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Potential regenerative rehabilitation technology: implications of mechanical stimuli to tissue health



Mechanical loads induced through muscle contraction, vibration, or compressive forces are thought to modulate tissue plasticity. With the emergence of regenerative medicine, there is a need to understand the optimal mechanical environment (vibration, load, or muscle force) that promotes cellular health. To our knowledge no mechanical system has been proposed to deliver these isolated mechanical stimuli in human tissue. We present the design, performance, and utilization of a new technology that may be used to study localized mechanical stimuli on human tissues. A servo-controlled vibration and limb loading system were developed and integrated into a single instrument to deliver vibration, compression, or muscle contractile loads to a single limb (tibia) in humans. The accuracy, repeatability, transmissibility, and safety of the mechanical delivery system were evaluated on eight individuals with spinal cord injury (SCI).


The limb loading system was linear, repeatable, and accurate to less than 5, 1, and 1 percent of full scale, respectively, and transmissibility was excellent. The between session tests on individuals with spinal cord injury (SCI) showed high intra-class correlations (>0.9).


All tests supported that therapeutic loads can be delivered to a lower limb (tibia) in a safe, accurate, and measureable manner. Future collaborations between engineers and cellular physiologists will be important as research programs strive to determine the optimal mechanical environment for developing cells and tissues in humans.


Vibration and compressive loads are mechanical stimuli that have a powerful influence on biological tissues. Recent studies in animal models demonstrate that certain types of mechanical load regulates bone [1], fat [2, 3], skeletal muscle [4, 5], and nerve tissues [6]. In addition, it is also well known that “over exposure” to mechanical stimuli is damaging to tissues [79]. With the emergence of regenerative medicine in tissue repair, rehabilitation specialists must understand the correct type and dose of mechanical stress that promotes cell survival and cell proliferation in bone, cartilage, ligaments, and muscle. However, to our knowledge, there is no technology that directs specific types of mechanical stimuli to limbs of humans. A method to study mechanical stimuli in humans is necessary to guide future research to determine optimal rehabilitation prescriptions. The importance is underscored as multi-potent adult stem cells are harvested and implanted after surgery, injury, disease, and paralysis as regenerative medicine advances. Our long term goal is to establish the extent to which various types of mechanical stimuli optimally influence the regenerative capacity of cells in humans. In this technological report, we present an innovative technology that may assist in determining the impact of mechanical stimuli of human tissues and discuss the importance of a partnership between engineers, bioscience researchers, and rehabilitation specialists.

The underlying need to study the value of therapeutic stress in humans is well grounded in the literature. For example, Wolff’s law supports that bone tissue (osteocytes) exposed to high loads triggers osteogenesis [10]. Subsequent studies verified that exerting high strain in a dynamic fashion to bone tissue was more effective than delivering a sustained strain [11, 12]. For many years, the dynamic delivery of high stress to bone was considered the primary mechanical method to up-regulate osteogenesis [1315]. However, more recently, low amplitude vibration stimuli, in the absence of high mechanical loads, were equally effective at up-regulating bone development in mice [5, 1619]. Indeed, regular mechanical stress promotes a healthy environment for bone [1], fat [2, 3], skeletal muscle [4, 5], nerve tissue [6], and cartilage (articular, menisci) [20, 21] in animal or reduced preparations in the laboratory. Translating these findings into human studies has been hampered by the lack of a capacity to dynamically deliver high passive loads and/or low vibration either independently or in various combinations with or without muscle activation (electrically or volitionally).

The dose of various mechanical loads has not been carefully examined. For example, most studies evaluating vibration deliver the load to the entire animal [5, 16, 19, 2224] or human [2530] which limits the ability to understand adaptive effects of localized vibration directly on tissues (muscle and bone). This point was emphasized when whole body vibration of mice had a systemic increase in bone density [5, 18, 19] and decrease in whole body adipogenesis [3]. The direct effect of the vibration stimuli on bone tissue was confounded by vestibular [31] and/or endocrine system [32] mechanical activation.

The purpose of this technological report is to present a novel method to introduce localized compressive loads and/or vibration into the limbs of humans. The accuracy, repeatability, transmissibility and safety of the instrument will be presented in this report. Future studies are recommended using technology that will assist in better understanding the impact of mechanical stimuli on tissue health. The need for collaborative and inter-disciplinary teams of engineers and cellular physiologists will be emphasized.


