible options.

Fixed:

Fixed problems with BVH models that have jumping angular data due to multiple solutions to the Euler angle equations when gimbal locks occur. The fix requires a new structure of the BVH model, where virtual marker trajectories are calculated by the AnyInputBVH class. See the updated BVH_Xsens example, and port your existing BVH models to the new example structure.
Fixed a problem in AnyMoCap models, where model view operations in Main.ModelSetup.Views.SetViewMacros would not trigger a redraw of the model view when executed directly.

Changed:

Increase the time offset when running MoCap inverse dynamics simulations. The offset was 2 frames which were skipped at the start/end of inverse dynamics simulations. But the accelerations of 4th order b-spline are only stable on the fourth frame, and hence the offset has been increased to three frames instead of two.
ScalingXYZ scaling law has been extended to respect the following new variables in the HumanModel.Anthropometrics.SegmentDimensions folder: (HeadWidth, HeadDepth, TrunkDepth, NeckLength, FootWidth)

Removed:

Remove the joint muscles’ strength dependency on the range of motion. Joint muscles are the torque actuators embedded in the joints when the model is loaded without muscles. Previously, joint muscles would reduce their strength to 10% when the joint was outside the range of motion. The lower strength outside the range of motion was originally implemented to prevent inverse-inverse simulations finding non-physiological solutions. However, this problem is now better solved with kinematic joint limits, and the change in joint strength could sometimes cause models to fail with a muscle recruitment failure.
Remove the warning for modified Body model files. The warning can still be enabled by setting the switch #define ANYBODY_ENABLE_MODIFIED_AMMR_NOTICE

Added:

Added a warning to MoCap models when the number of frames is below 8. Since the low number of frames causes problems with both low-pass filters and b-spline interpolation. Note: C3D files with only a single frame works fine since that is handled specially and often used for static trials.

AMMR 2.2.2 (2019-09-12)#

Fixed:

Fixed kinematic problems when driving specific wrist-flexion/abduction values. The definition of wrist flexion in BodyModel.Interface now measures the flexion between the radius and small artificial WristJointSeg segment between the radius and the hand segment. This ensures that there is always unique solution when driving the wrist flexion and abduction.
Fixed a bug in the AnyMoCap examples when setting BM_SCALING to _SCALING_LENGTHMASSFAT_.
Fixed a number of smaller bugs with Body Model configuration plugin.
Fixed a bug in calibration of 3 element leg muscles in the TLEM1 and TLEM2 model. The problem was that the first calibration study (LegCal1) included muscles which were also calibrated specifically in later calibrations. This could in some cases (certain scaling) lead to a problem where LegCal1 would be forces to change the fiber-length even though later specific calibration of the muscle did not need that. Now, LegCal1 only calibrates muscles which are not included in the later calibration studies.

Changed:

Changed the posture of the push-up model example to something which looks more natural, and reduces the max muscle activity.

AMMR 2.2.1 (2019-05-13)#

Fixed:

Fixed a symmetry issue with Scapula scaling in the _SCALING_XYZ_ scaling law.
Fixed a bug in the Knee Simulator example regarding an extra tibiofemoral AnyForceSurfaceContact.
Fixed a bug in how the Conoid driver scales with scapula size.
Fix bug in reference axes for SacrumPelvis Moment measures in selected output. Thanks to Divyaksh Chander from Politecnico di Torino for fixing this.
Attempt to fix muscle wrapping errors with Latissimus dorsi when the model bends forward. This was done by increasing the Augmented Lagrangian coefficient SPLine.AugLagCoef value and the using full wrapping solver.
Fix some muscle wrapping problems with subscapularis muscle by increasing the number of points in the string mesh.
Fixed minor symmetry issue in the head markers of the Full Body MoCap example.

Changed:

Changed the recruitment criterion to the power of 2 (quadratic) in the two MoCap examples using GRF prediction and weak human-ground residuals. (link 1 and link 2). This greatly increases the robustness of recruitment solver and prevents many muscle recruitment failures.

