The authors acknowledge Mr. Jean Luc Cornille, Science of Motion, for his input into modeling accuracy; Dr. Martha Littlefield and Mr. James Ray (LSU SVM), and Dr. Steve Holladay, Dr. Carla Jarrett, and Mr. Brent Norwood (UGA CVM) for access to anatomical specimens; Dr. Ajay Sharma (UGACVM) and Dr. L. Abbigail Granger and Mr. Mark Hunter (LSUSVM) for conducting CT scans; and undergraduate researchers Jeremy Baker, Joshua Maciejewski, Sarah Langlois and Daniel Pazooki (LSU School of Veterinary Medicine Functional and Evolutionary Anatomy Lab) for their work related to this research. Funding was procured from the Louisiana State University School of Veterinary Medicine&#39;s Equine Health Studies Program via a Charles V. Cusimano grant.

1. Forelimb rigging
<ol>
	<li>Place graphic joints inside the forelimb in all areas of movement. 
	NOTE: The resulting joint placement is a joint chain from the scapula to the distal end of the coffin bone (Figure 2A). In the area of the carpal bones, 3 joints in close proximity are used to increase the bending radius.
	<ol>
		<li>Press the F3 key to enable the Rigging Menu set. In the menus, select Skeleton | Create Joints to select the Create Joints tool.</li>
		<li>In the View panel of the software, click in the approximate areas of the joints found in Figure 2A in the order of 1 to 10, and press the ENTER key.</li>
		<li>Adjust the position of the joints by clicking on the desired joint and use&#160;the Move Tool&#160;by&#160;pressing the W key to translate the joint into the desired position. Alternatively, adjust a joint by clicking on the desired joint and altering the Translate X, Translate Y, and Translate Z values found in the Channel Box/Layer Editor panel.</li>
	</ol>
	</li>
	<li>Create 5 separate Inverse Kinematic handles (IK handles) (joints will be referred to by the numbers found in Figure 2A).
	<ol>
		<li>In the menus, select Skeleton | Create IK Handle to select the Create IK Handle tool. Using the Create IK Handle tool, select joint 1, then joint 3; name this IK handle Front Leg IK in the Outliner panel. Using the Create IK Handle tool, select joint 3, then joint 7; name this IK handle Front Lower IK.</li>
		<li>Using the Create IK Handle tool, select joint 7, then joint 8; name this IK handle Front Toe 1 IK in the Outliner panel. Using the Create IK Handle tool, select joint 8, then joint 9; name this IK handle Front Toe 2 IK in the Outliner panel. Using the Create IK Handle tool, select joint 9, then joint 10; name this IK handle Front Toe 3 IK in the Outliner panel.</li>
	</ol>
	</li>
	<li>Create forelimb controls
	<ol>
		<li>Create a Non-Uniform Rational B-Splines (NURBS) circle by using the Circle tool in the menu Create | NURBS Primitives | Circle.</li>
		<li>Create two NURBS Circles and move them using the Move Tool to encircle joint 3 and joint 10, and name them Front Ctrl and Front Lower Ctrl, respectively, in the Outliner panel.</li>
		<li>Create a NURBS Circle; select the circle, and in the Channel Box/Layer Editor Panel, change the Rotate Z value to 90. Using the Move tool, place it at the tip of joint 10, and name it Front Flick Ctrl in the Outliner panel.</li>
	</ol>
	</li>
	<li>Group Front Toe 1 IK, Front Toe 2 IK, and Front Toe 3 IK by selecting all three and pressing the CTRL + G keys. Name this group Front Toe Group in the Outliner panel. Parent the IK handles and Front Toe Group to the controls. 
	NOTE: It is important to Shift + select in the exact order described below to ensure a proper parent tree.
	<ol>
		<li>Select Front Leg IK, then Front Ctrl in the Outliner panel, and press the P key.</li>
		<li>Select Front Lower Ctrl, then Front Ctrl in the Outliner panel, and press the P key.</li>
		<li>Select Front Lower IK, then Front Lower Ctrl in the Outliner panel, and press the P key.</li>
		<li>Select Front Flick Ctrl, then Front Lower Ctrl in the Outliner panel and press the P key.</li>
		<li>Select Front Toe Group, then Front Flick Ctrl in the Outliner panel, and press the P key.</li>
	</ol>
	</li>
	<li>Use the Bind Skin tool to bind the bone meshes, except sesamoid bones, including navicular bones to the most proximal joint. Ensure that each bone mesh is only bound to one joint.
	<ol>
		<li>Click on the bone mesh, Shift + click on the most proximal joint, and select the Bind Skin tool under Skin | Bind Skin.</li>
	</ol>
	</li>
	<li>Rigging sesamoid bones and the navicular bone
	<ol>
		<li>Create a joint, place it in the middle of sesamoid bone, and press the Enter key. In the View panel, select the sesamoid bone mesh, and Shift + click the joint in the middle of the bone. Use the Bind Skin tool to bind the mesh to the joint. 
		&#8203;NOTE: The sesamoid bone can now be manipulated using the Move and Rotate tools for adjustment when changing the leg position.</li>
		<li>In the View panel, select the joint in the sesamoid bone, Shift + click the nearest joint in the forelimb, and press the P key. 
		NOTE: This parents the joint in the sesamoid bone to the forelimb.</li>
		<li>Repeat steps 1.6.1 to 1.6.2 for other sesamoid bones and the navicular bone.</li>
	</ol>
	</li>
	<li>Repeat steps 1.1 through 1.6 for the other forelimb. 
	NOTE: The joint at the scapula can be selected and translated in all 3 directions (6 degrees of freedom) using the Move tool.</li>
</ol>
2. Hindlimb rigging
<ol>
	<li>Place joints inside the hindlimb in all areas of movement to obtain a joint chain from the head of the demur to the distal end of the coffin bone (Figure 2B).</li>
	<li>Create 5 separate IK handles (joints will be referred to the numbers found in Figure 2B).
	<ol>
		<li>Using the Create IK handle tool, select joint 11, then joint 12; name this IK handle Hind IK in the Outliner panel. Using the Create IK handle tool, select joint 12, then joint 14; name this IK handle Hind Lower IK in the Outliner panel.</li>
		<li>Using the Create IK handle tool, select joint 14, then joint 15; name this IK handle Hind Toe 1 IK in the Outliner panel. Using the Create IK handle tool, select joint 15, then joint 16; name this IK handle Hind Toe 2 IK in the Outliner panel.</li>
		<li>Using the Create IK handle tool, select joint 16, then joint 17; name this IK handle Hind Toe 3 IK in the Outliner panel.</li>
	</ol>
	</li>
	<li>Create hindlimb controls
	<ol>
		<li>Create two NURBS Circles named Hind Ctrl and Hind Lower Ctrl and move them to encircle joint 12 and joint 17, respectively.</li>
		<li>Create a NURBS Circle named Hind Flick Ctrl. Make this circle vertical, and place it at the tip of joint 10.</li>
	</ol>
	</li>
	<li>Group Hind Toe 1 IK, Hind Toe 2 IK, and Hind Toe 3 IK by selecting all three and pressing CTRL + G. Name this group Hind Toe Group.</li>
	<li>Parent the IK handles and Hind Toe Group to the controls. Be sure to Shift + select in the exact order described below to ensure a proper parent tree.
	<ol>
		<li>Select Hind IK, then Hind Ctrl, and press the P key.</li>
		<li>Select Hind Lower Ctrl, then Hind Ctrl, and press the P key.</li>
		<li>Select Hind Lower IK, then Hind Lower Ctrl, and press the P key.</li>