Technology development and testing study subjects

Eight individuals with complete paralysis were tested on two occasions to determine the ability to reliably and accurately deliver the mechanical oscillations and loads to the limb of people with spinal cord injury (SCI). A power analysis revealed that 8 participants were required to have power to assess the reproducibility of the system (>80%). Informed written consent was obtained from all subjects prior to participation. All experimental protocols were approved by the University of Iowa Institutional Review Board.

General description of instrumentation

A servo-controlled vibration system (Figure 1) consists of five primary components from the Ling Dynamic Systems (Royston, England): PA1000L power amplifier, FPS10L field power supply, V722 shaker, cooling fan, and Laser USB 6.30 controller. The power amplifier and field power supply are connected in cascade and generate the required power for the vibration system. A magnetic field within the shaker is generated from the field power supply while the power amplifier drives the shaker and supplies power to the cooling fan. The cooling fan dissipates the heat generated. An accelerometer is attached to the shaker and connected to the controller, which is directed to the amplifier creating a feedback loop. The vibration frequency in Hertz (Hz) and acceleration in gravitational force of earth (g = 9.81 m/s2), respectively, are controlled. The software also allows the user to program multiple loops thereby creating a series of on and off cycles of vibration. The controller is also equipped with an abort button designed to stop the vibration quickly. When providing a mechanical intervention to humans it is important to have built in safety mechanisms in the event of an emergency.We interfaced a custom designed, pneumatically controlled piston that can safely deliver compressive loads to a limb segment either with our without the vibration (Figure 2). The mechanical loading system is driven by a pneumatic compression pump that is controlled by a custom circuit board communicating via the computer interface board. Custom software allows for parameter specification, feedback control, and safety shut down when unwanted loads are inadvertently applied.

Figure 1
figure 1

Schematic of the vibration system. The power amplifier and field power supply generate power for the system and supply the shaker and the cooling fan. An accelerometer is attached to the shaker and controller creating a feedback loop to control the frequency and magnitude of vibration.

Figure 2
figure 2

Schematic of the compression system. The mechanical portion consists of a series of hardware components which regulate the amount of air pressure delivered to the air cylinder and subsequently the load applied to the human tibia. The electrical system provides power to many of the mechanical components and links them to the data acquisition (DAQ) board. The personal computer (PC) and the DAQ board control the compression system and allow the user to program the compressive system.

The air flow to the limb loading piston begins at the air compressor, a Super Silent DR 500 Air Compressor (Silentaire Technology, Houston, TX). It regulates the air pressure entering the regulator to approximately 552 kPa. The air then passes through a Humphrey 3-way solenoid valve (Skarda Equipment Company, Inc., Omaha, NE). When the solenoid receives 12 Volts from the electrical portion of the system the valve closes and the compressed air remains in the pneumatic system. However, in the absence of power the valve remains open and the air vents to the atmosphere. If the valve is closed then the air continues to the next component, an electrical pressure regulator, T500X Miniature E/P Transducer (Control Air Inc., Amherst, NH). The pressure regulator converts a voltage from a buffer amplifier to a corresponding pneumatic output. The air then moves through a second 3-way solenoid valve and continues to an air manifold. The air manifold divides the air between a pressure switch, 2PSW2SYT5 Pressure Switch (Solon Manufacturing Co., Chardon, OH), a pressure transducer, PT100R13LU2H1131 Pressure Transducer (Turck Inc., Minneapolis, MN) , and an air cylinder, USR-32-1 Pneumatic Cylinder (Clippard Instrument Laboratory, Inc., Cincinnati, OH). The pressure switch is composed of two electrical switches and a diaphragm sensing element. If the pressure is greater than 414 kPa then the circuit is tripped and the loading system shuts down. The pressure switch is one of the safety mechanisms built into the system. The pressure transducer converts the pneumatic input to a voltage that is sent to the electrical portion of the system. The desired air pressure continues into the chamber of the air cylinder causing the piston to move downward. A force transducer, 1210ACK-300 lb Load Cell (Interface, Scottsdale, AZ), and pad are attached in series to the piston and allows pressure and force measurements simultaneously.

