We are grateful for the significant efforts that the Colorado State University-Pueblo Dept. of Engineering provided in constructing the three-point bending machine and its modification to a convertible three-point bending/compression testing machine. We are especially thankful to Mr. Paul Wallace, machine shop coordinator, for his efforts in planning and carrying out the construction and modification of the machine. Expertise and feedback from Dr. Bahaa Ansaf (Colorado State University-Pueblo, Dept. of Engineering) and Dr. Franziska Sandmeier (Colorado State University-Pueblo, Dept. of Biology) also significantly contributed to this project. The Institute of Cannabis Research Grant at Colorado State University-Pueblo funded the larger project that this experiment was a part of and allowed for the purchase of the mice, reagents, and some of the equipment used.

All experiments and protocols were conducted in compliance with the Guide for the Care and Use of Laboratory Animals from the National Institutes of Health and received approval from the Colorado State University-Pueblo Institutional Animal Care and Use Committee (Protocol Number: 000-000A-021). Detailed procedures for animal care have been previously described5,6. The mice were obtained at three weeks of age as part of a broader study aimed at investigating the effects of a hempseed-supplemented diet on young, growing female C57BL/6 mice (see Table of Materials). From 5 to 29 weeks of age, the mice were raised on one of three diets: control (0% hempseed), 50 g/kg (5%) hempseed, or 150 g/kg (15%) hempseed, with eight mice per group5,6. Throughout the study, mice had ad libitum access to their respective diets and water, were pair-housed in polycarbonate cages, and maintained on a 12 h light:12 h dark cycle (with lights on from 06:00 to 18:00 h). The mice&#39;s weight and health were assessed weekly, and all mice successfully completed the study without developing any adverse health conditions. At twenty-nine weeks of age, the mice were deeply anesthetized using isoflurane gas and euthanized via cervical dislocation5,6. A midline incision was made on the ventral surface from the sternum to the tail, and all intrathoracic, peritoneal, and retroperitoneal organs were removed from the carcasses. The eviscerated carcasses were preserved in 0.9% sodium chloride solution at -70 &#176;C until the time of bone dissection for vertebra testing, which occurred approximately one year later.
1. Conversion of a three-point bending machine to a compression testing machine
<ol>
	<li>Unscrew the crosshead beam attached to the load sensor on the three-point bending machine7 (see Table of Materials) (Figure 1A,B).</li>
	<li>Screw a self-aligning top platen onto the load sensor (see Table of Materials) with threading identical to the crosshead beam (Figure 1C).</li>
	<li>Drill two horizontal holes into each of the lower supports, where the bottom platen will be attached later (Figure 1D).</li>
	<li>Tap threads into the two sides of a stainless-steel bottom platen to align with the drilled holes in the lower supports (Figure 1E).</li>
	<li>Secure the bottom platen to the two lower supports using threaded hex screws and tighten until secure (Figure 1F). 
	&#8203;NOTE: Hex screws must have threads that match the tapped holes on the lower supports and top/bottom platens. The use of a self-aligning top platen may help achieve uniform contact between the top platen and the loading surface, but it is not sufficient given the concavity of the cranial end of vertebral bodies. Further preparation using a loading surface preparation method is required. When constructing a compression testing machine for small animal bones, which are smaller and weaker than many industrial/engineering materials, it is essential to consider the load capacity of the load sensor and the size of the load frame. Additionally, machines should be regularly cleaned and lubricated to ensure accurate results and smooth operation.</li>
</ol>
2. Correcting for the displacement of the compression testing machine
<ol>
	<li>With no test material between the top platen and bottom platen, lower the top platen onto the bottom platen until light contact has been made (~0.3-0.5 N preload force).</li>
	<li>Turn on the machine at a constant lowering speed (~1 mm/min) to begin compression testing. Collect load (N) and displacement (mm) measurements using digital data collection software (see Table of Materials) for data collection of mechanical testing. 
	NOTE: Since no material is&#160;between the top and bottom platen, all displacement observed will be due to displacement of the machine alone (&#916;xmachine) (frame, load cell, platens, couplings, etc.).</li>
	<li>Continue to lower the top platen onto the bottom platen at a constant (i.e., monotonic) speed until forces higher than what will be obtained from all bone samples are reached.</li>
	<li>Repeat steps 2.1 to 2.3 for a total of three times.</li>
	<li>Plot the data for system displacement (&#916;xmachine, mm) vs. applied load (Force, N).</li>
	<li>Fit a regression line of best fit to the data (Figure 2A-D).</li>
	<li>In a spreadsheet with the data from a bone compression test, use the equation provided by the regression analysis to determine the amount of machine displacement (&#916;xmachine) influencing the recorded displacement (&#916;xtotal recorded) for a data point of a mouse lumbar vertebra compression test. 
	NOTE: For example, consider a data point where 18 N of force is applied, and 2.730 mm of displacement has been recorded (&#916;xtotal recorded). According to the example third-order polynomial regression equation (Figure 2D) [&#916;xmachine = (4 &#215; 10-7 x Applied Load3) - (8 &#215; 10-5 x Applied Load2) + (0.0044 x Applied Load)], 0.056 mm of the displacement recorded is due to machine displacement (&#916;xmachine). 
	&#916;xtotal recorded= &#916;xmachine + &#916;xspecimen</li>
	<li>Correct the recorded displacement for the data point. 
	NOTE: For example, consider the example above. If 2.730 mm of displacement is recorded (&#916;xtotal recorded) and machine displacement (&#916;xmachine) accounts for 0.056 mm of the total, then the displacement that the specimen (i.e., bone) of interest underwent (&#916;xspecimen) is 2.664 mm. Thus, 2.664 mm is the actual displacement that the vertebra underwent (&#916;xspecimen) and is the value to be used for load-displacement curve analysis. 
	&#916;xspecimen = &#916;xtotal recorded&#160;- &#916;xmachine</li>
	<li>Repeat steps 2.7-2.8 for every data point collected for every single specimen (bone). 
	NOTE: This step is important because during compression testing, the displacement observed is not only due to displacement of the specimen, but instead, the observed displacement is a combination of machine displacement (&#916;xmachine) (e.g., compression/displacement of the frame, load cell, platens, couplings, etc.) and the specimen (&#916;xspecimen). Thus, for specimens that undergo relatively small amounts of displacement, such as those of a small animal (e.g., mouse), system displacement (&#916;xmachine) can cause large errors. The procedures described here to correct for system displacement were previously reported by Kalidindi and Abusafieh28, who also detail two other methods in addition to the one described here. Some researchers have been noted to use more than one method for determining system displacement17. Each machine may display unique patterns and degrees of system displacement when loads are applied to it. For this reason, the system displacement correction factor must be determined for each machine and will not be the same between any two machines. In contrast to compression testing of a vertebral bone, a large force reduction will not be observed when measuring for system displacement because no material is between the top and bottom platen.</li>
</ol>
3. Dissection of the 5&#160;th lumbar vertebra (L5) from the mouse carcass
<ol>
	<li>Thaw frozen mouse carcass at room temperature, taking care to keep soft tissues and bones hydrated by regularly applying an isotonic solution of 0.9% NaCl.</li>
	<li>Make a small (&#60;0.5 cm) incision in the skin on the dorsal midline near the base of the tail, then extend the cut across each hindlimb and gently pull to remove the pelt from the base of the tail to the head of the animal.</li>
	<li>Cut away the abdominal wall musculature until the vertebral column is easily visible.</li>
	<li>Under a dissecting microscope, visualize the two sacroiliac joints and the cranial end of the sacrum.</li>
