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The authors thank students enrolled in Biology of Muscle (UML BIOL4890, 2023&#8211;2025) and students from Lawrence High School (Lawrence, MA) for participating in the capstone project that served as the basis for this honors thesis (GC). Also, thanks to Matthew Borokowski at Aurora Scientific for his enduring support and to Victoria Flint and Samuel DeLap for their initial efforts in developing&#160;and deploying the finger flexor module for the UML course. The authors also thank Daniel Bartlett and Darrell La for assistance with analysis approaches. Funded by a UMass Lowell Honors College fellowship (to GC), and by the National Science Foundation (award 2217246), as well as startup funds from UMass Lowell (to NK).

All experiments forming the basis of this publication were approved by the Institutional Review Board at the University of Massachusetts Lowell (Protocol No. 21-163-KON-XPD).
NOTE: The apparatus uses a smartphone suspended with external loads from a 3D-printed pulley system. Acceleration data are collected at 100 Hz using a smartphone-based data acquisition application. Force is calculated by multiplying the combined mass of the smartphone and external load by acceleration. Velocity is obtained by integrating acceleration, and power is calculated as the product of force and velocity (Supplemental Coding File 1).
1. Apparatus assembly
<ol>
	<li>Attach two short aluminum beams to the underside of one long aluminum beam using aluminum frame fasteners. Position the short beams approximately 8 cm from each end of the long beam to form a stable, noncompliant base. 
	NOTE: This assembly is referred to hereafter as the frame.</li>
	<li>Build the pulley mount
	<ol>
		<li>Position a large cellular polyvinyl chloride block with the 7 in side oriented vertically and the 6.75 in side oriented horizontally.</li>
		<li>Measure 2.75 in from the bottom-left corner along the left edge and mark the location.</li>
		<li>Measure 2.75 in from the top-left corner along the top edge and mark the location.</li>
		<li>Draw a straight line connecting the two marked locations.</li>
		<li>Cut along the marked line and remove the resulting triangular section.</li>
		<li>Drill a 7/16 in hole 1.25 in from the top-right corner.</li>
		<li>Repeat steps 1.2.1–1.2.6 for the second large block.</li>
		<li>Position the small cellular polyvinyl chloride block behind the frame.</li>
		<li>Secure both large blocks to the small block such that they are 8 in apart. Orient the diagonal cuts above the small block and position the drilled holes beyond the edge of the small block.</li>
	</ol>
	</li>
	<li>Clamp the pulley mount securely to the corner of a table or counter. 
	NOTE: Position the mount so that the pulley extends beyond the table edge. This prevents the suspended weights and smartphone from contacting the table legs during contractions.</li>
	<li>Build and attach the armrest
	<ol>
		<li>Cut the 14 in cellular polyvinyl chloride armrest block into three pieces consisting of two 1.5 in sections and one 3.5 in section.</li>
		<li>Cut a 2 in x 1/8 in notch into the top surface of each smaller section, positioning the notch 1 in from the front edge.</li>
		<li>Secure the smaller sections to the underside of the larger section at each end. Align the notches with one another.</li>
		<li>Cover the upper surface of the larger section with hook-and-loop fastener tape.</li>
		<li>Thread the forearm strap through the two notches.</li>
		<li>Attach the armrest to the frame using bolts and drop-in T-nuts. Position the armrest 14 in from the pulley mount with the forearm strap facing away from the pulley.</li>
	</ol>
	</li>
	<li>Insert ball bearings into the grooves of the inner gear and outer gear components (Supplemental File 1).</li>