		<li>Select Hind Flick Ctrl, then Hind Lower Ctrl, and press the P key.</li>
		<li>Select Hind Toe Group, then Hind Flick Ctrl, and press the P key.</li>
	</ol>
	</li>
	<li>Use the Bind Skin tool to bind the bone meshes to the most proximal joint. Ensure that each bone mesh is bound to only one joint.
	<ol>
		<li>Click on the bone mesh, Shift + click the most proximal joint, and select the Bind Skin tool under Skin | Bind Skin.</li>
	</ol>
	</li>
	<li>Rigging patella, sesamoid bones, and navicular bone
	<ol>
		<li>Create a joint, place it in the middle of the patella, and press the Enter key. In the View panel, select the patella mesh, and Shift + click on the joint in the patella. Use the Bind Skin tool to bind the mesh to the joint. 
		NOTE: The patella can now be manipulated using the Move and Rotate tools for adjustment when changing the leg position.</li>
		<li>In the View panel, select the joint in the patella, Shift + click on the nearest joint in the forelimb, and press the P key to parent the joint in the patella to the forelimb.</li>
		<li>Repeat steps 2.7.1 and 2.7.2 for the sesamoid bones and the navicular bone.</li>
	</ol>
	</li>
	<li>Repeat steps 2.1 through 2.7 for the other hindlimb.</li>
</ol>
3. Ribbon spine rigging
<ol>
	<li>Create a NURBS Plane with altered options with the length roughly equal to the length of the spine with 1 U-patch and # V-patches, where # is the number of thoracic and lumbar vertebrae. 
	&#8203;NOTE: For this paper, the length is 20 with 22 V patches.
	<ol>
		<li>Select the square found next to the Create Plane tool under Create | NURBS Primitives | Plane.</li>
	</ol>
	</li>
	<li>Rebuild the plane with altered options.
	<ol>
		<li>Press the F2 key to enter the modeling menu set. Select the plane in the view panel, and select the Rebuild tool settings by selecting the square next to the Rebuild tool under Surfaces | Rebuild. Use the following options: number of spans U = 1; number of spans V = # (22 in this case); select &#34;1 Linear&#34; for both the Degree U and Degree V options; keep the other settings to default; and press the Rebuild button.</li>
	</ol>
	</li>
	<li>Create nhairs with altered options.
	<ol>
		<li>Press the F5 key to enter the FX menu set. &#8220;Select the plane in the view panel, and use the Create Hair tool with altered options by selecting the square next to nHair | Create Hairs. Use the following options: output set to NURBS curves; U count =1; V count = # (22 in this case); keep the other options to default; and press the Create Hairs button.</li>
	</ol>
	</li>
	<li>Delete the following in the outliner panel: nucleus1, hairSystem1OutputCurves group, and hairSystem1. Fully expand the group labeled hairSystem1Follicles, and delete all the items labeled with curve__. 
	NOTE: The result should leave a group labeled hairSystem1Follicles that contains a list of items labeled nurbsPlane_Follicle____.</li>
	<li>Select the plane, and move and orient it so that it is roughly overlapping with the spine by using the Move tool and Rotate tool. Select the plane, hold the right mouse button, and select Control Vertex to make all the vertices of the plane visible.</li>
	<li>Move the vertices to orient the follicles to be between the vertebrae at the height where the spinal cord would be. Create # number of separate joints (22 in this case) at any place in the View panel as the position of these joints will be corrected in later steps.</li>
	<li>Parent a joint with a nurbsPlane_Follicle____ so that each has a single joint under its tree.
	<ol>
		<li>In the Outliner panel, select a joint created in step 3.6, then Ctrl + click on a nurbsPlane_Follicle____, and press the P key. Repeat 3.7.1 with the other joints created in step 3.6 and the other nurbsPlane_Follicle____ objects.</li>
	</ol>
	</li>
	<li>In the Outliner panel, Ctrl + select all the joints; in the Chanel Box/Layer Box panel, set the Translate X, Y, and Z to 0. Duplicate all the joints by Ctrl + selecting all the joints in the Outliner panel and pressing the Ctrl + D keys. Un-parent all the duplicate joints by Ctrl + selecting all the duplicate joints in the Outliner panel and pressing the Shift + P keys</li>
	<li>Bind the joints under nurbsPlane_Follicle____ with their respective vertebra mesh.
	<ol>
		<li>Press the F3 key to enter the Rigging menu set. Click on the original joint (not the duplicate joint) under nurbsPlane_Follicle____, Shift + click on the respective vertebra mesh, and then use the Bind Skin tool under Skin | Bind Skin. Repeat these actions in step 3.9.1 for each joint and vertebrae mesh.</li>
	</ol>
	</li>
	<li>CTRL + click all duplicate joints and the plane, and use the Bind Skin tool to bind all the duplicate joints to the plane. 
	&#8203;NOTE: The duplicate joints can now be manipulated to control the vertebrae.</li>
	<li>Repeat steps 3.1 through 3.10 for the cervical and caudal vertebrae.</li>
</ol>
4. Rib and sternum rigging
<ol>
	<li>Place separate joints at the rib head, at the proximal end of the costal cartilage, and at the distal end of the costal cartilage. Parent the joint at the proximal end of the costal cartilage to the joint at its rib head.</li>
	<li>Parent the joint at the distal end of the costal cartilage to the closest joint at the proximal end of the costal cartilage. Parent the joint at the rib head to the spine joint that controls the vertebrae caudal to the rib.</li>
	<li>In the Rigging menu set under the Skin tab, use the Bind Skin tool to bind the rib to the joint at its head and the costal cartilage to both the joints at its proximal end and the distal end.</li>
	<li>Repeat steps 4.1 through 4.3 for each rib.</li>
	<li>Place separate joints at the most cranial end of each sternal segment. Parent each sternal segment joint to the spinal joint most dorsal to each sternal segment joint. In the Rigging menu set under the Skin tab, use the Bind Skin tool to bind the sternal segment to its joint.</li>
</ol>
5. Positioning and animation
<ol>
	<li>Select a frame in the timeline.</li>
	<li>Position the model and controls. Import an image to use as a reference by creating a Free Image Plane. 
	NOTE: The images from Muybridge13&#160;of the horse at the walk were used as proof of concept.
	<ol>
		<li>While the Free Image Plane is selected, select the image file under the Attribute Editor tab and under the Image Plane Attributes dropdown menu.</li>
	</ol>
	</li>
	<li>Select all controls and the spine control joints, and press the S key to save them as a key frame.</li>
	<li>Along different frames along the timeline, move and rotate the controls and spine control joints, and press S. 
	NOTE: Repositioning controls and spine control joints and saving them as key frames along different points of the timeline creates an animation. There need not be a key frame set along each frame of the timeline; only critical positions or timings need to be key-framed. The 3D animation and modeling software will interpolate between the key-framed positions of each control and spine control joint, creating a smooth animation.</li>
</ol>