	<li>Using a razor blade or scalpel, make a fine cut to separate the last lumbar vertebra (L6) from the cranial end of the sacrum.</li>
	<li>Again, cutting between the intervertebral space, remove L6 and L5 from the vertebral column, setting aside L5 for analysis (Figure 3).</li>
	<li>Inspect the vertebra under a dissecting microscope and remove all soft tissues from the bone, including the intervertebral disc, using mostly gauze pads and gently with forceps where necessary. 
	&#8203;NOTE: In the present study, the L5 was chosen as the vertebra of interest, but other lumbar vertebrae may be chosen for compression testing.</li>
</ol>
4. Preparing L5 vertebra loading surface for uniaxial compression testing using PMMA bone cement embedding method
<ol>
	<li>Using a diamond-cutoff wheel (see Table of Materials) attached to a rotary tool, make a cut at each pedicle to remove the transverse and spinous process (Figure 4). If left attached to the centrum, vertebral processes can result in local contacts with the upper/lower platens at the processes themselves as opposed to a distribution of the load throughout the centrum.</li>
	<li>Gently sand the caudal end of the vertebra using fine 120-grit sandpaper (see Table of Materials) to remove all intervertebral discs, soft tissue, and irregularities.</li>
	<li>Mark the sanded caudal end with a permanent marker for easy identification later.</li>
	<li>Mix the PMMA bone cement according to the manufacturer&#39;s instructions (see Table of Materials).</li>
	<li>With the PMMA bone cement still semi-soft, place a minimal amount onto the cranial (unmarked) end of the vertebra facing up, ensuring that the entire surface is covered while the vertebra sits in a saline bath to keep the bone sample hydrated and cool.</li>
	<li>With the PMMA still semi-soft, position the vertebra on the bottom platen with the caudal (marked) side facing down (Figure 5).</li>
	<li>Turn on the machine to engage the drive gears and slowly lower the top platen onto the vertebra + PMMA bone cement complex until contact is made with the bone cement and minimal force (&#60;0.5 N) is applied to distribute the PMMA evenly on the bone surface. The top platen in a neutral position can be estimated as horizontal and, when pressing onto semi-soft PMMA, will cause the PMMA to fill the concavity on the cranial end of the vertebra and form a flat horizontal surface beneath the top platen.</li>
	<li>With the top platen gently pressing down on the PMMA bone cement, let the sample sit undisturbed until the PMMA bone cement has completely hardened (~10 min per the manufacturer&#39;s instructions for the PMMA bone cement used in the present study). Keep the sample in a saline bath or frequently mist it with saline during this period to keep the sample hydrated and cool.</li>
	<li>Once the PMMA bone cement has completely hardened, compression testing can begin. Collect data for load (i.e., force) (N) and displacement (i.e., deflection) (mm) from the sensors into a spreadsheet in real-time using digital software designed for data collection of mechanical testing (see Table of Materials).</li>
	<li>After baseline data collection for 5 s, applied at a minimal preload force of &#60;0.5 N, begin lowering the top platen onto the sample at a single (i.e., monotonic), pre-determined lowering speed to start the compression test (~1 mm/min).</li>
	<li>Stop collecting data once a large reduction in load (N) has been observed, indicating material failure. 
	&#8203;NOTE: Manufacturer instructions will specify the approximate hardening time for PMMA bone cement. Hardening time for the PMMA bone cement may differ depending on the type of PMMA bone cement used. Follow manufacturer instructions to determine the wait time for PMMA hardening. However, as an indicator that the PMMA bone cement has completely hardened, an additional sample of the PMMA bone cement can be mixed at the same time as the sample that will be placed on the vertebra but kept aside and checked to see if it is still soft or completely hardened. If completely hardened, this can indicate that the PMMA on the bone is also completely hardened without disturbing the bone + PMMA complex. The bone sample must remain well-hydrated and cool throughout the PMMA hardening and testing periods. As little as a few minutes of exposure to dry air can result in changes to the biomechanical properties. Some researchers use compression testing machines equipped with a saline bath19. The compression testing machine did not have a saline bath in the present study. Instead, a fine mist of saline was regularly applied throughout the PMMA hardening period and testing period.</li>
</ol>
5. Analysis of load-displacement curves for L5 vertebra uniaxial compression tests
<ol>
	<li>Copy and paste load (N) and corrected displacement (mm) data from the spreadsheet into a technical graphing and data analysis software (see Table of Materials).</li>
	<li>Generate a graph with load (N) on the y-axis and corrected specimen displacement (&#916;xspecimen, mm) on the x-axis (Figure 6). Do this in the software by first clicking on Windows, New Table, then Do it to make a table. Copy corrected displacement (mm) and load (N) data from the raw data spreadsheet into the new table.</li>
	<li>Next, generate a waveform to represent raw data by clicking on Data, then click on XY Pair to Waveform and select corrected displacement data for the X-Wave and load data for the Y-Wave. Ensure that the correct number of data points is in the &#34;Number of Points&#34; box, name the waveform, then click on Make Waveform. Once a waveform has been made, generate a graph by clicking on Windows, then New Graph, and place the waveform on the Y-axis and &#34;calculated&#34; on the X-axis.</li>
	<li>Use the cursor tool to mark points/regions of interest on the graph for analysis. A few of the points/regions of interest to calculate common whole-bone mechanical properties are mentioned in steps 5.4-5.8 (Figure 6), and include work-to-failure (N x mm), maximum load (N), stiffness (N/mm), yield load (N), and post-yield displacement (mm).</li>
	<li>For calculation of work-to-failure (N x mm), place a cursor (A) at the start of the test and a cursor (B) at the point immediately before the material fails (i.e., at the maximum load reached during the test before a large decrease in load is observed). 
	NOTE: Thus, cursors A-B will bracket the entirety of the test from when the material starts to withstand forces and undergo displacement to the point where the material fails. Work-to-failure (N x mm) can be measured as the total area underneath the curve (i.e., the area underneath the curve between cursors A and B).</li>
	<li>Calculate maximum load (N) as the highest value for the load that is observed during the test (i.e., load at cursor B).</li>
	<li>Calculate the stiffness (N/mm) of the material as the slope of the linear elastic region (i.e., the slope between cursors C and D).</li>
	<li>The yield load (N) is the load at which the load-displacement curve deviates from linearity and enters the plastic region, thus sustaining permanent deformity (i.e., load at point D). Calculate this by measuring the load at cursor D.</li>
	<li>The post-yield displacement (mm) is an indicator of a material&#39;s ductility. Measure this as the displacement between the yield point and the point of material failure (i.e., the displacement between cursors D and B). 
	NOTE: The parameters listed above are only some of the common whole-bone mechanical properties reported. It is not a complete list of all whole-bone mechanical properties that can be obtained from a load-displacement curve. Other whole-bone mechanical property parameters include total displacement (mm), elastic energy absorbed (N x mm), elastic displacement (mm), plastic energy absorbed (N x mm), and plastic displacement (mm), to name a few. Furthermore, tissue-level bone mechanical properties are not listed; these require data transformations using specific anatomical measurements, such as bone diameter. Example code to make the measurements from the load-displacement curve in the software have been listed in Supplementary File 1.</li>
</ol>

Compression Testing of Mouse Vertebra for Determination of Mechanical Strength

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R., Abusafieh, A. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Accurate+characterization+of+machine+compliance+for+simple+compression+testing.">Accurate characterization of machine compliance for simple compression testing.</a> Experimental Mechanics. 37 (2), 210-215 (1997).</li></ol>

The authors declare no conflict of interest.