Added:

New options to optimize pelvis-, trunk- and head- widths and depths in the OptimizeAnthropometricsOnOff class template.
Simple library of Python utility functions which can be used from AnyScript. This first version only adds a few functions from the Python’s os.path module. They are used by including the Python.Utils.any file:
```
#include "<ANYBODY_PATH_MODELUTILS>/Python/Utils.any"

AnySwitchVar file_exists = PyUtils.os.path.exist("some-file")
```

AMMR 2.2 (2019-04-03)#

Added:

New implementation of the Deltoid muscles that uses wrapping instead of previous rake-segment/via-point approach. The new wrapping deltoid was developed by Marta Strzelczak from Ecole de technologie superieure, Montreal, CA. The new implementation is used by default but the old implementation can be enabled with the BM_ARM_DELTOID_WRAPPING switch. Please see the Shoulder-Arm Documentation for more information.
Added new example model of a Knee Simulator using a knee implant model and force-dependent kinematics (FDK). See the Knee Simulator example for more information.
New model plugin (BodyModel Configurator) which provides a graphical user interface to configure the Body Model (i.e. setting the BM_* parameters). Please see the blog post introducing the BM plugin.
Added a new Posture prediction model based on standing posture. The model can predict posture as a consequence of applied loads in hands. It does this by minimizing joint torques and applying balance drivers which account for external applied loads.
Added new standing model example which uses soft constraints and GRF prediction. See this link. This new model is good starting point for making standing/balancing models, and the corresponding standing model in the template generator has also been updated.
Added new kinematic rhythm to determine the Sterno-Clavicular axial rotation, effectively removing the degree of freedom from the shoulder model. The rhythm distributes the axial rotation equally between SC and AC joint. The rhythm is active by default, but can be disabled with BM_ARM_CLAVICULA_ROTATION_RHYTHM switch.
More documentation on the AnyMoCap framework and the settings available .
New measures for shoulder angles based on recommendation from International Society of Biomechanics (ISB). The measures are available in the BodyModel.Interface folder. The new measures are:
- AcromioClavicular (Wu et al. 2005 section 2.4.3)
  - Protraction
  - MedialRotation
  - PosteriorTilt
- ScapulaHumerus (Wu et al. 2005 section 2.4.4)
  - PlaneOfElevation
  - Elevation
  - InternalAxialRotation
- ThoraxScapula (Wu et al. 2005 section 2.4.6)
  - Protraction
  - MedialRotation
  - PosteriorTilt
- ThoraxHumerus (Wu et al. 2005 section 2.4.7)
  - PlaneOfElevation
  - Elevation
  - InternalAxialRotation
Three new BM switches to control add default drivers for the individual neck degrees of freedom:
A default center of mass kinematic measure were added
- Main.HumanModel.BodyModel.Interface.CenterOfMass
Markers in MoCap models now changes color to gray when they drop out (i.e. have a weight of zero).
Added new ASIS/PSIS/PT bony-landmark nodes to the PelvisSeg.Right/Left folders. This ensures the bony landmarks are easily available as nodes in all models even if the legs are not included.
Added a new setting (#define MOCAP_FILTER_JOINT_ANGLES ON/OFF) to the AnyMoCap frame work. If enabled a filter will be applied to the intermediate set of joint angles generated by the Marker Tracking step. This can be useful to remove high accelerations due to kinematic limit constraints (e.g. Joint angle limits, surface contacts etc.).
Added a #define MOCAP_PARAMETER_FILE_PREFIX switch to override the prefix for parameter identification files (containing marker position and scaling). This can be useful in special cases where subjects share a common parameter identification file.
Added two new default arguments (MANNEQUIN_FOLDER, BODYMODEL_FOLDER) to the class_template Template_MannequinDrivers, making it easier to reuse the class template as a general-purpose driver for all joint angles.
Added a PreAnalysis step to the video recorder template (CameraClassTemplate.any). Operations placed in the PreAnalysis step will be executed before the video recorder starts.
Added a new warning if using low-pass filters in the AnyMoCap model without a zero phase filter (e.g. warn if FilterForwardBackwardOnOff is set to Off)
Added a new option for choosing a different implementation of the kinematic sliding between scapula and thorax. The new scapula sliding implementation uses multiple points on the ribs and a norm measures to surfaces on the scapula. This work is preparation of a new thoracic model where ribs are individual segments. Note that this implementation is still a work-in-progress. The new thorax-scapula contact can be enabled with the BM_ARM_THORAX_SCAPULA_CONTACT switch:
```
#define BM_ARM_THORAX_SCAPULA_CONTACT _MULTIPLE_POINT_CONTACT_
```