	<li>Thread 40 cm of timing belt through the lateral slot of the inner gear component. Create a loop with a 2 cm overlap and secure the overlap within the slot.</li>
	<li>Insert the metal axle through the left pulley mount, a stopper, the inner gear component, the force-carry component, the outer gear component, a second stopper, and the right pulley mount. 
	NOTE: Orient the lateral slot of the inner gear toward the frame. Position both stoppers 1 mm from either side of the pulley assembly.</li>
	<li>Install two additional stoppers on the axle, positioning each stopper 1 mm from the pulley mounts to prevent lateral movement.</li>
	<li>Loop 40 cm of multistrand steel wire through the finger brace and secure it with a crimp. Loop the opposite end through Carabiner A and secure it with a second crimp. 
	NOTE: Carabiners A and B are identical and are labeled only for identification during assembly.</li>
	<li>Connect the inner gear component to Carabiner A using the attached timing belt. Secure the overlap with Key A. 
	NOTE: Keys A, B, and C are identical. Additional keys may be printed because they are designed as sacrificial components that fail before other parts of the apparatus are damaged.</li>
	<li>Loop 10 cm of multistrand steel wire around Carabiner A and secure it with a crimp. Loop the opposite end around an aluminum frame fastener, crimp the wire, and secure the fastener to the frame. 
	NOTE: This assembly is referred to hereafter as the safety bolt.</li>
	<li>Create a loop using 40 cm of timing belt with 2 cm overlap and insert the loop into Key B. Loop the opposite end around Carabiner B and secure the overlap using Key C.</li>
	<li>Insert Key B into the largest tier of the outer gear component.</li>
	<li>Attach the smartphone armband holder to Carabiner B using either the armband loop or the headphone-cable openings.</li>
	<li>Suspend the desired starting weight from Carabiner B using a looped and crimped steel wire.</li>
</ol>
2. Data acquisition setup
<ol>
	<li>Install the data acquisition application on a smartphone equipped with an accelerometer.</li>
	<li>Open the Acceleration (without g) module.</li>
	<li>Place the smartphone in the armband holder attached to Carabiner B.</li>
	<li>Collect data according to section 3.</li>
	<li>Export the recorded data as an .xls file. Assign a unique filename corresponding to the participant.</li>
	<li>Transfer the .xls file to a computer with internet access.</li>
	<li>Process the data using Supplemental Coding File 1 
	NOTE: The script computes velocity using forward Euler integration of the measured vertical acceleration (Equation 3). Position is computed using the constant-acceleration kinematic equation (Equation 4). The calculations use raw acceleration values without smoothing or filtering. 
	Equation 3: vi = vi-1 + ai ∆t 
	Equation 4:  <img alt="Equation of motion, showing position update formula, physics, kinematics calculation." src="/files/ftp_upload/71757/71757eq4.jpg" style="margin:auto;" data-altupdatedat="1790654420000" data-alt="Equation 4">
	<ol>
		<li>Install the Supplemental Coding File 1.</li>
		<li>Install Python on the computer used for data processing.</li>
		<li>Open a terminal window and execute: pip install streamlit pandas matplotlib scipy openpyxl xlrd.</li>
		<li>Navigate to the folder containing Supplemental Coding File 1 and execute: streamlit run muscle_velocity_gui.py. 
		NOTE: When using Windows PowerShell, execute: python -m streamlit run muscle_velocity_gui.py. If prompted for an email address, leave the field blank and press Enter.</li>
		<li>Click on Upload and select the exported .xls file.</li>
		<li>Click on Process Data to load and analyze the dataset.</li>
		<li>Review the acceleration, velocity, and position plots generated for the first trial.</li>
		<li>Select the detected peaks corresponding to valid muscle contractions using the checkboxes adjacent to each peak. 