The limb loading system was designed to introduce a vertical compression load to the tibia via a load applied over the top of the femoral condyles (knee) as a percentage of body weight (%BW). A feedback loop was incorporated into the software design written in LabVIEW 8.6 (National Instruments, Austin, TX) to continuously monitor the force and pressure through the transducers and adjust accordingly. The user can define the time that the load is on and off in seconds, the number of cycles, and the magnitude of the force. In addition, data is collected with real-time display of force, pressure, electromyography (EMG), vibration, and other mechanical factors.The apparatus that serves to hold the human limb consists of a custom designed frame that was fabricated and attached to the shaker so that vibration and load can be delivered concurrently (Figure 3). The novelty of this system is that it enables the load to be applied while the entire limb segment receives vibratory stimuli. Thus, during vibration, a force-time impulse may be delivered to the extremity. The frame is made of an aluminum base plate and foot plate connected with T-slot frames. The uprights and cross bar are also made with aluminum struts. Aluminum housing contains the air cylinder and slides within the frame uprights allowing full adjustability for limb length. In addition, a tilt in space chair was welded to a lift that allows any subject, including individuals with paralysis to be positioned correctly into the device.

Figure 3
figure 3

Vibration and compression system. A) A participant seated in the adjustable wheelchair with the lower limb secured to custom designed compression frame which is fixed to the vibration shaker. The cabinet rack houses the compression hardware, DAQ board, computer, vibration controller, field power supply, and power amplifier. B-D) The output of the B) vibration, C) compression, and D) the two systems together was measured for 10 seconds or 1 cycle.

Vibration verification and transmissibility testing

We applied an independent external accelerometer, Model 3233A High-Sensitivity triaxial accelerometer (Dytran Instruments, Inc., Chatsworth, CA), to the vibration platform. The Laser vibration software is capable of various vibration parameters. We included settings aligned with those found to be effective in previous studies (0.1 g-10 g at 20–90 Hz) [2530]. In 2009, Totosy de Zepetnek presented a review of whole body vibration which concluded the optimal vibration parameters for humans have yet to be determined [33]. To test the transmissibility of the vibration signal, the software was programmed for 0.6 g at 30 Hz for 1 minute. The work of Garman and Ozcivici demonstrated the vibration of 0.6 g enhanced the bone of the vibrated limb compared to the contra lateral limb [17, 18]. During the vibration, acceleration was collected in all the cardinal directions. The x and y axes were parallel to the platform and the z axis was a perpendicular measure of the acceleration in the vertical direction. A custom MATLAB program (MathWorks, Natick, MA) was written to determine the peak of the acceleration and its frequency content. The peak was defined as the maximum value of the acceleration signal. To determine the frequency of the signal a fast Fourier transform (FFT) was performed. Based on the sampling frequency of 4,000, 32.7680 seconds or 2^17 data points of acceleration data were used for the FFT. This window of data was chosen so the length of data was a power of 2, the recommended length for a FFT.

An accelerometer was attached to the leg, thigh, and head during the vibration protocol of both the vibrated and contra lateral limbs in a single subject. Anatomical locations were defined as tibia tuberosity, distal thigh, and forehead. We defined transmissibility as the ratio of the root mean square (RMS) of acceleration of the anatomical site to the RMS of the acceleration at the mechanical apparatus, consistent with Rubin et al. [34].

Transmissibility = RM S acceleration _ body RM S acceleration _ platform

Repeatability, linearity, and accuracy testing of limb load

The custom software controls the instrumentation to deliver air pressure to the desired load to the lower leg. The calibration between the air pressure and the delivered force to the limb was determined using five known input pressures (138, 207, 276, 345, 414 kPa). The five input pressures were chosen to calibrate the system. We targeted loads that were able to secure the limb to the device and loads that we previously published to modulate spinal cord activity [35, 36]. Ten cycles were collected at each pressure. The accuracy of the limb loading system was measured by determining the linearity, repeatability, and percent error. Linearity was defined as the maximum deviation of the mean difference between the predicted response and the measured load. Repeatability was the maximum difference between measures under the same testing conditions, while percent error was calculated using the following equation, ((measured value-predicted value)/predicted value)*100. Repeatability and percent error were normalized and expressed at percentage of full scale (%FS). Prior to this air pressure validation, the load cell was calibrated. The maximum acceptable error for these three measurement was less than 5%FS.