New DEFAULT_PARAMETER_FOLDER class template for creating folders with default values which can be overridden. See the following example:

DEFAULT_PARAMETER_FOLDER Settings(
    NPARAM = 2,
    PARAM_1 = TibialRotation, PARAM_1_TYPE = AnyMat33,
    PARAM_2 = Offset, PARAM_2_TYPE = AnyVar
) = {
    // Default values are specified in the defaults folder.
    Default.TibialRotation = RotMat(5*pi/180,y);
    Default.Offset = 0.005;
};

// Parameters can now be overridden if desired.
Settings.TibialRotation = RotMat(10*pi/180,y);

Changed:

Re-implemented the origins for the Semitendinosus and Biceps Caput Longum muscles in the TLEM-2.1 model based on the original digitized insertions and MRI scans. Better correspondence with the original MRI scans increases the moment-arms through range of motion.
New wrapping surfaces for Semitendinosus and Biceps Caput Longum muscles based on original MRI scans. New surfaces ensure that muscles don’t penetrate the pelvis bone at high hip flexion angles.
Reimplement insertion of Gluteus Medius/Minimus of the TLEM2.1 model based on original TLEM2 dataset. This improves range of motion in which Gluteus Medius and Gluteus Minimus has a moment arm for internal rotation of the hip.
Kinematic rhythms for the shoulder, lumber-spine and cervical-spine can now be specified as soft contraints. The setting is controlled by setting the BM control statement BM_XXX RHYTHM to _RHYTHM_SOFT_. For example:
```
#define BM_ARM_SHOULDER_RHYTHM _RHYTHM_SOFT_
```
Re-implemented the origins for the Semitendinosus and Biceps Caput Longum muscles in the TLEM-2.1 model based on the original digitized insertions and MRI scans. Better correspondence with the original MRI scans increases the moment-arms through range of motion.
New wrapping surfaces for Semitendinosus and Biceps Caput Longum muscles based on original MRI scans. New surfaces ensure that muscles don’t penetrate the pelvis bone at high hip flexion angles.
Reimplement insertion of Gluteus Medius/Minimus of the TLEM2.1 model based on original TLEM2 dataset. This improves range of motion in which Gluteus Medius and Gluteus Minimus has a moment arm for internal rotation of the hip.
The TLEM2 model is now the default leg model unless the model is configured otherwise.
All AnyMoCap examples where changed to use the _SCALING_XYZ_ scaling law. This scaling law is similar to _SCALING_LENGTHMASSFAT_, but allows for optimization of all segment dimensions (hence the XYZ name).
Scaling law _SCALING_XYZ_ now has a scaling factors to control the neck scaling. Before neck scaling were controlled by the head scale factors.
All MoCap model examples now use the option (UseC3DWeightResiduals=ON) in the marker protocols. This ensures that the marker weights are reduced to zero when a marker drops out (i.e. when the residual value in the C3D file becomes negative).
AnyMoCap examples are updated with extra margin at the start/end of the analysis compared to the data in the C3D file. This prevents inaccurate kinematics due to low-pass filter transients.
Add warning to AnyMoCap models when tStart/tEnd are very close to the start/end times of the data in the C3D file. This can cause inaccurate kinematics at the very start/end of the simulation due to low-pass filter transients.
Increased the resolution tibia bones for the TLEM1 and TLEM2 models.
All examples now have their body model configuration in a separate file (usually, BodyModelConfiguration.any) to accommodate the new Body Model Configurator plugin.
The MoCap models now use joint angles for all degrees of freedom when transferring motion from MarkerTracking study to the Inverse dynamic study. This means that rhythms can now be soft constraints when running the Marker tracking study, and markers can override the kinematic rhythms if needed.
Refactored all examples to avoid the confusing paradigm with a reference called Model.HumanModel pointing to HumanModel.BodyModel.
Improvements to the accuracy of the wrapping cylinder used by Teres Minor and Teres Major.
The interface morphing algorithm (which morphs pelvis of the trunk or leg dataset to match) now includes the ASIS/PSIS/PT bony landmarks as control points. This change ensures that bony-landmarks of the Trunk and Leg datasets map to the exact same point.
Models generated from templates now fail with a descriptive error message if they are loaded with an older unsupported version of the AMMR.