		NOTE: Valid peaks typically occur before the acceleration trace becomes negative and are associated with positive velocity and position values. The automated peak-detection algorithm may incorrectly identify peaks and therefore requires manual verification.</li>
		<li>Adjust peak detection parameters 
		NOTE: If the software does not correctly identify peaks, expand Advanced Tweakables &gt; Peak Detection Parameters and adjust the detection settings.
		<ol>
			<li>Adjust Zero Threshold to define the acceleration range considered stationary. 
			NOTE: Increase this value when acceleration traces contain excessive noise. The threshold is displayed as red reference lines on the acceleration plot. Default value = 0.30. Suggested range = 0.10–5.00.</li>
			<li>Adjust Min Velocity for Peak to define the minimum accepted velocity peak. 
			NOTE: Decrease this value if valid peaks are excluded. The threshold is displayed as the lower green reference line on the velocity plot. Default value = 0.30. Suggested range = 0.10–10.00.</li>
			<li>Adjust Zero Scope to define the minimum number of consecutive near-zero acceleration samples required to identify a stationary period. 
			NOTE: Decrease this value if the velocity and position traces fail to reset. Default value = 10. Suggested range = 3–25.</li>
			<li>Adjust Max Velocity for Peak to define the maximum accepted velocity peak. 
			NOTE: Increase this value if valid peaks exceed the threshold. The threshold is displayed as the upper green reference line on the velocity plot. Default value = 10.00. Suggested range = 10.00–30.00.</li>
			<li>Adjust Min Peak Distance to define the minimum number of samples between detected peaks. 
			NOTE: Default value = 2. Suggested range = 1–10. Modification is generally unnecessary.</li>
			<li>Adjust Min Peak Prominence to define the prominence required for peak detection. 
			NOTE: Lower values increase sensitivity and may identify additional peaks. Default value = 0.10. Suggested range = 0.01–0.90. Modification is generally unnecessary.</li>
		</ol>
		</li>
		<li>After identifying all valid peaks for the current trial, click on Next to advance to the next trial.</li>
		<li>Repeat steps 2.7.7–2.7.10 until all trials have been processed. 
		NOTE: Do not modify the peak-detection parameters after processing the first trial. If parameter changes become necessary, repeat the analysis for all previously processed trials using the updated settings.</li>
		<li>Copy the selected velocity and acceleration data into a spreadsheet for subsequent force–velocity–power analyses.</li>
	</ol>
	</li>
</ol>
3. Experimental protocol 
<ol>
	<li>Secure the participant's forearm to the armrest using the forearm strap. Tighten the strap sufficiently to prevent the forearm from moving forward.</li>
	<li>Place the finger brace on the participant's thumb and tighten the brace securely.</li>
	<li>Remove slack from the pulley system by rotating the pulley through the ratchet mechanism until the timing belt is taut. 
	NOTE: The ratchet mechanism produces an audible click as it advances between positions.</li>
	<li>Slide the safety bolt toward the pulley until the wire connecting the safety bolt and Carabiner A is taut.</li>
	<li>Select two weights of approximately equal mass, each weighing approximately 1.25 kg.</li>
	<li>Fixed testing sequence
	<ol>
		<li>Test the largest tier, the middle tier, and the smallest tier using one weight and the smartphone.</li>
		<li>Test the smallest tier, middle tier, and largest tier using two weights and the smartphone.</li>
		<li>Test the largest tier and smallest tier using only the smartphone. 
		NOTE: Use the same sequence for all participants to minimize fatigue-related bias.</li>
	</ol>
	</li>
	<li>Tap Start Recording in the data acquisition application.</li>