The goal of the present study was to describe the construction of a convertible three-point bending machine/compression testing machine, as well as the use of a PMMA bone cement embedding method for the preparation of mouse lumbar vertebrae samples before uniaxial compression testing. Descriptive statistics were obtained and reported for the bone samples, which will be useful for comparison in future studies. Some of the most commonly reported whole-bone mechanical properties were analyzed in the present study. However, it&#39;s worth noting that there are several additional whole-bone and tissue-level mechanical properties that were not investigated here.
It remains unclear how the mechanical properties obtained from samples prepared using the embedding method compare to those prepared using the cutting method for mouse lumbar vertebrae. Schumancher17 previously assessed the mechanical properties of rat vertebrae prepared using the two different methods and found that vertebrae prepared using the embedding method had significantly lower stiffness, higher yield displacement, and higher yield strain than samples prepared using the cutting method. Further characterization is needed to understand how the vertebral mechanical properties of mice or other animal models compare when measured using the two different methods of loading surface preparation. It&#39;s expected that some parameters differ between vertebrae prepared using different methods, given that the embedding method adds material to the sample but preserves the end plate, which is an important structure in vertebral fractures in vivo17,27. The addition of bone cement to the cranial end adds height to the sample, whereas cutting the end plates removes height, altering the aspect ratio and thereby changing mechanical properties like stiffness. Furthermore, although PMMA is stiffer than vertebral cancellous bone, it&#39;s possible that the PMMA undergoes displacement, and the extent of this displacement needs further characterization. Additionally, it&#39;s unclear how the results obtained from either the embedding method or cutting method compare to predictions of bone parameters using finite element analysis for mouse vertebrae or how the results vary under different conditions (e.g., lowering speed, different vertebral levels, PMMA compositions). Nonetheless, because all specimens are prepared in a similar manner, this method is appropriate and allows for an easy and cost-effective means of making comparisons between treatment groups in a single study where samples are prepared and tested under similar conditions.
Regarding specimen preparation before compression testing, it&#39;s essential to prepare samples in a reproducible manner. One possible limitation of the method described in the present study is the use of a rotary tool to remove the vertebral processes. Another method to remove the vertebral processes of mouse lumbar vertebrae has been described by Pendleton et al.19, which may allow for more consistent sample preparation. Furthermore, inconsistencies may arise from the application of PMMA bone cement. Therefore, it&#39;s important to apply the bone cement consistently in terms of volume, placement, and hardening time. However, the embedding method may provide a simpler means of achieving consistent sample preparation compared to the cutting method, as it can be challenging to achieve perfectly even, parallel cuts consistently between all samples due to their small size and fragility. Future studies will be needed to assess the precision of results obtained from samples prepared using the embedding vs. cutting method.
As mentioned, further characterization and investigation of the embedding method for specimen preparation of mouse lumbar vertebrae before uniaxial compression testing are needed. Nonetheless, this study demonstrates that such a method can be employed, provides a detailed description of the proposed method, and offers descriptive statistics of the parameters measured from samples prepared using the method. This protocol is valuable to the field due to the current lack of available methodology. Moreover, this method may better mimic the mechanism by which in vivo vertebral fractures occur compared to other methods17,27. The method also has the advantage of overcoming the technical difficulties associated with other currently reported methods, making uniaxial compression testing more feasible in bone research. This is particularly significant because drugs, diets, or other interventions may influence cortical-rich bones (e.g., long bone mid-diaphysis) and trabecular-rich bones (e.g., vertebral bodies) differently, yet three-point bending is the predominant method to assess the mechanical properties of bones13. The combination of three-point bending and uniaxial compression testing can become even more easily achievable through the use of a convertible three-point bending/compression testing machine. Thus, the present study proposes two possible means of making the assessment of both cortical-rich and trabecular-rich bone in the same study more available to researchers, potentially leading to a better understanding of how a given treatment affects different bone types between experimental groups.