Fixed:

Fixed problem with the initial guess for Vastus wrapping which could cause the Vastus muscle to wrap incorrectly when the knee started in slightly over stretched posture.
Fixed location of bicep longus via points to pass through bicipital groove
Fixed a regression in bike model where the foot crank connection did not rotate around the correct point (PedalConnectNode). The point in the foot coordinate system was also updated to a more posteriorly location beneath the meta tarsal joints.
Fixed an issue with over-constraint default mannequin drivers when shoulder rhythm was enabled. Now the default mannequin drivers will not create drivers for sterno-clavicular rotation, elevation, protraction when the shoulder rhythm is enabled.
Fixed the initial wrapping guess for Teres Minor to prevent incorrect wrapping when starting model in postures which are close to range of motion.
Fixed typo in Flexor_Digitorum_Profundus_Digit5 name.
Fixed an interpolation issue with BVH based AnyMoCap models when the models were using all frames in a BVH file.
Added missing hand length/breadth values needed by Detailed Hand to the CustomScaling.any for custom scaling scenarios
Fixed missing possibility for overriding the reaction forces for the Trunk flexion/extension/rotation drivers in HumanModel.DefaultMannequinDrivers.
Add missing strength scaling factor to pectoralis_major_thoracic_part_3 in the simple muscle configuration.
Fixed issue with the Standing Model example, where the elbow flexion velocity was incorrectly set to a non zero value.
Fixed the problem with over-constraint models when adding the shoulder rhythm.
Fixed a bug with the Video class (CameraClassTemplate.any) when specifying direct path to ffmpeg.
Fixed a problem with the FullBody AnyMoCap example where a relative high weight on the soft clavicula rotation constraints could cause the model to fail kinematically in with the AnyBody Modeling System 7.2.

Removed:

Removed previously deprecated MoCap model which were not based on the AnyMoCap framework.
Removed all references to the previously deprecated BM_TRUNK_NECK switch.
Removed outdated versions of JointLimits_template.any and KinLimitsDriver_template.any from the AnyMoCap folder. Updated version of the files still exists in the Tools\ModelUtilities\KinematicLimits folder.
All uses of the Sterno-Clavicular axial rotation in all examples, since this DOF is now handled by a kinematic rhythm which distributes the rotation equally between SC and AC joint.
The BM_MANNEQUIN_DRIVER_INDIVIDUAL_WEIGHTS switch was removed, since the individual weights can be set directly using
```
Main.HumanModel.DefaultMannequinDrivers.KneeDriverRight.WeakDriverWeight = 0.1;
```

AMMR 2.1.1 (2018-06-12)#

The AMMR 2.1.1 version is a minor release of the AMMR with smaller changes and bugfixes. The AnyBody Managed Model Repository now has a DOI (10.5281/zenodo.1250764). This is handled by Zenodo.org (The European Open Science platform hosted at CERN).