	<li>Instruct the participant to contract the thumb as rapidly and forcefully as possible. 
	NOTE: Participant motivation can substantially affect performance. Provide consistent verbal encouragement throughout testing to promote maximal effort.</li>
	<li>Pause data recording after each trial. Adjust the pulley tier and loading condition according to the sequence established in step 3.6.</li>
	<li>Resume data recording and repeat steps 3.8–3.9 until all eight pulley-tier and loading combinations have been completed.</li>
	<li>Monitor the participant throughout testing and repeat trials affected by excessive arm movement or incomplete effort.</li>
	<li>Review the acceleration trace after each trial. 
	NOTE: Repeat trials that exhibit abnormally low initial acceleration peaks, excessive oscillations, or continued smartphone movement between contractions, as these conditions may compromise data quality.</li>
	<li>Record notes for each trial, including repeated or excluded trials, to facilitate subsequent data analysis.</li>
</ol>
4. Gold-standard ergometer usage
<ol>
	<li>Set up the gold-standard ergometer
	<ol>
		<li>Power on the computer and launch the data acquisition software. Open the dual-mode lever system procedure file.</li>
		<li>Set the force offset to 10 and the length offset to 9 on the lever control unit.</li>
		<li>Power on the dual-mode lever system and the data acquisition unit.</li>
		<li>Verify proper motor operation by gently rotating the lever and confirming the presence of resistance.</li>
		<li>Loop 40 cm of multistrand steel wire through the second hole from the bottom of the lever and secure the wire using a crimp.</li>
		<li>Loop the opposite end of the wire through the finger brace and secure the wire using a crimp.</li>
		<li>Attach the dual-mode lever system to the frame 3 in in front of the armrest.</li>
	</ol>
	</li>
	<li>Secure the participant's forearm to the armrest and position the thumb within the finger brace.</li>
	<li>Slide the participant's arm forward until the thumb reaches maximal flexion and the cable is under light tension.</li>
	<li>Tighten the forearm strap sufficiently to prevent movement of the arm in the forward or lateral directions.</li>
	<li>Configure data acquisition settings
	<ol>
		<li>Open Scan Control Device Dev6.</li>
		<li>Set Number of Samples to 60,000.</li>
		<li>Set Averaging Samples to 1.</li>
		<li>Set Sample Period to 0.0001.</li>
		<li>Set Convert Period to 0.</li>
		<li>Set Post Trigger Samples to 0.</li>
		<li>Set Reference Trigger Source to /Dev6/PFI1.</li>
		<li>Set 2x Type to Digital.</li>
		<li>Set 2x Lever1 to 0.</li>
		<li>Set 2x Lever2 to 0.</li>
		<li>Set Mode to One Shot.</li>
		<li>Set Return Immediately to Off.</li>
		<li>Set Start Trigger to Off.</li>
		<li>Set Trigger Source to /Dev6/PFI0.</li>
		<li>Set Sample Clock to Off.</li>
		<li>Set Clock Source to /Dev6/PFI7.</li>
		<li>Set Convert Clock to Off.</li>
		<li>Set Convert Clock Source to /Dev6/PFI2.</li>
		<li>Select Channel 1 + Channel 2 under Select Channels to Scan.</li>
	</ol>
	 </li>
	<li>Click on Start in Scan Control Device and instruct the participant to contract the thumb as rapidly and forcefully as possible. 
	NOTE: Participant motivation can substantially affect performance. Provide consistent verbal encouragement throughout testing to promote maximal effort.</li>
	<li>Click on GetWaves and save the resulting data using the participant identifier and the current force offset value. 
	NOTE: For the first contraction, the force offset is 10.</li>
	<li>Reduce the force offset by increments of 1.0. 
	NOTE: Example progression: 10.0 &gt; 9.0 &gt; 8.0.</li>
	<li>Repeat steps 4.6–4.8 until the motor provides no noticeable resistance to thumb movement.</li>
	<li>Extract peak force and peak velocity values from each trial using the analysis procedure described in Supplemental Coding File 2.</li>
</ol>