Age-related bone changes are widely recognized as problematic due to the increased risk of bone fractures associated with these changes. Bone fractures in humans can lead to chronic pain, reduced mobility, long-term disability, an increased risk of death, and economic burdens1. Common therapies investigated to address the symptoms of age-related bone changes include dietary supplements, hormone treatments, and drugs2,3,4,5,6,7,8,9. Initial investigations of such treatments for human subjects are commonly done using small animal models (e.g., laboratory rats and mice), which possess the two major types of bones found in the human skeleton10. Appendicular long bones, such as the humerus, femur, and tibia, are rich in cortical (i.e., compact) bone, whereas vertebrae are rich in cancellous bone (i.e., woven, spongy, or trabecular bone)4. There is growing knowledge that the mechanisms of bone regulation and signaling pathways differ between cortical bone (e.g., long bone mid-diaphysis) and cancellous bone (e.g., vertebral centrum)2. Because of this, therapies may have differential effects that are bone-specific or even site-specific within the same bone2,3,4.
The application of force to an object (e.g., bone) causes the object to undergo acceleration, deformation, or both, depending on the object&#39;s boundary conditions. When the bone is constrained, an opposite force of equal magnitude resists the acceleration of the bone, and deformation occurs. As the bone sustains deformation, internal resistance called stress is generated, of which there are two basic types: Normal force, in the form of tension or compression, and shear force10. Often, a combination of the basic types of stress is generated, depending on the applied force system10. The strength of a material is its ability to withstand stress without failing. As increasingly larger forces are applied to a material, it eventually undergoes permanent deformation, at which point it is said to have transitioned from an elastic state (i.e., will return to its original shape if the force is removed) to a plastic state (i.e., will not return to its original shape if the force is removed)11. The point at which the transition from an elastic state to a plastic state occurs is called the yield point. As even larger forces are applied to the material beyond the yield point, it increasingly sustains microfractures (i.e., damage) until total fracture occurs; at this point, the material is said to have failed11,12. The fracture of a bone represents a failure at both a structural level and a tissue level10. As an example, the breakage of a vertebral bone happens because not only do multiple trabeculae fail at a structural level, but there&#39;s also a failure of extracellular matrix elements like collagen and hydroxyapatite crystals in an individual trabecula at the tissue level.
The mechanical events leading up to the failure of a material can be measured using a variety of testing methods. Three-point bending is a common method for testing the mechanical properties of long bones from the appendicular skeleton. This method is simple and reproducible, making it the preferred method of biomechanical testing for many researchers13. By lowering a crosshead beam onto the mid-diaphysis of a long bone resting on two lower support beams, this method specifically tests the mechanical properties of the mid-diaphysis region, which is densely organized cortical bone. From load-displacement curves, tensile force effects on elasticity, toughness, force to failure, and the transition from elastic to plastic behavior of bone materials, among other properties, can be determined.
In the second type of bone, referred to as trabecular, spongy, woven, or cancellous bone, bone elements are formed into an array of rods and beams called trabeculae, giving a &#34;spongy&#34; appearance. The main vertebral bodies (i.e., centra) are rich in cancellous bone and are often the sites of age-related compression bone fractures in humans14. Lumbar (i.e., lower back) vertebrae are the largest vertebrae, bear most of the body&#39;s weight, and are the most common site for vertebral fractures15,16. The mechanical properties of vertebral bodies can best be directly assessed using uniaxial compression testing methods since axial compression is the normal force load imposed on vertebral columns in vivo17. Compression of the vertebral bodies in vivo occurs as a result of muscle and ligament contractions, the force of gravity, and ground reaction forces18.
Ex vivo compression testing of small animal vertebra can be difficult due to their small size, irregular shape, and fragility. The shape of vertebral bodies can be estimated as a parallelogram with mild ventral tilt and slight cranial concavity17. This shape presents challenges for achieving uniaxial compression testing ex vivo because, without adequate preparation to the loading surface, compressive forces will be applied to only part of the loading surface, resulting in a &#34;local contact&#34;17,19. This can cause inconsistent results and premature failure19. This is not the case in vivo because the loading surface is surrounded by intervertebral discs at the vertebral joints, which allows the load to be distributed throughout the cranial end plate. The intervertebral disc-cranial end plate complex plays an important role in the application of force throughout the vertebral body and the biomechanics of fracture to the vertebral body14,20. While compression testing is not new to the field of biology, there are limitations in the current methods of mechanical testing of bones. These limitations include the lack of predictor models and simulations for bone mechanics, unique geometric spatial architecture, and even inherent sample-based biological variations21. More importantly, the field is challenged by a lack of standardization between methods and an overall lack of reported methods in the literature22.
There are two methods reported in the literature for the preparation of rodent lumbar vertebrae to achieve uniaxial compression testing: the cutting method and the embedding method17,19,23,24,25,26. The cutting method requires that the vertebral processes, cranial end plate, and caudal end plate are cut from the vertebral body. Pendleton et al.19 have previously reported a detailed method for the use of this method on mouse lumbar vertebrae. This method presents the challenges of achieving perfectly parallel cuts at both the caudal and cranial end plates while also avoiding any damage to the sample. It also has the limitation that the cranial end plate is removed. The cranial end plate contains a dense shell of cortical bone and plays an important role in distributing loads from the intervertebral discs in vivo and is involved in the failure of the bone for in vivo fractures17,20,27. In contrast, the embedding method involves removing the vertebral processes while keeping the cranial end plate of the vertebral body intact. The loading surface is then made approximately horizontal by placing a small amount of bone cement onto the cranial end of the vertebral body. This method has the advantage that it overcomes the technical challenges associated with the cutting method and may better mimic the mechanism of load application and bone failure in vivo due to the preservation of the cranial end plate. This approach has previously been documented in studies involving uniaxial compression testing on rat bones. However, as far as we are aware, it has not been previously documented in the context of smaller mouse lumbar vertebrae17,25,26. The method in question was previously detailed by Chachra et al.25 &#160; and originally used a bone specimen held in between two plates, each with a cylindrical cavity, which was then filled with polymethylmethacrylate (PMMA). The same research group later improved the method where one end is gently sanded (caudal), and the other end has a small spot of bone cement added (cranial)26. This method is an improvement on the previous method because it minimizes the material between the platens and is the focus of this article. Despite the challenges associated with uniaxial vertebral compression testing, it is a method that may provide valuable information regarding the effects of a proposed therapy on bone, especially when paired with three-point bending.
Here, the use of a convertible three-point bending/compression testing machine to allow for easy testing of both long bones and vertebral bodies using a single machine is presented. Furthermore, the use of an embedding method to achieve uniaxial compression testing of mouse lumbar vertebrae is presented. The present study was performed as part of a larger study that aimed to investigate the influences of dietary hempseed supplementation on the properties of skeletal bone in young, growing female C57BL/6 mice5,6. The three-point bending tester was originally constructed by faculty and students in the Engineering Dept. at Colorado State University-Pueblo and used by our research group in three-point bending tests on long bones [rat femur and tibia7 and mouse humerus, femur, and tibia5,6,8,9]. However, its modification and application for use in mouse vertebral body compression testing was&#160;not been explored. The design and construction of the three-point bending machine have been previously described7. This report will focus on methods used to modify the machine for compression testing and to correct for system displacement. Secondly, the embedding method for mouse vertebral body loading surface preparation is described, along with methods for uniaxial compression testing and the analysis of load-displacement data.

<table><tbody><tr><td>120-Grit Sand Paper</td><td>N/A</td><td>N/A</td><td>For removal of caudal end plate soft tissues and irregularities</td></tr><tr><td>24-bit Load Cell Interface</td><td>LoadStar Sensors, Freemont, California, USA</td><td>DQ-1000</td><td>To connect load and displacement sensors to personal coputer</td></tr><tr><td>Base Mouse Diet</td><td>Dyets, Inc, Bethlehem, PA, USA</td><td>AIN-93G</td><td>Diet the mice were fed, without added hempseed</td></tr><tr><td>Diamond Cutoff Wheel w/ Rotary Tool</td><td>Dremel US, Mt. Prospect, Illinois, USA</td><td>F0130200AK</td><td>To remove vertebral proccesses</td></tr><tr><td>Displacement Sensor</td><td>Mitutoyo, Aurora, Illinois, USA</td><td>ID-S112EX</td><td>Displacement sensor with 0.001 mm resolution and 0.00305 mm accuracy</td></tr><tr><td>External Variable Voltage Power Source</td><td>Extech Instruments, Nashua, New Hampshire, USA</td><td>382213</td><td>To provide power to compression testing machine</td></tr><tr><td>Female C57BL/6 Mice</td><td>Charles River Laboratories, Wilmington, Massachusetts, USA</td><td>027 (Strain Code)</td><td>Mouse model used in present study</td></tr><tr><td>Hempseed</td><td>Natera, Pitt Meadows, Canada</td><td>670834012199</td><td>Hempseed added to Base Mouse Diet</td></tr><tr><td>Igor Pro Software (Version 8.04)</td><td>Wave Metrics, Portland, Oregon, USA</td><td>N/A</td><td>Sofware used for load-displacement curve analysis</td></tr><tr><td>iLoad Mini Force Sensor</td><td>LoadStar Sensors, Freemont, California, USA</td><td>MFM-010-050-S</td><td>Load (force) sensor with 1.0% accuracy</td></tr><tr><td>Isotonic (0.9%) Saline Solution</td><td>N/A</td><td>N/A</td><td>To keep bone sampels hydrated</td></tr><tr><td>Leica EZ4 W Miscoscope</td><td>Leica Microsystems, Wetzlar, Germany</td><td>NC1601884</td><td>For bone dissections and vertebral process removal</td></tr><tr><td>Microsoft Excel Software</td><td>Microsoft Corporation, Redmond, Washington, USA</td><td>N/A</td><td>For data transfer from SensorVue software</td></tr><tr><td>PALACOS R Bone Cement</td><td>Hareus Medical, Wehreim, Germany</td><td>00-1112-140-01</td><td>PMMA bone cement for embedding of the loading surface</td></tr><tr><td>Personal Computer</td><td>N/A</td><td>N/A</td><td>For data recording (see 24-bit Load Cell Interface, SensorVue Software, Microsoft Excel Software) and analysis (see Igor Pro Software)</td></tr><tr><td>SensorVue Software</td><td>LoadStar Sensors, Freemont, California, USA</td><td>N/A</td><td>Software used for real-time data collection during compression testing</td></tr><tr><td>Small Animal Dissecting Kit</td><td>N/A</td><td>N/A</td><td>Dissecting scissors, forceps, scalpel, blades, pins, gauze pads</td></tr><tr><td>Stainless Steel Top Platen (Self-Alligning) and Bottom Platen Pair</td><td>N/A</td><td>N/A</td><td>Constructed by Colorado State University-Pueblo Dept. of Engineering</td></tr><tr><td>Three-Point Bending Machine</td><td>N/A</td><td>N/A</td><td>Constructed by Colorado State University-Pueblo Dept. of Engineering. Refer to Sarper et al. (2014) for further details regarding construction</td></tr></tbody></table>