Added:

model. This RefNode was also present in the TLEM1 model and was used by few

Added a Leg.Seg.Foot.GroundJoint RefNode to the foot segment of the TLEM2 applications.
New GroundVelocity setting added to the ForcePlateAutoDetection class_template, which makes class usable with instrumented treadmills.
All force plate types now have a user-definable ForcePlate.CalMatrix variable. The feature is useful to easily compensate for errors in the c3d file (i.e. swapped channel and wrong sign)

Changed:

Enhanced the multi-trial MoCap example for best practice for MoCap trials with multiple subjects and trials. The example now shows how to deal with multiple subjects and storing the c3d files in a separate folder.

Fixed:

Corrected the default mass of the patella segment in the TLEM2 model from zero to 0.025.
Add missing unilateral reaction between TS node on Scapula and the Thorax when using the shoulder rhythm.
Adjusted the initial wrapping vectors for the semitendinosus, semimembranosus, and biceps caput breve muscles around the knee. This has no influence on the output of the model, and is only done to reduce the risk of the muscles wrapping the wrong direction around the wrapping surface.
AnyMoCap:
- The high memory usage of the AnyMoCap BVH model has been fixed. The high memory usage was due to a reference in the CreateMarkerDriver class template which caused the studies to include the BVH input data multiple times in the output.
- The BVH and multi-trial examples now use zero phase shift filtering of force plate forces. The zero-phase filter can be important to ensure that forces are synchronized with kinematic data.
- Fix bug in Type 1 Force plate when data is not in meters (i.e. PointScaleFactor != 1). The PointScaleFactor was applied twice to the z moment component.
- Fix a problem reading C3D files where force plate meta information is saved with the wrong dimensionality. Such a issue can, for example, happen if the c3d files are created manually in MATLAB.
- The option to load parameter optimization results is no longer hidden when the MOCAP_CREATE_PARAMETER_ID_SHORTCUT is set to OFF.

AMMR 2.1.0 (2018-03-22)#

Added:

New squat example model which demonstrates a parameterized squatting motion.
New #class_template for adding limit drivers to kinematic measures. Can be included with #include "<ANYBODY_PATH_MODELUTILS>/KinematicLimits/KinLimit_template.any"
Muscle ColorScale can now be set from the Main.DrawSettings.Muscles.ColorScale. If you port an older model to the new AMMR you will need to update your DrawSettings.any file.
AnyMoCap framework:
- New argument DRAW_SCALE in the CreateMarkerDriver class_template to control the visual size of markers.
- Added an option to the ForcePlateAutoDetection class template to make the limb1/2 contact detection mutually exclusive. Setting the option ALLOW_MULTI_LIMB_CONTACT=OFF will ensure that both legs cant be in contact with the plate at the same time. This can prevent accidental contact detection for the collateral leg in the swing phase.
- New option to specify the contact nodes in ForcePlateAutoDetection class template. This makes the class useful for connecting force plate to other limbs than the feet.
- Add support for the Shoulder Rhythm in AnyMoCap based models.
- Add support for the Detailed hand model in AnyMoCap based models.
New BM_FOOT_MODEL parameter, as preparation for integrating the Glasgow-Maastricht foot model (GM-Foot) back into the AMMR. Currently, the parameter can only be used for excluding the feet (#define BM_FOOT_MODEL _FOOT_MODEL_NONE_). making it easier to work on integrating the GM foot model.