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Part 1: Navicular bone and related structures.</a> Equine Veterinary Journal. 38 (1), 15-22 (2006).</li><li>Dyson, S., Murray, R. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Magnetic+resonance+imaging+evaluation+of+264+horses+with+foot+pain:+the+podotrochlear+apparatus,+deep+digital+flexor+tendon+and+collateral+ligaments+of+the+interphalangeal+joint.">Magnetic resonance imaging evaluation of 264 horses with foot pain: the podotrochlear apparatus, deep digital flexor tendon and collateral ligaments of the interphalangeal joint.</a> Equine Veterinary Joint. 39 (4), 340-343 (2007).</li><li>Dyson, S., Murray, R. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Use+of+concurrent+scintigraphic+and+magnetic+resonance+imaging+evaluation+to+improve+understanding+of+the+pathogenesis+of+injury+of+the+podotrochlear+apparatus.">Use of concurrent scintigraphic and magnetic resonance imaging evaluation to improve understanding of the pathogenesis of injury of the podotrochlear apparatus.</a> Equine Veterinary Journal. 39 (4), 365-369 (2007).</li><li>Egenvall, A., Lonnell, C., Roepstorff, L. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Analysis+of+morbidity+and+mortality+data+in+riding+school+horses,+with+special+regard+to+locomotor+problems.">Analysis of morbidity and mortality data in riding school horses, with special regard to locomotor problems.</a> Preventive Veterinary Medicine. 88 (3), 193-204 (2009).</li><li>Waguespack, R., Hanson, R. 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The authors have declared no conflicts of interest.

This protocol demonstrates how to create a 3D whole-body skeletal model of an organism and demonstrates how to use the whole-body equine skeletal model described in this paper. The model is currently in a format that requires a specific 3D animation and modeling software, which has quite a learning curve for new users. However, a version of this software is freely available for those who are affiliated with a university. Although modeling whole-body posture and movement is used to assess human athletes and to identify causes of mechanically induced chronic injuries11, it is less commonly done with equine athletes. To use this approach for the assessment of the potential causes of equine athletic injuries and performance issues, a realistic whole-body skeletal equine model was created from CT data using the 3D visualization software and 3D animation and modeling software. This model is different from other equine models that are either artistic graphic recreations of the skeleton (https://www.youtube.com/watch?v=YncZtLaZ6kQ) or that only depict the limbs14,15,16,17.&#160;In this whole-body model, forelimbs, hindlimbs, spine, and ribcage were all rigged and had controls attached that allow for easy manipulation of the model for realistic and accurate positioning and animation.
The protocol used to rig the model allows for repeatability and future alterations to suit the needs of the specific horse being rigged, enabling individualized analysis. Thus, the equine model is a tool to be used by researchers as they analyze movement. However, it is not an automated program that provides answers without the input of parameters specific to the animal being modeled and the question being addressed, as the accuracy of the model is directly related to the strength of a particular analysis. The ability to input parameters also allows the model to be continually updated with data from future research studies. Additionally, this graphic rigging protocol can be applied and/or adjusted to reflect the anatomical differences between individuals. It can also be adapted to effectively model other animals. The 3D equine model can be easily manipulated and positioned to simulate positions and movements. This is especially evident with the limbs as their movements are relatively simple to see and model.
Graphic joint positioning in the model was determined by a similar approach to that used in other studies18,19. The bone meshes were placed in a neutral position. Graphic joints were positioned so that the bones were able to rotate freely without causing any collision with other bone meshes. In the digits, the graphic joint was placed at the point where a sphere coincided with the surfaces of movement. The graphic joint of the scapula was placed in the approximate center of the scapula blade. This positioning of the graphic joint allows it to be moved in 6 degrees of freedom to orient the scapula into the desired position. Unlike the limbs, the movement of the spine is not easily seen, is more complex than often realized, and thus is more difficult to model. Although the model has the flexibility to be used to investigate movements and issues at specific spinal joints, it also needed to be able to represent the often hard-to-distinguish movements of the whole spine. The use of the &#34;ribbon spine&#34; allows for more realistic movement of the spine during animations.
This is important as the spine in horses, as has been found in humans, is often the origin of issues that are potentially related to aberrant biomechanical movements and injury to the limbs. A strength of this model is the ability to accurately demonstrate spine positions, like transversal vertebral rotations20 (Figure 4). How these postures impact the limbs in three dimensions during various gaits can be determined by using the model in combination with kinematic and force analysis (e.g., pressure plate studies to confirm increased loading of the limbs and static force analysis). Soft tissue musculofascial components are currently being added to the whole-body skeletal model. Future goals are to expand the use of the model in 3D biomechanical analysis for studies of equine lameness. Such expansion would include using the model to complete 3D force analyses that compare healthy and unhealthy postures and registering the model with 3D data points collected in motion capture studies to provide a more effective visual representation of movement.