mouse lumbar vertebra uniaxial compression testing with embedding of the loading surface

There is increasing awareness that cortical and cancellous bone differ in regulating and responding to pharmaceutical therapies, hormone therapies, and other treatments for age-related bone loss. Three-point bending is a common method used to assess the influence of a treatment on the mid-diaphysis region of long bones, which is rich in cortical bone. Uniaxial compression testing of mouse vertebrae, though capable of assessing bones rich in cancellous bone, is less commonly performed due to technical challenges. Even less commonly performed is the pairing of three-point bending and compression testing to determine how a treatment may influence a long bone's mid-diaphysis region and a vertebral centrum similarly or differently. Here, we describe two procedures to make compression testing of mouse lumbar vertebrae a less challenging method to perform in parallel with three-point bending: first, a procedure to convert a three-point bending machine into a compression testing machine, and second, an embedding method for preparing a mouse lumbar vertebra loading surface.

With this step-by-step protocol that uses embedding of the L5 loading surface and a convertible three-point bending machine/compression testing machine, it is possible to perform compression testing on mouse lumbar vertebra for inter-group comparisons. A total of twenty-four mouse L5 vertebrae were prepared using the embedding method. Three of the samples, however, were damaged during the removal of the vertebral processes using a diamond cutoff wheel on a rotary tool and, thus, were not tested. Given this, the mechanical properties listed were successfully obtained from twenty-one of twenty-four samples using the embedding method. Specimens were visually inspected after each test, and the PMMA cap sustained no damage in any of the tests. As noted, the mice used in the present study were part of a larger study aiming to determine the effects of dietary hempseed on the bones of young and growing C57BL/6 female mice. Descriptive statistics of five commonly reported whole-bone mechanical properties are offered in Table 1. The load-displacement curves for all twenty-one samples are provided in Figure 7.
<img alt="Figure 1" class="xfigimg" src="/files/ftp_upload/65502/65502fig01.jpg" /> 
Figure 1: The conversion of a three-point bending machine to a compression testing machine. (A) The machine fully equipped to operate as a three-point bending machine with the displacement sensor and load sensor indicated (white arrows). (B) The machine after the crosshead beam has been removed. (C) The machine after a self-aligning top platen has been placed where the crosshead beam was previously placed. (D) The lower support beams with holes drilled into them. (E) The stainless-steel bottom platen with four threaded holes tapped into it, and a screw partially screwed into one of the holes. The other two holes not seen in the photo are on the opposite side. (F) The lower support beams with the bottom platen attached to them by four hex screws. <a href="https://www.jove.com/files/ftp_upload/65502/65502fig01large.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/65502/65502fig02.jpg" /> 
Figure 2: An example system displacement (&#916;xmachine) vs. load plot fitted with a linear (A), logarithmic (B), second-order polynomial (C), and third-order polynomial (D) regression. In this example, the third-order polynomial provides the best fit per R2 value, and its regression is used as the system displacement correction factor. Images represent example data to demonstrate regression fitting and will need to be obtained by researchers for individual machines. <a href="https://www.jove.com/files/ftp_upload/65502/65502fig02large.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/65502/65502fig03.jpg" /> 
Figure 3: Mouse lumbar vertebral column. A mouse lumbar vertebral column under a dissecting microscope before L6 was removed (A), and after L6 had been removed, leaving L5 attached (B). L5 will be subsequently removed and prepared for compression testing.&#160;The white colored bands are the intervertebral discs which were dissected and removed.&#160;<a href="https://www.jove.com/files/ftp_upload/65502/65502fig03large.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/65502/65502fig04.jpg" /> 
Figure 4: Anatomy of L5 vertebra. A representative mouse L5 vertebra in cranial, caudal, dorsal, and ventral views under a dissecting microscope. Important dimensions for the vertebral body include height, dorsoventral width, and lateral width, as shown by the colored lines. The black dashed lines show approximately where cuts are to be made to remove the vertebral processes. <a href="https://www.jove.com/files/ftp_upload/65502/65502fig04large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 5" class="xfigimg" src="/files/ftp_upload/65502/65502fig05.jpg" /> 
Figure 5: Hardening period of PMMA bone cement. An example L5 vertebra with PMMA bone cement (green) placed on the cranial endplate and the top platen lowered onto the PMMA bone cement + bone complex. Once PMMA bone cement has fully hardened, the compression test will begin. The top platen will be further lowered until failure of the material is observed. <a href="https://www.jove.com/files/ftp_upload/65502/65502fig05large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 6" class="xfigimg" src="/files/ftp_upload/65502/65502fig06.jpg" /> 
Figure 6: Mouse vertebral bone compression test load-displacement curve and data analysis. Cursor A marks the start of the compression test. Cursor B marks the point of material failure. Cursor C marks the start of the linear elastic region, whereas cursor D marks the end (i.e., the yield point). The area shaded in light gray is the linear elastic region, where the material will return to its original shape if the load is removed. The area shaded dark gray is the plastic region, where the material has undergone permanent deformity and will not return to its original shape if the load is removed. <a href="https://www.jove.com/files/ftp_upload/65502/65502fig06large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 7" class="xfigimg" src="/files/ftp_upload/65502/65502fig07.jpg" /> 
Figure 7: Load-displacement curves for all twenty-one bone samples. Patterns varied between bones. In general, the greatest variability was in post-yield displacement, with a few (n = 5) of the bones having a relatively small post-yield displacement and others (n = 16) having a relatively large post-yield displacement. <a href="https://www.jove.com/files/ftp_upload/65502/65502fig07large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<table border="1" fo:keep-together.within-page="1" fo:keep-with-next.within-page="always">
	<tbody>
		<tr>
			<td>Group</td>
			<td>Work-to-Failure (N*mm)</td>
			<td>Maximum Load (N)</td>
			<td>Stiffness (N/mm)</td>
			<td>Yield Load (N)</td>
			<td>Post-Yield Displacement (mm)</td>
		</tr>
		<tr>
			<td>CON (n = 7)</td>
			<td>13.43 &#177; 2.44 A,B</td>
			<td>37.93 &#177; 3.28</td>
			<td>109.14 &#177; 11.86</td>
			<td>22.68 &#177; 2.04</td>
			<td>0.34 &#177; 0.06</td>
		</tr>
		<tr>
			<td>5HS (n = 8)</td>
			<td>12.12 &#177; 1.23 A</td>
			<td>33.62 &#177; 2.43</td>
			<td>99.70 &#177; 16.62</td>
			<td>20.88 &#177; 2.69</td>
			<td>0.38 &#177; 0.08</td>
		</tr>
		<tr>
			<td>15HS (n = 6)</td>
			<td>19.55 &#177; 2.13 B</td>
			<td>41.82 &#177; 1.85</td>
			<td>134.58 &#177; 19.73</td>
			<td>28.07 &#177; 3.20</td>
			<td>0.51 &#177; 0.07</td>
		</tr>
		<tr>
			<td>Combined Groups (n = 21)</td>
			<td>14.68 &#177; 1.27</td>
			<td>37.40 &#177; 1.63</td>
			<td>121.82 &#177; 9.43</td>
			<td>23.54 &#177; 1.60</td>
			<td>0.40 &#177; 0.04</td>
		</tr>
	</tbody>
</table>
Table 1: Representative values for commonly reported whole-bone mechanical properties obtained using the loading surface preparation embedding method. Values were obtained using all protocols detailed in the present study. Thus, the values represent those that can be obtained using the methods described here. Values are means &#177; SEM. Groups represent C57BL/6 female mice fed a diet enriched with whole hempseed at concentrations of 0% (CON), 50 g/kg (5%) (5HS), or 150 g/kg (15%) (15HS) from ages 5-29 weeks. For one of the parameters (work-to-failure), it appears that the diet influenced the values per a one-way ANOVA (p &#60; 0.05). Values sharing the same letter superscript are not significantly different (p &#62; 0.05), while values with different letter superscripts are significantly different (p &#60; 0.05), per Tukey-Kramer post hoc analysis.
Supplementary File 1: Example code to obtain whole-bone mechanical properties. <a href="https://www.jove.com/files/ftp_upload/65502/JOVE_Supplementary.zip" target="_blank">Please click here to download this File.</a>