AMMR 2.0.0 (2017-11-29)#

Major changes:#

New lower extremity model (TLEM2.1)#

The Twente Lower Extremity Model version 2.0 dataset, developed in the TLEMsafe EU project was implemented in the AMMR repository. The model is not the default model, but can be enabled with the BM parameter #define BM_LEG_MODEL _LEG_MODEL_TLEM2_
The model is versioned TLEM 2.1, to indicate the number of changes and correction which has been added in the process. The changes and updates to the TLEM2 dataset was done in the Life Long Joints EU research project (paper submitted for publication).
The most important changes to the TLEM 2 dataset include the following:
- Updated wrapping for the Gluteus Maximus, Iliacus, Psoas around the hip.
- Reworked muscle topology for Gluteus Medius and Gluteus Minimus
- Updated wrapping for Hamstring muscles, and Gastrocnemius around the knee.
- Redefined revolute knee axis and patella joint axis and patella tendon length based on the bone geometry. The original TLEM knee axis was estimated using a functional method, and was only valid for very small flexion angles. Thanks to Marco Antonio Marra (Radboudumc) for this for this improvement.
- The ratio of volume between Gluteus Maximus superior/inferior has been re-estimated based on the original cadaver MRI scans.
- Update the Sartorius via points.
- Re-implemented the Hip Joint location for the pelvis and the femur by fitting spheres to the femoral head and the acetabulum. This is in contrast to the original TLEM2.0 implementation where the hip joint center was found using a functional method.
- Included a more detailed version of the patella bone.
- Various minor bug fixes from the original implementation used in the TLEMSafe project.
- Corrected the femoral attachment points for the popliteus muscle
- Update ankle joint nodes with positions fitted to the bone geometry
- Small correction to wrong insertion points for Adductor Longus and Vastus Medialis.
See the dedicated TLEM2.1 page page for more information.

AnyMoCap#

New framework for running MoCap models. The AnyMoCap framework is an effort to create a simple and unified framework for doing any kind of MoCap analysis with the AnyBody Modeling System. See the AnyMoCap example gallery for more information.
Algorithms and file for Ground reaction force prediction are added to: ammr/tools/GRFPrediction/. See the MoCap examples for how they are used.

TLEM 1 updates#

The cumulated smaller bug fixes and updates to the TLEM1 model mean that we now denote the model 1.2.
Changed the position of the Heel contact node, to align the heights of the TLEM1 and TLEM2 models.
Added missing GeomScale function to the patella segment.
Update ankle joint nodes with positions fitted to the bone geometry
PSCA is now calculated based on the scaled fiber length. This aligns the TLEM 1 model with the new TLEM 2 model. It also means that scaling the model without changing the muscle volumes will change the strength of the model.
Update scaling of the Patella tendon to work with non-linear scaling laws.
Added visualization of the Fibula bone.

AMMR restructure#

Added a top-level Tools folder helper files and other models which don’t belong in Body/ or Application.
Moved Body/AAUHuman/Toolbox to Tools/ModelUtilities
Renamed the Body/AUHuman to Body/Mandible_AU
Restructured the anthropometric (“AnyMan”) folder. The folder HumanModel.AnthroDataSubject is renamed to HumanModel.Anthropometics. The structure of the folder has also changed with a SegmentDimensions and SegmentMasses subfolder.

Configuration parameters#

The previously used system to configure human body using a BodyPartSetup file was completely replaced with the new body model (BM) parameters.
Please see the documentation on: BM parameters.

Scaling laws#

An additional scaling law based on individual segmental scaling factors was added to the repository. It can be enabled using this BM parameter #define BM_SCALING _SCALING_XYZ_. See the guide on scaling.
Default scaling is now _SCALING_STANDARD_ (e.g #define BM_SCALING _SCALING_STANDARD_) which scales all models to default standard 50% male.
Introduced _SCALING_NONE_, which disables scaling. E.g. models gets the original unscaled size.

New Mandible model#

Added new mandible model based on a CT scan of a 40 year old male. For more information see the documentation for the model or the validation example.

Spine model#

BM parameters were updated to have control over each section of the spine and relevant components.
The anatomical reference frame of the thorax segment was modified. This change reflects a change in the pelvic anatomical reference, and ensures upright posture for the standing postures, to align C1C0 joint with the hip joint centers.
Boney surfaces of both pelvis and sacrum were updated and now correspond better to the relevant muscle attachments. These segments now also share a common scaling function. Hip joint centers were corrected for the old Leg model.
Improved wrapping surface for Psoas Major muscles based on the TLEM2.0 MR scans
Insertion, via, and attachment nodes of relevant muscles have been updated to match new geometries of pelvis and sacrum.