Chronic lameness in horses is often associated with progressive degenerative tissue lesions similar to those of osteoarthritis (OA), a major public health problem in humans1,2,3,4,5,6,7,8,9. In human medicine, because therapeutic approaches focused on treating specific lesions (e.g., pharmacotherapy and direct chondral repair) have mostly failed, pathomechanical forces are now recognized as the root cause of tissue damage in OA. Aberrant or pathomechanical forces impact both bone and cartilage cells directly, inducing the release of inflammatory mediators and progressive tissue degeneration9. These observations indicate that unless the causative mechanical forces are corrected, many chronic degenerative bone and joint diseases will continue to progress. Hence, the therapeutic focus in human medicine is shifting to approaches that &#34;unload&#34; the affected joints through targeted exercise10,11. However, this shift has not yet been made in equine medicine, partly because models for equine motion that can be adapted to show an individual&#39;s movements are needed.
Comprehensive, whole-body biomechanical analysis is common in designing training programs to optimize athletic performance and facilitate injury recovery in human athletes11 (see also e.g., the journal &#34;Sports Biomechanics&#34;), but is less commonly done for equine athletes (but see12). Thus, the overarching goal here is to establish pathomechanical models of equine lameness that can be used to develop individualized preventative and rehabilitative therapies to improve the health of equine athletes. Such pathomechanical models can characterize differences in the functional anatomy of regions (i.e., the spine) that are not as easily discernible to the naked eye as others (i.e., the lower limb). To achieve this goal, the first objective was to develop an anatomically accurate, manipulatable, whole-body, equine&#160;skeletal model that can be used as a template by researchers interested in functional anatomical, kinematic, and kinetic analyses. To be useful to equine clinicians and researchers, this model must (1) be biologically realistic to enable accurate anatomical positioning, (2) allow for easy and accurate adjustments for modeling various postures of healthy and non-healthy horses, (3) be able to be animated to study the effects of various gaits, and (4) facilitate repeatable re-creations of positions and movements.
A 3D graphic&#160;whole-body equine&#160;skeletal model was built from CT data in which the positions of bones relative to each other could be manipulated and then animated to match movements from pictures or videos of a horse in motion, thus creating a 4D equine skeletal model. Depending upon what best fits the question to be addressed, the model can be used in 2D, 3D, and 4D versions or in various combinations to illustrate and characterize the pathomechanical effects of specific positions or postures. Because of its basic and flexible design, the model serves as a template that can be modified by researchers to reflect their specific questions and data parameters. Such parameters include, for example, anatomical information based on sex and animal size, 3D motion analysis data, soft tissue force estimations, and inertial properties. Thus, the model allows for more detailed analysis of specific areas or joints, while also providing the basis to set up experiments that are unable to be performed on living horses. Due to practical limitations related to specimen availability (e.g., the ribs cut) and the scanner, the whole-body equine model is the result of merging data from three equine specimens. Thus, the model is not a perfect representation of a single individual, but has been standardized to represent individual variability more broadly. In short, it is a template to be used and modified to suit the needs of researchers. CT scans of the trunk, head and neck, and limbs were acquired from two equine specimens of approximately the same size with a 64-slice CT scanner using a bone algorithm, pitch of 0.9, 1 mm slice. CT scans of a set of ribs were acquired with a 64-slice CT scanner using a bone algorithm, pitch of 0.9, 0.64 mm slices.
Anatomic integrity of the bony joints (e.g., within the limb) was maintained. The soft tissues available in the CT scans were also used to confirm the placement of the bones. As some whole ribs and the proximal portions of all the ribs were available and scanned on the thorax specimen, the separately scanned ribs could be accurately sized and placed within the whole-body skeletal model. The resulting CT Digital Imaging and Communications in Medicine (DICOM) data were imported into the 3D visualization software (see the Table of Materials), and individual bones were segmented into individual data sets (i.e., bone meshes). The individual 3D bone meshes were then imported into the 3D animation and modeling software (Table of Materials) where they were sized, if necessary, and assembled into a complete equine skeleton in preparation for rigging-a graphic method of connecting the bone meshes so that their movements are linked (Figure 1).