Watch this Scientific Journal Video about Author Spotlight: Enhancing Small Animal Bone Compression Testing for Research at JoVE.com

Author Spotlight: Enhancing Small Animal Bone Compression Testing for Research

In this protocol, two approaches are described to make uniaxial compression testing of mouse lumbar vertebrae more attainable. First, the conversion of a three-point bending machine to a compression testing machine is described. Second, an embedding method for preparing the loading surface that uses bone cement is adapted for mouse lumbar vertebrae.

Mouse Lumbar Vertebra Uniaxial Compression Testing with Embedding of the Loading Surface

There is increasing awareness that cortical and cancellous bone differ in regulating and responding to pharmaceutical therapies, hormone therapies, and ...

mouse-lumbar-vertebra-uniaxial-compression-testing-with-embedding

Research

JoVE Journal

Biology

1.5K Views.  Colorado State University-Pueblo. In this protocol, two approaches are described to make uniaxial compression testing of mouse lumbar vertebrae more attainable. First, the conversion of a three-point bending machine to a compression testing machine is described. Second, an embedding method for preparing the loading surface that uses bone cement is adapted for mouse lumbar vertebrae.

Video: Author Spotlight: Enhancing Small Animal Bone Compression Testing for Research

Mechanical Stimulation of Stem Cells Using Cyclic Uniaxial Strain

The role of mechanical forces in the development and maintenance of biological tissues is well documented, including several mechanically regulated phenomena such as bone remodeling, muscular hypertrophy, and smooth muscle cell plasticity. However, the forces involved are often extremely complex and difficult to monitor and control in vivo. To better investigate the effects of mechanical forces on cells, we have developed an in vitro method for applying uniaxial cyclic tensile strain to adherent cells cultured on elastic membranes. This method utilizes a custom-designed bioreactor with a motorized cam-rotor system to apply the desired force. Here we present a step-by-step video protocol demonstrating how to assemble the various components of each "stretch chamber", including, in this case, a silicone membrane with micropatterned topography to orient the cells with the direction of the strain. We also describe procedures for sterilizing the chambers, seeding cells onto the membrane, latching the chamber into the bioreactor, and adjusting the mechanical parameters (i.e. magnitude and rate of strain). The procedures outlined in this particular protocol are specific for seeding human mesenchymal stem cells onto silicone membranes with 10 &micro;m wide channels oriented parallel to the direction of strain. However, the methods and materials presented in this system are flexible enough to accommodate a number of variations on this theme: strain rate, magnitude, duration, cell type, membrane topography, membrane coating, etc. can all be tailored to the desired application or outcome. This is a robust method for investigating the effects of uniaxial tensile strain applied to cells in vitro.

It is widely understood that mechanical forces in the body can influence cell differentiation and proliferation. Here we present a video protocol demonstrating the use of a custom-built bioreactor for delivering uniaxial cyclic tensile strain to stem cells cultured on flexible micropatterned substrates.

The role of mechanical forces in the development and maintenance of biological tissues is well documented, including several mechanically regulated ...

In situ Compressive Loading and Correlative Noninvasive Imaging of the Bone-periodontal Ligament-tooth Fibrous Joint

This study demonstrates a novel biomechanics testing protocol. The advantage of this protocol includes the use of an in situ loading device coupled to a high resolution X-ray microscope, thus enabling visualization of internal structural elements under simulated physiological loads and wet conditions. Experimental specimens will include intact bone-periodontal ligament (PDL)-tooth fibrous joints. Results will illustrate three important features of the protocol as they can be applied to organ level biomechanics: 1) reactionary force vs. displacement: tooth displacement within the alveolar socket and its reactionary response to loading, 2) three-dimensional (3D) spatial configuration and morphometrics: geometric relationship of the tooth with the alveolar socket, and 3) changes in readouts 1 and 2 due to a change in loading axis, i.e. from concentric to eccentric loads. Efficacy of the proposed protocol will be evaluated by coupling mechanical testing readouts to 3D morphometrics and overall biomechanics of the joint. In addition, this technique will emphasize on the need to equilibrate experimental conditions, specifically reactionary loads prior to acquiring tomograms of fibrous joints. It should be noted that the proposed protocol is limited to testing specimens under ex vivo conditions, and that use of contrast agents to visualize soft tissue mechanical response could lead to erroneous conclusions about tissue and organ-level biomechanics.

In situ Compressive Loading and Correlative Noninvasive Imaging of the Bone-periodontal Ligament-tooth Fibrous Joint

In this study, the use of an in situ loading device coupled with micro-X-ray computed tomography for fibrous joint biomechanics will be discussed. Experimental readouts identifiable with an overall change in joint biomechanics will include: 1) reactionary force vs. displacement, i.e. tooth displacement within the alveolar socket and its reactionary response to loading, 2) three-dimensional (3D) spatial configuration and morphometrics, i.e.&#160;geometric relationship of the tooth with the alveolar socket, and 3) changes in readouts 1 and 2 due to a change in loading axis, i.e. concentric or eccentric loads.

This study demonstrates a novel biomechanics testing protocol. The advantage of this protocol includes the use of an in situ loading device coupled to a ...