Arm model#

The model now facilitates individual personalization for each side using nonlinear morphing schemes in a more consistent manner. Previously the morphing needed to be done on the right side and then reflect to have the left side morphing. This change removes an extra mirroring step.
Arm calibration was updated
BM parameters have been updated for more convenient use. BM_ARM_DETAILED_HAND and BM_ARM_SHOULDER_RHYTHM are now used instead of individual switches for right and left side, which were deprecated.
Muscle wrapping surfaces were updated for more physiological behavior.
Scapula reaction contact forces were simplified, and do not longer utilize slider segments.
Conoid ligament length now scales along with the scapula width.
Add a GeomScale function the Clavicula segment.

Muscle models#

All muscle models are updated to support the structure of the new AnyMuscleModel3E and AnyMuscleModel in the AnyBody Modeling System 7.1. The following variables are renamed:
- The “optimal fiber length” variable renamed from Lfbar to Lf0
- The “Pennation angle” variable renamed from Gammabar to Gamma0
- The “Tendon strain at F0” variable renamed from Epsilonbar to Epsilon0
Restructured the muscle model section of both TLEM1 and TLEM2 models.
- All the original TLEM based muscle parameter are now located under: Leg/ModelParameters/Muscles
- All scaled muscle parameters are located in Leg/MusPar/SubjectMusPar. This folder references the TLEM muscle and applies strength scaling etc. The SubjectMusPar folder and all subfolders are implemented with class_template. Thus, all muscle parameter can now be overridden in applications by just assigning the variables a new value: E.g.
```
Main.HumanModel.BodyModel.Right.Leg.MusPar.SubjectMusPar = {
  GastrocnemiusMedialis.MuscleVolume = 300; // Volume in mililiters
  GastrocnemiusMedialis.Pennationangle = 15; // (in degrees)
};
```

Calibration#

Updated calibration for Arms and TLEM legs in the Body Model to
- include muscles to the calibration study with search functions.
- drive the postures using the measures from the interface folder to remain anatomically similar throughout future versions.
Added new experimental two-parameter calibration, which is based on range-of-motion postures. The calibration type is controlled by the BM_CALIBRATION_TYPE parameter.

For example:
```
#define BM_CALIBRATION_TYPE _CALIBRATION_TYPE_2PAR_
```

Minor Changes:#

Added new initial guess for wrapping muscles, which make the wrapping more when the model starts in extreme postures.
Updated many examples to use the TLEM 2.1 model. See the example gallery.
BM mannequin drivers are now implemented with a class_template allowing all weights and other settings to be customized.
A default HumanModel.Mannequin folder is now automatically created with a class_template when no user-defined Mannequin file is set.
A default Main.DrawSettings folder is now automatically created with a class_template when no user-defined DrawSettings file is set.
Extra Mannequin drivers for the individual shoulder degrees of freedom: Sterno clavicula protraction, Sterno clavicula elevation, Sterno clavicula axial rotation
The initial positions of the pelvis now use the anatomical reference frame. This follows the logic from the initial rotation of the pelvis which also uses the anatomical frame.
DeltoidMuscleConnector segment loading time positioning now depends on the Humerus segment.
Added class template to easily create videos from AnyScript model. The tool requires that FFmpeg is installed. The class template can be found in: <ANYBODY_PATH_MODELUTILS>/Video/CameraClassTemplate.any. See this blog post.
In TLEM models make the opacity of the patellar tendon dependent on the opacity of the patellar surface.
New AnyDoc classes are added to the different body model, so the GUI can create direct links to the documentation.
Simplify the Scapular reactions to the thorax segment.
Foot contact nodes are aligned with the AnatomicalFrame
Updated the Wilke Validation example to reflect the forces for the AMMR 2.0 repository.
Updates to BM parameters:
- New BM_ARM_DETAILED_HAND parameter for the detailed hand. The old BM_ARM_DETAIL_HAND_RIGHT/LEFT are deprecated.
- New BM_ARM_SHOULDER_RHYTHM parameter for controlling the shoulder rhythm. The old BM_ARM_SHOULDER_RHYTHM_RIGHT/LEFT are deprecated.
- Added new BM_JOINT_TYPE_<joint>_<side> parameter for completely disabling joint and associated nodes in the lower extremity models. (See: for example BM_JOINT_TYPE_HIP_RIGHT)
- New BM_LEG_MODEL parameter for setting the type of leg model used. The BM_LEG_RIGHT/LEFT are now only ON/OFF options.