<ol>
	<li>Hill AV. The heat of shortening and the dynamic constants of muscle. Proc R Soc Lond B Biol Sci. 1938;126:136-195.</li>
	<li>Huxley AF. Muscle structure and theories of contraction. Prog Biophys Biophys Chem. 1957;7:255-318.</li>
	<li>Seow CY. Hill&#39;s equation of muscle performance and its hidden insight on molecular mechanisms. J Gen Physiol. 2013;142:561-573.</li>
	<li>Alcazar J, Csapo R, Ara I, Alegre LM. On the shape of the force-velocity relationship in skeletal muscles: the linear, the hyperbolic, and the double-hyperbolic. Front Physiol. 2019;10:769.</li>
	<li>Huxley AF, Simmons RM. Proposed mechanism of force generation in striated muscle. Nature. 1971;233:533-538.</li>
	<li>Judge JL, Cazares VA, Thompson Z, Skidmore LA. Development of low-cost cardiac and skeletal muscle laboratory activities to teach physiology concepts and the scientific method. Adv Physiol Educ. 2020;44:181-187.</li>
	<li>Nelson FE, Gabald&#243;n AM, Roberts TJ. Force-velocity properties of two avian hindlimb muscles. Comp Biochem Physiol A Mol Integr Physiol. 2004;137:711-721.</li>
	<li>Wilkie DR. The relation between force and velocity in human muscle. J Physiol. 1949;110:249-280.</li>
	<li>Marsh RL, Bennett AF. Thermal dependence of contractile properties of skeletal muscle from the lizard Sceloporus occidentalis with comments on methods for fitting and comparing force-velocity curves. J Exp Biol. 1986;126:63-77.</li>
	<li>Medeiros HBO, Fontana HB, Herzog W. A low-cost 2-D sarcomere model to demonstrate titin-related mechanisms for force production. Adv Physiol Educ. 2024;48:92-96.</li>
	<li>Capuano V, Xu L, Estrada Benavides J. Smartphone MEMS accelerometer and gyroscope measurement errors: laboratory testing and analysis of the effects on positioning performance. Sensors. 2023;23:7609.</li>
	<li>Balaram J, et al. Mars Helicopter technology demonstrator [conference presentation]. Presented at: AIAA Atmospheric Flight Mechanics Conference, AIAA SciTech Forum; Kissimmee, FL; 2018. Available from: https://doi.org/10.2514/6.2018-0023</li>
	<li>Marsh RL. How muscles deal with real-world loads: the influence of length trajectory on muscle performance. J Exp Biol. 1999;202:3377-3385.</li>
	<li>Kontra C, Lyons DJ, Fischer SM, Beilock SL. Physical experience enhances science learning. Psychol Sci. 2015;26:737-749.</li>
	<li>Freeman S, et al. Active learning increases student performance in science, engineering, and mathematics. Proc Natl Acad Sci U S A. 2014;111:8410-8415.</li>
</ol>