Bioengineering

Application of Design Aspects in Uniaxial Loading Machine Development

In terms of accurate and precise mechanical testing, machines run the continuum. Whereas commercial platforms offer excellent accuracy, they can be cost-prohibitive, often priced in the $100,000 - $200,000 price range. At the other extreme are stand-alone manual devices that often lack repeatability and accuracy (e.g., a manual crank device). However, if a single use is indicated, it is over-engineering to design and machine something overly elaborate. Nonetheless, there are occasions where machines are designed and built in-house to accomplish a motion not attainable with the existing machines in the laboratory. Described in detail here is one such device. It is a loading platform that enables pure uniaxial loading. Standard loading machines typically are biaxial in that linear loading occurs along the axis and rotary loading occurs about the axis. During testing with these machines, a load is applied to one end of the specimen while the other end remains fixed. These systems are not capable of conducting pure axial testing in which tension/compression is applied equally to the specimen ends. The platform developed in this paper enables the equal and opposite loading of specimens. While it can be used for compression, here the focus is on its use in pure tensile loading. The device incorporates commercial load cells and actuators (movers) and, as is the case with machines built in-house, a frame is machined to hold the commercial parts and fixtures for testing.

Here we present a protocol to develop a pure uniaxial loading machine. Critical design aspects are employed to ensure accurate and reproducible testing results.

In terms of accurate and precise mechanical testing, machines run the continuum. Whereas commercial platforms offer excellent accuracy, they can be ...

Engineering

An In Vitro Organ Culture Model of the Murine Intervertebral Disc

Intervertebral disc (IVD) degeneration is a significant contributor to low back pain. The IVD is a fibrocartilaginous joint that serves to transmit and dampen loads in the spine. The IVD consists of a proteoglycan-rich nucleus pulposus (NP) and a collagen-rich annulus fibrosis (AF) sandwiched by cartilaginous end-plates. Together with the adjacent vertebrae, the vertebrae-IVD structure forms a functional spine unit (FSU). These microstructures contain unique cell types as well as unique extracellular matrices. Whole organ culture of the FSU preserves the native extracellular matrix, cell differentiation phenotypes, and cellular-matrix interactions. Thus, organ culture techniques are particularly useful for investigating the complex biological mechanisms of the IVD. Here, we describe a high-throughput approach for culturing whole lumbar mouse FSUs that provides an ideal platform for studying disease mechanisms and therapies for the IVD. Furthermore, we describe several applications that utilize this organ culture method to conduct further studies including contrast-enhanced microCT imaging and three-dimensional high-resolution finite element modeling of the IVD.

An In Vitro Organ Culture Model of the Murine Intervertebral Disc

Whole organ culture of the intervertebral disc (IVD) preserves the native extracellular matrix, cell phenotypes, and cellular-matrix interactions. Here we describe an IVD culture system using mouse lumbar and caudal IVDs in their functional spinal units and several applications utilizing this system.

Intervertebral disc (IVD) degeneration is a significant contributor to low back pain. The IVD is a fibrocartilaginous joint that serves to transmit and ...

Imaging of the Microstructural Failure Mechanism in the Human Hip

Imaging the bone microstructure under progressively increasing loads allows for observing the microstructural failure behavior of bone. Here, we describe a protocol for obtaining a sequence of three-dimensional microstructural images of the entire proximal femur under progressively increasing deformation, causing clinically relevant fractures of the femoral neck. The protocol is demonstrated using four femora from female donors aged 66-80 years at the lower end of bone mineral density in the population (T-score range = &#8722;2.09 to &#8722;4.75). A radio-transparent compressive stage was designed for loading the specimens replicating a one-leg stance, while recording the applied load during&#160;micro-computed tomography (micro-CT) imaging. The field of view was 146 mm wide and 132 mm high, and the isotropic pixel size was 0.03 mm. The force increment was based on finite-element predictions of the fracture load. The compressive stage was used to apply the displacement to the specimen and enact the prescribed force increments. Sub-capital fractures due to opening and shear of the femoral neck occurred after four to five load increments. The micro-CT&#160;images and the reaction force measurements were processed to study the bone strain and energy absorption capacity. Instability of the cortex appeared at the early loading steps. The subchondral bone in the femoral head displayed large deformations reaching 16% before&#160;fracture, and a progressive increase in the support capacity up to&#160;fracture. The deformation energy linearly increased with the displacement up to&#160;fracture, while the stiffness decreased to near-zero values immediately before&#160;fracture. Three-fourths of the fracture energy was taken by the specimen during the final 25% force increment. In conclusion, the protocol developed revealed a remarkable energy absorption capacity, or damage tolerance, and a synergic interaction between the cortical and trabecular bone at an advanced donor age.

The protocol enables the measurement of the deformation of the bone microstructure in the entire proximal human femur and its toughness by combining large-volume micro-CT scanning, a custom-made compressive stage, and advanced image processing tools.

Imaging the bone microstructure under progressively increasing loads allows for observing the microstructural failure behavior of bone. Here, we describe ...

A Millimeter Scale Flexural Testing System for Measuring the Mechanical Properties of Marine Sponge Spicules

Many load bearing biological structures (LBBSs)&#8212;such as feather rachises and spicules&#8212;are small (&#60;1 mm) but not microscopic. Measuring the flexural behavior of these LBBSs is important for understanding the origins of their remarkable mechanical functions.
We describe a protocol for performing three-point bending tests using a custom-built mechanical testing device that can measure forces ranging from 10-5 to 101 N and displacements ranging from 10-7 to 10-2 m. The primary advantage of this mechanical testing device is that the force and displacement capacities can be easily adjusted for different LBBSs. The device&#39;s operating principle is similar to that of an atomic force microscope. Namely, force is applied to the LBBS by a load point that is attached to the end of a cantilever. The load point displacement is measured by a fiber optic displacement sensor and converted into a force using the measured cantilever stiffness. The device&#39;s force range can be adjusted by using cantilevers of different stiffnesses.
The device&#39;s capabilities are demonstrated by performing three-point bending tests on the skeletal elements of the marine sponge Euplectella aspergillum. The skeletal elements&#8212;known as spicules&#8212;are silica fibers that are approximately 50 &#181;m in diameter. We describe the procedures for calibrating the mechanical testing device, mounting the spicules on a three-point bending fixture with a &#8776;1.3 mm span, and performing a bending test. The force applied to the spicule and its deflection at the location of the applied force are measured.

We present a protocol for performing three-point bending tests on sub-millimeter scale fibers using a custom-built mechanical testing device. The device can measure forces ranging from 20 &#181;N up to 10 N and can therefore accommodate a variety of fiber sizes.

Many load bearing biological structures (LBBSs)&#8212;such as feather rachises and spicules&#8212;are small (&#60;1 mm) but not microscopic. Measuring the ...