<table><tbody><tr><td>Avizo</td><td>VSG, Visualization Science Group, Inc., Burlington, MA</td><td>N/A</td><td>cited in text as &quot;3D visualization software&quot;</td></tr><tr><td>Maya</td><td>Autodesk, Inc., San Rafael, CA</td><td>N/A</td><td>cited in text as &quot;3D animation and modeling software&quot;; Free student version</td></tr></tbody></table>

construction of a realistic, whole-body, three-dimensional equine skeletal model using computed tomography data

Therapies based upon whole-body biomechanical assessments are successful for injury prevention and rehabilitation in human athletes. Similar approaches have rarely been used to study equine athletic injury. Degenerative osteoarthritis caused by mechanical stress can originate from chronic postural dysfunction, which, because the primary dysfunction is often distant from the site of tissue injury, is best identified through modeling whole-body biomechanics. To characterize whole-body equine kinematics, a realistic skeletal model of a horse was created from equine computed tomography (CT) data that can be used for functional anatomical and biomechanical modeling. Equine CT data were reconstructed into individual three-dimensional (3D) data sets (i.e., bones) using 3D visualization software and assembled into a complete 3D skeletal model. The model was then rigged and animated using 3D animation and modeling software. The resulting 3D skeletal model can be used to characterize equine postures associated with degenerative tissue changes as well as to identify postures that reduce mechanical stress at the sites of tissue injury. In addition, when animated into 4D, the model can be used to demonstrate unhealthy and healthy skeletal movements and can be used to develop preventative and rehabilitative individualized therapies for horses with degenerative lamenesses. Although the model will soon be available for download, it is currently in a format that requires access to the 3D animation and modeling software, which has quite a learning curve for new users. This protocol will guide users in (1) developing such a model for any organism of interest and (2) using this specific equine model for their own research questions.

The result of the method was a 3D full equine skeletal model inside the 3D animation and modeling software that allows for accurate anatomical positioning and movement simulations. The model itself has a graphic rigging system delegated to the forelimbs, hindlimbs, spine, neck, and ribcage. The 3D model could be placed into different postures (Figure 3 and Figure 4) by multiple individuals. The movements of the 4D model (in motion) have been compared to videos from the side, back, and front, as well as with overhead drone footage to more accurately depict the motion of the spine and video of horses at the walk (Video), canter, and trot to create animations of those gaits.
<img alt="Figure 1" class="xfigimg" src="/files/ftp_upload/62276/62276fig01.jpg" /> 
Figure 1: The 3D equine model can be moved into various postures and animated to demonstrate whole-body movements in various gaits in the 3D animation and modeling software. (A,C) Graphic rigging systems for the horse. The graphic ribbon spine that enables natural movement of the bony spine is illustrated by the green plane. The controls used to move the various graphic rigs and the attached bone meshes are illustrated by the yellow ovals and cross arrows on the model. (A) Standing position. (C) Rearing position. (B, D) The model with the bone meshes attached to the graphic rigging system. The positions of the controls change the position of the skeleton of the horse. (B) Standing horse. (D) Rearing horse. <a href="https://www.jove.com/files/ftp_upload/62276/62276fig01large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" class="xfigimg" src="/files/ftp_upload/62276/62276fig02.jpg" /> 
Figure 2: The rigging of each limb with joints allows for positioning and the creation of movement. (A) Forelimb with graphic joints indicated with numbers 1-10. (B) Hindlimb with graphic joints indicated with numbers 11-17. <a href="https://www.jove.com/files/ftp_upload/62276/62276fig02large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 3" class="xfigimg" src="/files/ftp_upload/62276/62276fig03.jpg" /> 
Figure 3: The 3D equine model was matched to classic Muybridge13&#160;photos as proof of concept and to create the first animations. (A) Muybridge photographs of a horse at the walk. (B) The 3D equine model superimposed over the photographs to be used as key frames in the animation. (C) The 3D equine model. <a href="https://www.jove.com/files/ftp_upload/62276/62276fig03large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 4" class="xfigimg" src="/files/ftp_upload/62276/62276fig04.jpg" /> 
Figure 4: The 3D equine model can be moved into various postures (e.g., the transversal rotation of the spine demonstrated here) to understand the relationship of such postures to pathomechanical force regimes and the resulting degeneration of the affected skeletal elements, joints, and soft tissues. (A) A graphic 2D representation of a normal posture of a horse (with rider) using graphically manipulated photographs of an equine skeleton compared to a still image of the 3D equine model with the head and cervical vertebrae hidden to enable the visualization of the thorax. (B) A graphic 2D representation of a horse (with rider) with a transversal rotation of the spine using graphically manipulated photographs of an equine skeleton compared to a still image of the 3D equine model with the head and cervical vertebrae hidden to enable the visualization of the thorax. Note here the effect of the transversal rotation on the skeleton and the limbs of the body. The depicted position would overload the left forelimb, which was supported by the compression and cracking of the left front hoof wall in the living horse. <a href="https://www.jove.com/files/ftp_upload/62276/62276fig04large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
Video. The 4D Horse. Key positions of the skeleton, as matched to the Muybridge13&#160;photos of the horse, have been interpolated to create an animation of the horse at a walk. The movement can be seen from the front, side, top, and back. <a href="https://www.jove.com/files/ftp_upload/62276/4D Horse.mp4" target="_blank">Please click here to download this Video.</a>

Watch this Scientific Journal Video about Construction of a Realistic, Whole-Body, Three-Dimensional Equine Skeletal Model using Computed Tomography Data at JoVE.com

Construction of a Realistic, Whole-Body, Three-Dimensional Equine Skeletal Model using Computed Tomography Data

The purpose of this protocol is to describe the method of creation of a realistic, whole-body, skeletal model of a horse that can be used for functional anatomical and biomechanical modeling to characterize whole-body mechanics.