The authors have no disclosures to declare.

A low-cost apparatus was validated as an alternative to gold-standard ergometers for measuring force–velocity and power–velocity relationships of human muscles in the classroom.
The validation results support the assertion that a low-cost, and therefore more economically and technologically accessible, apparatus can generate measurements that are statistically indistinguishable from those obtained using a gold-standard ergometer. The ability of the low-cost apparatus to generate high-quality f...

Striated muscle is the motor that generates skeletal movement in humans and other animals. Understanding its unique hierarchical composition is complicated by cross-scale factors influencing the generation of force and production of work1,2. Perhaps because of these complexities, muscle function can be an underprioritized component in anatomy and physiology curricula, because educators lack the tools needed to properly showcase the fundamental and most fascinating aspects of muscle function3,4,5,6.
Muscle function has historically been described through several enduring paradigms, none more widely recognized than the force–velocity trade-off first characterized nearly a century ago by Archibald Vivian Hill1,2,3,4,5,6. This fundamental physiological relationship describes the trade-off between muscle contraction velocity and force, whereby isometric or very slow shortening contractions are generally the strongest, producing peak muscle force (Fmax), whereas the fastest isotonic contractions approaching peak muscle velocity (Vmax) are typically the weakest1. When Hill described the force–velocity–power (FVP) relationship in 1938, he introduced a function that still bears his name. The Hill equation (Equation 1) relates the peak force generated during an isometric contraction (with fixed muscle ends) to the peak velocity achieved in the absence of an external load.
Equation 1: (v + b) (F + a) = b (Fmax + a)
where v is shortening velocity, F is muscle force, Fmax is maximum isometric force, and a and b are constants that describe the force–velocity relationship and the energetic properties of muscle shortening1.
Embedded within this fundamental relationship are several key concepts of muscle function represented by five quantitative parameters that define the FVP relationship. The product of instantaneous muscle force and velocity is power, which typically reaches a maximum value (Pmax) at approximately one-third of Vmax7. The velocity at which  Pmax occurs is referred to as the optimal velocity (Vopt), and its location within the range of shortening velocities (from V0 to Vmax) is an important characteristic of the force–velocity and power–velocity relationships. For example, a greater Vopt results in peak power being delivered at a higher shortening velocity. Within the force–velocity relationship itself, peak force (Fmax) and peak velocity (Vmax) are connected by intermediate force–velocity relationships in a curvilinear manner (Figure 5A). Representative force–velocity and power–velocity relationships obtained using the present methodology are shown in Figure 1. The slope of this curve is referred to as the force–velocity curvature, which describes the rate of force decline with increasing velocity. Curvature is defined as a/Fmax8, where a is the thermodynamic constants in the Hill equation that quantifies frictional heat generation by an unloaded shortening muscle1. Curvature influences the position of Vopt on the force–velocity curve and determines how much force a muscle can generate at a given shortening velocity. Curvature has also been described using the muscular power ratio (Equation 2)9. 
Equation 2:  <img alt="Equilibrium equation Pmax/(vmax*Fmax); physics formula; educational use." src="/files/ftp_upload/71757/71757eq2.jpg" style="margin:auto;" data-altupdatedat="1790654420000" data-alt="Equation 2">
where Pmax is the maximum muscle power output, and Vmax and Fmax are the maximum shortening velocity and maximum isometric force, respectively.
The intuitive nature of the force-velocity and power-velocity relationships provides effective entry points when teaching muscle function in the life sciences classroom. The importance of providing students with hands-on opportunities to build a more complete understanding of the FVP relationships is underscored by the fact that hands-on learning has been shown to improve knowledge-retention10. Moreover, experimental learning is known to strengthen the foundation for assessing muscle function, both in a fundamental scientific context and as preparation for occupations in healthcare, including injury prevention, rehabilitation, and physical training.
Traditional instruments for testing muscle physiological properties, such as dual-mode servomotor lever systems, are highly precise and accurate but incur prohibitive costs and therefore pose substantial barriers to implementation in most classroom environments7. To address these limitations and expand opportunities for hands-on learning, a low-cost alternative was developed. The apparatus is built around a 3D-printed pulley incorporating a ratchet-and-pawl gear and uses off-the-shelf slotted aluminum railings, stiff wire, and a caddy-mounted smartphone running a free data acquisition application (Figure 2). A smartphone was selected instead of dedicated acceleration-measurement devices because smartphones are widely available and are typically equipped with accurate and robust accelerometers11. The utility of smartphones as scientific measurement devices has been demonstrated previously, including the incorporation of a commercially available smartphone accelerometer into the inertial measurement unit of the Ingenuity Mars Helicopter12.
While there are a few existing low-cost tools for teaching muscle physiology, they target different concepts: Judge et al.6 developed affordable SpikerBox-based activities for recording muscle electrical activity, and Medeiros et al.10 created a low-cost 2-D sarcomere model to demonstrate titin-related mechanics. However, no existing low-cost tool allows students to directly measure the FVP relationships of a contracting human muscle and generate quantitative, research-comparable data. The present apparatus is intended to fill this gap by delivering gold-standard-validated FVP measurements for under $300.
The present study reports on the construction of a low-cost FVP apparatus with a cross-validation against the industry gold standard. The validation analyses rely on pairwise comparisons of the five recognized FVP summary variables, measured in the same subjects on both apparatuses. The analyses test the hypothesis that both apparatuses generate equivalent force-velocity and power-velocity curves. With successful cross-validation, the low-cost apparatus can democratize classroom studies of muscle physiology and musculoskeletal biomechanics by lowering the financial barrier to apparatus acquisition, whilst maintaining experimental accuracy and thus scientific rigor. It is anticipated that the low-cost apparatus can inspire and enable students and educators in physiology and biomechanics classrooms worldwide who already study and teach muscle anatomy to practically explore one of the most foundational relationships of muscle. By including a hands-on activity for generating physiological measurements, classrooms can achieve multimodal understanding and improved knowledge-retention.