Cantilever Bending of Murine Femoral Necks

Fractures in the femoral neck are a common occurrence in individuals with osteoporosis. Many mouse models have been developed to assess disease states and therapies, with biomechanical testing as a primary outcome measure. However, traditional biomechanical testing focuses on torsion or bending tests applied to the midshaft of the long bones. This is not typically the site of high-risk fractures in osteoporotic individuals. Therefore, a biomechanical testing protocol was developed that tests the femoral necks of murine femurs in cantilever bending loading to replicate better the types of fractures experienced by osteoporosis patients. Since the biomechanical outcomes are highly dependent on the flexural loading direction relative to the femoral neck, 3D printed guides were created to maintain a femoral shaft at an angle of 20&#176; relative to the loading direction. The new protocol streamlined the testing by reducing variability in alignment (21.6&#176; &plusmn; 1.5&#176;, COV = 7.1%, n = 20) and improved reproducibility in the measured biomechanical outcomes (average COV = 26.7%). The new approach using the 3D printed guides for reliable specimen alignment improves rigor and reproducibility by reducing the measurement errors due to specimen misalignment, which should minimize sample sizes in mouse studies of osteoporosis.

The present protocol describes the development of a reproducible testing platform for murine femoral necks in a cantilever bending set-up. Custom 3D printed guides were used to consistently and rigidly fix the femurs in optimal alignment.

Fractures in the femoral neck are a common occurrence in individuals with osteoporosis. Many mouse models have been developed to assess disease states and ...

Development of a Uterosacral Ligament Suspension Rat Model

Pelvic organ prolapse (POP) is a common pelvic floor disorder (PFD) with the potential to significantly impact a woman's quality of life. Approximately 10%-20% of women undergo pelvic floor repair surgery to treat prolapse in the United States. PFD cases result in an overall $26.3 billion annual cost in the United States alone. This multifactorial condition has a negative impact on the quality of life and yet the treatment options have only dwindled in the recent past. One common surgical option is uterosacral ligament suspension (USLS), which is typically performed by affixing the vaginal vault to the uterosacral ligament in the pelvis. This repair has a lower incidence of complications compared to those with mesh augmentation, but is notable for a relatively high failure rate of up to 40%. Considering the lack of standard animal models to study pelvic floor dysfunction, there is an urgent clinical need for innovation in this field with a focus on developing cost-effective and accessible animal models. In this manuscript, we describe a rat model of USLS involving a complete hysterectomy followed by fixation of the remaining vaginal vault to the uterosacral ligament. The goal of this model is to mimic the procedure performed on women to be able to use the model to then investigate reparative strategies that improve the mechanical integrity of the ligament attachment. Importantly, we also describe the development of an in situ tensile testing procedure to characterize interface integrity at chosen time points following surgical intervention. Overall, this model will be a useful tool for future studies that investigate treatment options for POP repair via USLS.

Pelvic organ prolapse affects millions of women worldwide and yet some common surgical interventions have failure rates as high as 40%. The lack of standard animal models to investigate this condition impedes progress. We propose the following protocol as a model for uterosacral ligament suspension and in vivo tensile testing.

Pelvic organ prolapse (POP) is a common pelvic floor disorder (PFD) with the potential to significantly impact a woman's quality of life. Approximately ...

Medicine

Biomechanical Analysis of Adjacent Segments after Spinal Fusion Surgery Using a Geometrically Parametric Patient-Specific Finite Element Model

This study aimed to perform a mechanical analysis of adjacent segments after spinal fusion surgery using a geometrically parametric patient-specific finite element model to elucidate the mechanism of adjacent segment degeneration (ASD), thereby providing theoretical evidence for early disease prevention. Fourteen parameters based on patient-specific spinal geometry were extracted from a patient's preoperative computed tomography (CT) scan, and the relative positions of each spinal segment were determined using the image match method. A preoperative patient-specific model of the spine was established through the above method. The postoperative model after L4-L5 posterior lumbar interbody fusion (PLIF) surgery was constructed using the same method except that the lamina and intervertebral disc were removed, and a cage, 4 pedicle screws, and 2 connecting rods were inserted. Range of motion (ROM) and stress changes were determined by comparing the values of each anatomical structure between the preoperative and postoperative models. The overall ROM of the lumbar spine decreased after fusion, while the ROM, stress in the facet joints, and stress in the intervertebral disc of adjacent segments all increased. An analysis of the stress distribution in the annulus fibrosus, nucleus pulposus, and facet joints also showed that not only was the maximum stress in these tissues elevated, but the areas of moderate-to-high stress were also expanded. During torsion, the stress in the facet joints and annulus fibrosus of the proximal adjacent segment (L3-L4) increased to a larger extent than that in the distal adjacent segment (L5-S1). While fusion surgery causes an overall restriction of motion in the lumbar spine, it also causes more load sharing by the adjacent segments to compensate for the fused segment, thus increasing the risk of ASD. The proximal adjacent segment is more prone to degeneration than the distal adjacent segment after spinal fusion due to the significant increase in stress.

Here, we used a patient-specific finite element model to analyze the mechanical changes in adjacent segments after spinal fusion surgery. The results showed that fusion surgery reduced the overall motion of the lumbar spine but increased the load on and stress in adjacent segments, especially the proximal segment.

This study aimed to perform a mechanical analysis of adjacent segments after spinal fusion surgery using a geometrically parametric patient-specific ...

A Mouse Model of Lumbar Spine Instability

Intervertebral disc degeneration (IDD) is a common pathological change leading to low back pain. Appropriate animal models are desired for understanding the pathological processes and evaluating new drugs. Here, we introduced a surgically induced lumbar spine instability (LSI) mouse model that develops IDD starting from 1 week post operation. In detail, the mouse under anesthesia was operated by low back skin incision, L3&#8211;L5 spinous processes exposure, detachment of paraspinous muscles, resection of processes and ligaments, and skin closure. L4&#8211;L5 IVDs were chosen for the observation. The LSI model develops lumbar IDD by porosity and hypertrophy in endplates at an early stage, decrease in intervertebral disc volume, shrinkage in nucleus pulposus at an intermediate stage, and bone loss in lumbar vertebrae (L5) at a later stage. The LSI mouse model has the advantages of strong operability, no requirement of special equipment, reproducibility, inexpensive, and relatively short period of IDD development. However, LSI operation is still a trauma that causes inflammation within the first week post operation. Thus, this animal model is suitable for study of lumbar IDD.

We developed a lumbar intervertebral disc degeneration mouse model by resection of L3&#8211;L5 spinous processes along with supra- and inter-spinous ligaments and detachment of paraspinous muscles.

Intervertebral disc degeneration (IDD) is a common pathological change leading to low back pain. Appropriate animal models are desired for understanding ...

Mouse Lumbar Vertebra Uniaxial Compression Testing with Embedding of the Loading Surface

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Mechanical Stimulation of Stem Cells Using Cyclic Uniaxial Strain

In situ Compressive Loading and Correlative Noninvasive Imaging of the Bone-periodontal Ligament-tooth Fibrous Joint

Application of Design Aspects in Uniaxial Loading Machine Development

An In Vitro Organ Culture Model of the Murine Intervertebral Disc

Imaging of the Microstructural Failure Mechanism in the Human Hip

A Millimeter Scale Flexural Testing System for Measuring the Mechanical Properties of Marine Sponge Spicules

Cantilever Bending of Murine Femoral Necks

Development of a Uterosacral Ligament Suspension Rat Model

Biomechanical Analysis of Adjacent Segments after Spinal Fusion Surgery Using a Geometrically Parametric Patient-Specific Finite Element Model

A Mouse Model of Lumbar Spine Instability