Therapies based upon whole-body biomechanical assessments are successful for injury prevention and rehabilitation in human athletes. Similar approaches ...

construction-realistic-whole-body-three-dimensional-equine-skeletal

Research

JoVE Journal

Biology

3.1K Views.  Louisiana State University School of Veterinary Medicine. Een realistisch skeletmodel van een paard wordt gemaakt van computertomografiegegevens van paarden die kunnen worden gemanipuleerd om de functionele, anatomische en biomechanische modellering van het hele paardenlichaam te begrijpen. De techniek maakt een snelle en eenvoudige positionering van het model mogelijk om verschillende paardenhoudingen te karakteriseren. Het model kan helpen bij het karakteriseren van paardenhoudingen geassocieerd met degeneratieve weefselziekten en het identificere...

Video: Construction of a Realistic, Whole-Body, Three-Dimensional Equine Skeletal Model using Computed Tomography Data

Bioelectric Analyses of an Osseointegrated Intelligent Implant Design System for Amputees

The projected number of American amputees is expected to rise to 3.6 million by 2050.  Many of these individuals depend on artificial limbs to perform routine activities, but prosthetic suspensions using traditional socket technology can prove to be cumbersome and uncomfortable for a person with limb loss.  Moreover, for those with high proximal amputations, limited residual limb length may prevent exoprosthesis attachment all together. Osseointegrated implant technology is a novel operative procedure which allows firm skeletal attachment between the host bone and an implant. Preliminary results in European amputees with osseointegrated implants have shown improved clinical outcomes by allowing direct transfer of loads to the bone-implant interface.  Despite the apparent advantages of osseointegration over socket technology, the current rehabilitation procedures require long periods of restrictive load bearing prior which may be reduced with expedited skeletal attachment via electrical stimulation.  The goal of the osseointegrated intelligent implant design (OIID) system is to make the implant part of an electrical system to accelerate skeletal attachment and help prevent periprosthetic infection. To determine optimal electrode size and placement, we initiated proof of concept with computational modeling of the electric fields and current densities that arise during electrical stimulation of amputee residual limbs.  In order to provide insure patient safety, subjects with retrospective computed tomography scans were selected and three dimensional reconstructions were created using customized software programs to ensure anatomical accuracy (Seg3D and SCIRun) in an IRB and HIPAA approved study.  These software packages supported the development of patient specific models and allowed for interactive manipulation of electrode position and size. Preliminary results indicate that electric fields and current densities can be generated at the implant interface to achieve the homogenous electric field distributions   required to induce osteoblast migration, enhance skeletal fixation and may help prevent periprosthetic infections.  Based on the electrode configurations experimented with in the model, an external two band configuration will be advocated in the future.

There is a need to develop alternative prosthesis attachment due to limb loss attributed to vascular occlusive diseases and trauma. The goal of the work is to introduce an osseointegrated intelligent implant design system to increase skeletal fixation and reduce periprosthetic infection rates for patients needing osseointegrated technology.

The projected number of American amputees is expected to rise to 3.6 million by 2050.  Many of these individuals depend on artificial limbs to perform ...

Scaled Anatomical Model Creation of Biomedical Tomographic Imaging Data and Associated Labels for Subsequent Sub-surface Laser Engraving (SSLE) of Glass Crystals

Biomedical imaging modalities like computed tomography (CT) and magnetic resonance (MR) provide excellent platforms for collecting three-dimensional data sets of patient or specimen anatomy in clinical or preclinical settings. However, the use of a virtual, on-screen display limits the ability of these tomographic images to fully convey the anatomical information embedded within. One solution is to interface a biomedical imaging data set with 3D printing technology to generate a physical replica. Here we detail a complementary method to visualize tomographic imaging data with a hand-held model: Sub Surface Laser Engraving (SSLE) of crystal glass. SSLE offers several unique benefits including: the facile ability to include anatomical labels, as well as a scale bar; streamlined multipart assembly of complex structures in one medium; high resolution in the X, Y, and Z planes; and semi-transparent shells for visualization of internal anatomical substructures. Here we demonstrate the process of SSLE with CT data sets derived from pre-clinical and clinical sources. This protocol will serve as a powerful and inexpensive new tool with which to visualize complex anatomical structures for scientists and students in a number of educational and research settings.

Scaled Anatomical Model Creation of Biomedical Tomographic Imaging Data and Associated Labels for Subsequent Sub-surface Laser Engraving SSLE of Glass Crystals

A methodology is described herein for representing anatomical imaging data within crystals. We create scaled three-dimensional models of biomedical imaging data for use in Sub-Surface Laser Engraving (SSLE) of crystal glass. This tool offers a useful complement to computational display or three-dimensionally printed models used within clinical or educational settings.

Biomedical imaging modalities like computed tomography (CT) and magnetic resonance (MR) provide excellent platforms for collecting three-dimensional data ...

Bioengineering

Four-Dimensional CT Analysis Using Sequential 3D-3D Registration

Four-dimensional computed tomography (4DCT) provides a series of volume data and visualizes joint motions. However, numerical analysis of 4DCT data remains difficult because segmentation in all volumetric frames is time-consuming. We aimed to analyze joint kinematics using a sequential 3D-3D registration technique to provide the kinematics of the moving bone with respect to the fixed bone semiautomatically using 4DCT DICOM data and existing software. Surface data of the source bones are reconstructed from 3DCT. The trimmed surface data are respectively matched with surface data from the first frame in 4DCT. These trimmed surfaces are sequentially matched until the last frame. These processes provide positional information for target bones in all frames of the 4DCT. Once the coordinate systems of the target bones are decided, translation and rotation angles between any two bones can be calculated. This 4DCT analysis offers advantages in kinematic analyses of complex structures such as carpal or tarsal bones. However, fast or large-scale motions cannot be traced because of motion artifacts.

We analyzed joint kinematics from four-dimensional computed tomography data. The sequential 3D-3D registration method semiautomatically provides the kinematics of the moving bone with respect to the subject bone from four-dimensional computed tomography data.

Four-dimensional computed tomography (4DCT) provides a series of volume data and visualizes joint motions. However, numerical analysis of 4DCT data ...