<table><tbody><tr><td>1.25 kg Weights</td><td>NEXO Fitness</td><td>ASIN: B09JHQ6QB8</td><td>Can be substituted with generic weights approx. 1-2 kg&lt;br/&gt; number needed: 2</td></tr><tr><td>3D printer timing belt</td><td>&amp;lrm;3D printer belt 10m</td><td>ASIN: B08974S1CC</td><td>Can be substituted with generic 3D printer timing belts: 2mm Pitch, 6mm Width, made of Rubber and Fiberglass&lt;br/&gt; number needed: 1</td></tr><tr><td>3DPart1 - Inner Gear</td><td>N/A</td><td>N/A</td><td>See Supplemental STLs - Print in ABS&lt;br/&gt; number needed: 1</td></tr><tr><td>3DPart2 - Outer Gear</td><td>N/A</td><td>N/A</td><td>See Supplemental STLs - Print in ABS&lt;br/&gt; number needed: 1</td></tr><tr><td>3DPart3 - Key</td><td>N/A</td><td>N/A</td><td>See Supplemental STLs - Print 3-5x in ABS&lt;br/&gt; number needed: 1</td></tr><tr><td>3DPart4 - Force Carry</td><td>N/A</td><td>N/A</td><td>See Supplemental STLs - Print in PLA&lt;br/&gt; number needed: 1</td></tr><tr><td>Aluminum beam Long</td><td>80/20 inc</td><td>1020</td><td>1 in x 2 in x 32 in&lt;br/&gt; number needed: 1</td></tr><tr><td>Aluminum beam Short</td><td>80/20 inc</td><td>1010</td><td>1 in x 1 in x 12 in&lt;br/&gt; number needed: 2</td></tr><tr><td>Aluminum frame Fastener / Safety Bolt</td><td>80/20 inc</td><td>4108</td><td>&amp;nbsp;number needed: 3</td></tr><tr><td>Arm brace</td><td>&amp;nbsp;FEATOL</td><td>ASIN: B0CGX8QZ3C</td><td>Can be substituted with generic arm brace&lt;br/&gt; number needed: 1</td></tr><tr><td>Arm rest cellular polyvinyl chloride block</td><td>Azek board</td><td>8/4 X Thickness Traditional Only</td><td>14 in x 6 1/2 in x 3/4 in&lt;br/&gt; number needed: 14</td></tr><tr><td>Carabiners</td><td>Rewoalzx</td><td>ASIN:&amp;nbsp; B0FB3VYV3N&amp;nbsp;</td><td>number needed: 2</td></tr><tr><td>Chrome Alloy Steel Ball Bearings</td><td>uxcell</td><td>UXCELL 6900 2RS - ASIN: B07FVX92MJ</td><td>Dimensions: inner diameter 10 mm, outer diameter 22 mm, width 6 mm.&lt;br/&gt; number needed: 1</td></tr><tr><td>Excel/Spreadsheet</td><td>Microsoft</td><td>Excel</td><td>Can be substituted with any spreadsheet software&lt;br/&gt; number needed: 1</td></tr><tr><td>Finger brace</td><td>Sopito</td><td>ASIN:&amp;nbsp; B0B5C6RWR4&amp;nbsp;</td><td>Can be substituted with generic finger brace&lt;br/&gt; number needed: 1</td></tr><tr><td>IGOR 8 PRO</td><td>Wavemetrics.com</td><td>8 PRO</td><td>Used with Aurora Scientific Apparatus and for a/Fmax calculation.&lt;br/&gt; number needed: 1</td></tr><tr><td>Large cellular polyvinyl chloride board</td><td>Azek board</td><td>8/4 X Thickness Traditional Only</td><td>6 3/4 in x 7 in x 3/4 in&lt;br/&gt; number needed: 2</td></tr><tr><td>Metal axle</td><td>Generic</td><td>ASIN: B0CC8T8X77</td><td>Steel Rod 9.97 mm thick, 45 cm long.&lt;br/&gt; number needed: 1</td></tr><tr><td>Multi-strand steel wire&amp;nbsp;</td><td>Catch All Tackle</td><td>ASIN: B00JTWDSQS</td><td>1.4mm diameter #400lb rating&lt;br/&gt; number needed: 2</td></tr><tr><td>Phone holder</td><td>Tribe</td><td>ASIN: B00SXRXUFE</td><td>number needed: 1</td></tr><tr><td>Phyphox app</td><td>Phyphox.org</td><td>N/A</td><td>Download from Apple App Store or Google Play Store&lt;br/&gt; number needed: 1</td></tr><tr><td>Python script</td><td>N/A</td><td>N/A</td><td>Can be downloaded: Supplemental Document 1 muscle_velocity_gui.py&lt;br/&gt; number needed: 1</td></tr><tr><td>Small cellular polyvinyl chloride board</td><td>Azek board</td><td>8/4 X Thickness Traditional Only</td><td>1 in x 3 1/4 in x 3/4 in&lt;br/&gt; number needed: 1</td></tr><tr><td>Smartphone</td><td>Apple</td><td>IPhone 11</td><td>Can be substituted with any Smartphone with an accelerometer&lt;br/&gt; number needed: 1</td></tr><tr><td>Steel wire crimps</td><td>Catch All Tackle</td><td>ASIN: B00JTWDSQS</td><td>#400lb rating&lt;br/&gt; number needed: 6</td></tr><tr><td>Stoppers</td><td>Befenybay</td><td>ASIN: B0B1C6BPKQ</td><td>inner diameter 10 mm, outer diameter 20 mm, width 20 mm&lt;br/&gt; number needed: 2</td></tr></tbody></table>