Fixed:#

Sign for the plantar flexion variable were reversed in some section of the model. This has been fixed.
Bug in Mannequin drivers for the neck, where velocities were not set correctly. (Thanks to Assoc. Prof. Michael Skipper Andersen for reporting this)
Fix small bug preventing StandingModelScalingDisplay from loading when using the Leg model.
Fixed the opacity of the patellar surface in TLEM models, which pointing erroneously to the opacity of the talus.
Fixed wrong symmetry of nodes on the C7 segment of full neck model.
Latissimus Dorsi 5 fascicle was missing in MuscleNames.any and thus from many symmetry measures.
Fixed a symmetry problem for the Deltoid muscles at the shoulder.
Fixed a symmetry problem for the Disc stiffness from L1 to L5
Fix white surfaces in examples with flat STL surfaces. For example Cross Trainer.
Fixed an issue preventing Standing Model from working with one leg.
Fixed a problem with the drawings of the bones in the Arm model which were not always symmetrical.
Fixed symmetry issues in scaling laws for scapula and clavicula, and humerus.
Fixed a bug where a the Pectoralis wrapping cylinder was not a included in the calibration study.
Fixed wrong sign for the AnklePlantarFlexion variable.
Added missing GeomScale and AnatomicalFrame for Ulna segment.
Fixed ScalingCustom.any to use Thorax folder instead of Trunk.

Removed:#

Old MoCap examples have been moved to Application/Examples/Deprecated
Removed the deprecated AMMR1.4 hip rotation sequences.
The GM-foot model. A new version of this in the pipeline. Contact us if you are interested in this work.
All older BodyModels which were deprecated in AMMR1.3

Changelog

Contents

Changelog#

AMMR 4.0 beta#

AMMR 3.1.0 (2024-??-??)#

➕ Added:#

🩹 Fixed:#

🔧 Changed:#

AMMR 3.0.4 (2024-07-02)#

🩹 Fixed:#

AMMR 3.0.3 (2024-06-10)#

🩹 Fixed:#

AMMR 3.0.1 (2024-02-13)#

🔧 Changed:#

AMMR 3.0 (2024-02-13)#

✨ Highlights#

🩹 Fixed:#

➕ Added:#

🔧 Changed:#

🧹 Removed:#

AMMR 2.4.4 (2023-04-03)#

AMMR 2.4.3 (2023-01-27)#

AMMR 2.4.2 (2022-07-08)#

AMMR 2.4.1 (2022-05-30)#

AMMR 2.4 (2022-04-28)#

AMMR 2.3.4 (2021-07-05)#

AMMR 2.3.3 (2021-03-24)#

AMMR 2.3.2 (2021-01-21)#

AMMR 2.3.1 (2020-09-30)#

AMMR 2.3 (2020-07-07)#

AMMR 2.2.3 (2019-11-13)#

AMMR 2.2.2 (2019-09-12)#

AMMR 2.2.1 (2019-05-13)#

AMMR 2.2 (2019-04-03)#

AMMR 2.1.1 (2018-06-12)#

AMMR 2.1.0 (2018-03-22)#

AMMR 2.0.0 (2017-11-29)#

Major changes:#

New lower extremity model (TLEM2.1)#

AnyMoCap#

TLEM 1 updates#

AMMR restructure#

Configuration parameters#

Scaling laws#

New Mandible model#

Spine model#

Arm model#

Muscle models#

Calibration#

Minor Changes:#

Fixed:#

Removed:#