3D Printing of Preclinical X-ray Computed Tomographic Data Sets

Three-dimensional printing allows for the production of highly detailed objects through a process known as additive manufacturing. Traditional, mold-injection methods to create models or parts have several limitations, the most important of which is a difficulty in making highly complex products in a timely, cost-effective manner.1 However, gradual improvements in three-dimensional printing technology have resulted in both high-end and economy instruments that are now available for the facile production of customized models.2 These printers have the ability to extrude high-resolution objects with enough detail to accurately represent in vivo images generated from a preclinical X-ray CT scanner. With proper data collection, surface rendering, and stereolithographic editing, it is now possible and inexpensive to rapidly produce detailed skeletal and soft tissue structures from X-ray CT data. Even in the early stages of development, the anatomical models produced by three-dimensional printing appeal to both educators and researchers who can utilize the technology to improve visualization proficiency. 3, 4 The real benefits of this method result from the tangible experience a researcher can have with data that cannot be adequately conveyed through a computer screen. The translation of pre-clinical 3D data to a physical object that is an exact copy of the test subject is a powerful tool for visualization and communication, especially for relating imaging research to students, or those in other fields. Here, we provide a detailed method for printing plastic models of bone and organ structures derived from X-ray CT scans utilizing an Albira X-ray CT system in conjunction with PMOD, ImageJ, Meshlab, Netfabb, and ReplicatorG software packages.

Using modern plastic extrusion and printing technologies, it is now possible to quickly and inexpensively produce physical models of X-ray CT data taken in a laboratory. The three -dimensional printing of tomographic data is a powerful visualization, research, and educational tool that may now be accessed by the preclinical imaging community.

Three-dimensional printing allows for the production of highly detailed objects through a process known as additive manufacturing.  Traditional, ...

Three-Dimensional Printing of a Complex Aortic Anomaly

Complex congenital aortic anomalies include diverse types of malformations that may be clinically asymptomatic or present with respiratory or esophageal symptoms. These anomalies may be associated with other congenital heart diseases. It is hard to identify the accurate anatomic vessel location from two-dimensional imaging data, such as computed tomography. As an additive manufacturing method, three-dimensional (3-D) printing can covert the acquired imaging data into 3-D physical models. This protocol describes the procedure for modeling the volumetric DICOM imaging into 3-D data and printing it as an anatomically realistic 3-D model. Using this model, surgeons can identify the vessel location of complex aortic anomalies, which is helpful for pre-operative planning and intra-operative guidance.

Here, we present a protocol to use three dimensional printed models for pre-operative planning and intra-operative reorganization of complicated vascular locations when handling a congenital aortic anomaly.

Complex congenital aortic anomalies include diverse types of malformations that may be clinically asymptomatic or present with respiratory or esophageal ...

Medicine

Development and Evaluation of 3D-Printed Cardiovascular Phantoms for Interventional Planning and Training

Catheter-based interventions are standard treatment options for cardiovascular pathologies. Therefore, patient-specific models could help training physicians&#39; wire-skills as well as improving planning of interventional procedures. The aim of this study was to develop a manufacturing process of patient-specific 3D-printed models for cardiovascular interventions.
To create a 3D-printed elastic phantom, different 3D-printing materials were compared to porcine biological tissues (i.e., aortic tissue) in terms of mechanical characteristics. A fitting material was selected based on comparative tensile tests and specific material thicknesses were defined. Anonymized contrast-enhanced CT-datasets were collected retrospectively. Patient-specific volumetric models were extracted from these datasets and subsequently 3D-printed. A pulsatile flow loop was constructed to simulate the intraluminal blood flow during interventions. Models&#39; suitability for clinical imaging was assessed by x-ray imaging, CT, 4D-MRI and (Doppler) ultrasonography. Contrast medium was used to enhance visibility in x-ray-based imaging. Different catheterization techniques were applied to evaluate the 3D-printed phantoms in physicians&#39; training as well as for pre-interventional therapy planning.
Printed models showed a high printing resolution (~30 &#181;m) and mechanical properties of the chosen material were comparable to physiological biomechanics. Physical and digital models showed high anatomical accuracy when compared to the underlying radiological dataset. Printed models were suitable for ultrasonic imaging as well as standard x-rays. Doppler ultrasonography and 4D-MRI displayed flow patterns and landmark characteristics (i.e., turbulence, wall shear stress) matching native data. In a catheter-based laboratory setting, patient-specific phantoms were easy to catheterize. Therapy planning and training of interventional procedures on challenging anatomies (e.g., congenital heart disease (CHD)) was possible.
Flexible patient-specific cardiovascular phantoms were 3D-printed, and the application of common clinical imaging techniques was possible. This new process is ideal as a training tool for catheter-based (electrophysiological) interventions and can be used in patient-specific therapy planning.

Here we present development of a mock circulation setup for multimodal therapy evaluation, pre-interventional planning, and physician-training on cardiovascular anatomies. With the application of patient-specific tomographic scans, this setup is ideal for therapeutic approaches, training, and education in individualized medicine.

Catheter-based interventions are standard treatment options for cardiovascular pathologies. Therefore, patient-specific models could help training ...

Creation of a High-Fidelity, Low-Cost, Intraosseous Line Placement Task Trainer via 3D Printing

The description of procedural task trainers includes their use as a training tool to hone technical skills through repetition and rehearsal of procedures in a safe environment before ultimately performing the procedure on a patient. Many procedural task trainers available to date suffer from several drawbacks, including unrealistic anatomy and the tendency to develop user-created &#39;landmarks&#39; after the trainer tissue undergoes repeated manipulations, potentially leading to inappropriate psychomotor skill development. To ameliorate these drawbacks, a process was created to produce a high-fidelity procedural task trainer, created from anatomy obtained from computed tomography (CT) scans, that utilize ubiquitous three-dimensional (3D) printing technology and off-the-shelf commodity supplies.
This method includes creating a 3D printed tissue mold capturing the tissue structure surrounding the skeletal element of interest to encase the bony skeletal structure suspended within the tissue, which is also 3D printed. A tissue medium mixture, which approximates tissue in both high-fidelity geometry and tissue density, is then poured into a mold and allowed to set. After a task trainer has been used to practice a procedure, such as intraosseous line placement, the tissue media, molds, and bones are reclaimable and may be reused to create a fresh task trainer, free of puncture sites and manipulation defects, for use in subsequent training sessions.