a low-cost apparatus for measuring muscle force&#8211;velocity relationships

A Low-Cost Apparatus for Measuring Muscle Force&#8211;Velocity Relationships

The relationship between muscle force, contractile velocity, and power represents a nearly century-old paradigm in physiology and a cornerstone of our understanding of musculoskeletal function. However, this paradigm is rarely studied directly in physiology and biomechanics classrooms because of the prohibitive cost of the required equipment. This study sought to design and validate a low-cost apparatus using a 3D-printed pulley system incorporating a ratchet-and-pawl gear that can be easily constructed and configured to collect force&#8211;velocity&#8211;power data from human finger muscles via a smartphone accelerometer using the free Phyphox application. A custom Python script converts raw accelerometer measurements into velocity and power outputs, which are then compared on a subject-by-subject basis with measurements obtained using a gold-standard dual-mode lever system. Pairwise comparisons of five summary variables (peak force, Fmax; peak speed, Vmax; peak power, Pmax; optimal speed, Vopt; and force&#8211;velocity curvature, a/Fmax) revealed no statistically significant differences between force-velocity-power data collected using the two apparatuses (paired t-tests, p &#62; 0.05). Therefore, without a significant reduction in data quality, the inexpensive apparatus offers an accessible, safe, and cost-effective means of teaching and studying biomechanical and physiological principles. This apparatus has the potential to democratize muscle physiology and biomechanics education, particularly in underfunded and resource-limited educational settings worldwide.

Force–velocity and power–velocity data were collected from a sample of undergraduate students (N = 15) using both the gold-standard ergometer and the low-cost apparatus to evaluate the functional outputs of each system under an identical experimental protocol. Individual subject data are shown in Figure 1, and summary data for each apparatus are shown in Figure 3.
The low-cost apparatus was evaluated as a potential classroom substitut...

An accessible, low-cost apparatus for measuring human muscle force&#8211;velocity&#8211;power relationships was developed using inexpensive materials, a 3D-printed gear, a smartphone accelerometer, and Python freeware. Validation against a gold-standard ergometer demonstrated physiologically relevant measurements while providing equitable, hands-on learning opportunities in an undergraduate classroom setting.

The relationship between muscle force, contractile velocity, and power represents a nearly century-old paradigm in physiology and a cornerstone of our ...

a-low-cost-apparatus-for-measuring-muscle-forcevelocity-relationships

Research

JoVE Journal

Biology

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Muscle Velocity Recovery Cycles to Examine Muscle Membrane Properties

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In Vivo Measurement of Hindlimb Dorsiflexor Isometric Torque from Pig

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University of Massachusetts Lowell.  An accessible, low-cost apparatus for measuring human muscle force–velocity–power relationships was developed using inexpensive materials, a 3D-printed gear, a smartphone accelerometer, and Python freeware. Validation against a gold-standard ergometer demonstrated physiologically relevant measurements while providing equitable, hands-on learning opportunities in an undergraduate classroom setting.

A Low-Cost Apparatus for Measuring Muscle Force–Velocity Relationships

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