We describe a procedure to process computed tomography (CT) scans into high-fidelity, reclaimable, and low-cost procedural task trainers. The CT scan identification processes, export, segmentation, modeling, and 3D printing are all described, along with the issues and lessons learned in the process.

The description of procedural task trainers includes their use as a training tool to hone technical skills through repetition and rehearsal of procedures ...

Digital Hybrid Model Preparation for Virtual Planning of Reconstructive Dentoalveolar Surgical Procedures

Virtual, hybrid three-dimensional (3D) model acquisition is presented in this article, utilizing the sequence of radiographic image segmentation, spatial registration, and free-form surface modeling. Firstly cone-beam computed tomography datasets were reconstructed with a semi-automatic segmentation method. Alveolar bone and teeth are separated into different segments, allowing 3D morphology, and localization of periodontal intrabony defects to be assessed. The severity, extent, and morphology of acute and chronic alveolar ridge defects are validated concerning adjacent teeth. On virtual complex tissue models, positions of dental implants can be planned in 3D. Utilizing spatial registration of IOS and CBCT data and subsequent free-form surface modeling, realistic 3D hybrid models can be acquired, visualizing alveolar bone, teeth, and soft tissues. With the superimposition of IOS and CBCT soft tissue, thickness above the edentulous ridge can be assessed about the underlying bone dimensions; therefore, flap design and surgical flap management can be determined, and occasional complications may be avoided.

A workflow for creating three-dimensional (3D) virtual hybrid models has been designed based on cone-beam computed tomography dataset and intraoral optical scans utilizing radiographic image segmentation methods and free-form surface modeling. Digital models are used for the virtual planning of reconstructive dentoalveolar surgical procedures.

Virtual, hybrid three-dimensional (3D) model acquisition is presented in this article, utilizing the sequence of radiographic image segmentation, spatial ...

Four-Dimensional Computed Tomography-Guided Valve Sizing for Transcatheter Pulmonary Valve Replacement

The measurements of the right ventricle (RV) and pulmonary artery (PA), for selecting the optimal prosthesis size for transcatheter pulmonary valve replacement (TPVR), vary considerably. Three-dimensional (3D) computed tomography (CT) imaging for device size prediction is insufficient to assess the displacement of the right ventricular outflow tract (RVOT) and PA, which could increase the risk of stent misplacement and paravalvular leak. The aim of this study is to provide a dynamic model to visualize and quantify the anatomy of the RVOT to PA over the entire cardiac cycle by four-dimensional (4D) cardiac CT reconstruction to obtain an accurate quantitative evaluation of the required valve size. In this pilot study, cardiac CT from sheep J was chosen to illustrate the procedures. 3D cardiac CT was imported into 3D reconstruction software to build a 4D sequence which was divided into eleven frames over the cardiac cycle to visualize the deformation of the heart. Diameter, cross-sectional area, and circumference of five imaging planes at the main PA, sinotubular junction, sinus, basal plane of the pulmonary valve (BPV), and RVOT were measured at each frame in 4D straightened models prior to valve implantation to predict the valve size. Meanwhile, dynamic changes in the RV volume were also measured to evaluate right ventricular ejection fraction (RVEF). 3D measurements at the end of the diastole were obtained for comparison with the 4D measurements. In sheep J, 4D CT measurements from the straightened model resulted in the same choice of valve size for TPVR (30 mm) as 3D measurements. The RVEF of sheep J from pre-CT was 62.1 %. In contrast with 3D CT, the straightened 4D reconstruction model not only enabled accurate prediction for valve size selection for TPVR but also provided an ideal virtual reality, thus presenting a promising method for TPVR and the innovation of TPVR devices.

This study assessed a new methodology with a straightened model generated from the four-dimensional cardiac computed tomography sequence to obtain the desired measurements for valve sizing in the application of transcatheter pulmonary valve replacement.

The measurements of the right ventricle (RV) and pulmonary artery (PA), for selecting the optimal prosthesis size for transcatheter pulmonary valve ...

Three-Dimensional Preoperative Virtual Planning in Derotational Proximal Femoral Osteotomy

Anterior knee pain (AKP) is a common pathology among adolescents and adults. Increased femoral anteversion (FAV) has many clinical manifestations, including AKP. There is growing evidence that increased FAV plays a major role in the genesis of AKP. Furthermore, this same evidence suggests that derotational femoral osteotomy is beneficial for these patients, as good clinical results have been reported. However, this type of surgery is not widely used among orthopedic surgeons.
The first step in attracting orthopedic surgeons to the field of rotational osteotomy is to give them a methodology that simplifies preoperative surgical planning and allows for the previsualization of the results of surgical interventions on computers. To that end, our working group uses 3D technology. The imaging dataset used for surgical planning is based on a CT scan of the patient. This 3D method is open access (OA), meaning it is accessible to any orthopedic surgeon at no economic cost. Furthermore, it not only allows for the quantification of femoral torsion but also for carrying out virtual surgical planning. Interestingly, this 3D technology shows that the magnitude of the intertrochanteric rotational femoral osteotomy does not present a 1:1 relationship with the correction of the deformity. Additionally, this technology allows for the adjustment of the osteotomy so that the relationship between the magnitude of the osteotomy and the correction of the deformity is 1:1. This paper outlines this 3D protocol.

This work presents a detailed surgical planning protocol using 3D technology with free open-source software. This protocol can be used to correctly quantify femoral anteversion and simulate derotational proximal femoral osteotomy for the treatment of anterior knee pain.

Construction of a Realistic, Whole-Body, Three-Dimensional Equine Skeletal Model using Computed Tomography Data

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