We delivered limb loads to individuals with complete paralysis to test the reproducibility of the apparatus. Eight individuals underwent two sessions on different days to determine the between day reliability of load delivery to human limbs. Ninety compressive load cycles of 50% of body weight were delivered to one leg of the individuals with paralysis. These five second loading cycles were separated by five second rest periods so ninety cycles took 15 minutes to complete. The peak load was measured after cycles 1, 30, 60, and 90 for each session. The percent difference between days and the intra-class correlation coefficients (ICC) at each time point were calculated (IBM SPSS Statistics Version 19). An ICC > 0.8 indicates that the system has high reproducibility in delivering mechanical load on a day to day basis [37]. Included in this error assessment is the ability to connect the human subject to the mechanical interface system. Any error less than 10% was considered low for the between day reliability assessment.

Load safety assessment

Since this device is designed to interface with a human tibia, safety is of utmost importance. Although, the vibration parameters (0.6 g, 30 Hz) for this intervention are safe for humans, the system is capable of generating much larger vibration signals (66.3 g, 400 Hz) The shaker parameters were altered so that the maximum acceleration is 6 g and the shaker itself has an over travel protection that limits the peak-to-peak excursion to 11 mm. Finally, the vibration controller is equipped with an abort button that will immediately shut down the system.

The compressive system also has several safety features including an emergency stop switch that removes the load by venting the air to the environment. In addition to a mechanical stop, before starting the compression system, the user must input the cycle time, air pressure, and maximum load. The maximum load is the safety parameter which can be set to ensure that an excessive load for human tibia cannot be inadvertently applied.

To assess the safety of the compression an air pressure of 263 kPa or 445 N was programmed into the system while varying the maximum load. Seven maximum load settings, 423 N, 437 N, 441 N, 445 N, 449 N, 454 N, and 467 N were tested. The force was recorded using custom LabVIEW software written to control the compression system. The effectiveness of the maximum load safety setting was determined by examining the force signal and measuring the peak force delivered.


Transmissibility and quality of vibration signal

At a setting for a 0.6 vertical (z) acceleration and 30 Hz frequency the actual peaks were 0.0406 g, 0.0732 g, and 0.6289 g, for the x, y, and z directions, respectively. There was minimal acceleration in the planes parallel to the vertical platform direction. Through a Fast Fourier Transform we verified that over 98% of the signal power was in the intended 30 Hz frequency domain (Figure 4). Transmissibility, defined as the ratio of vibration amplitude at the anatomical site to the vibration amplitude measured at the shaker, should be equal to 1.0 if there is perfect transmissibility of the vibration to the limb segment. The transmissibility at the tibia and femur were 0.71 and 1.17, respectively. The transmissibility of vibration at the human head and the contra lateral tibia and femur was less than 0.02 (Figure 5). Therefore, the entire system directs the most of the mechanical events specifically to the targeted limb segment.

Figure 4
figure 4

Acceleration of the vibration platform. A-C) Magnitude of acceleration in the x, y, and z directions are shown. As designed, virtually all of the vibration occurs in the vertical or z direction with minimal acceleration in the axes parallel to the platform. D-F) Fast Fourier transform of the vibration signal confirms that the frequency content of the vibration is desired frequency of 30 Hz. It also demonstrated that the z-direction contained most of the frequency content.

Figure 5
figure 5

Transmissibility of the vibration. The transmissibility of the vibration signal was calculated as a ratio of the anatomical landmark RMS to the RMS of the platform. An accelerometer was place on the tibia and femur of the vibrated and unvibrated leg as well as the head. A transmissibility of 1.0 indicates that the acceleration of the anatomical site is equal to the vibration platform.

Limb load testing results

The linearity, repeatability, and error were calculated at each air pressure was 4%, 1%, and 1%, respectively (Table 1). The between session reproducibility assessment using human subjects was excellent with an intra-class correlation of 0.90 (Table 2). The percent change in limb load never exceeded 7% during between day tests. These data support that total error associated with “setting up” a human subject was low.

Table 1 The compression system performed with a high level of accuracy which is indicated by the linearity, repeatability, and percent error
Table 2 The data of eight spinal cord injury subjects were used to determine the inter-session reliability of the compression system

Vibration and limb load safety results

The vibration system consistently shutdown when the acceleration exceeded a 6.1 g, if the platform exceeded 11 mm of displacement, or the user manually pushed the shutdown switch built into the controller. In addition, activating the emergency stop switch consistently aborted the limb loading system by exhausting the compressed air into the environment. To formally test the safety mechanisms under software control, we input a load of 445 N (263 kPa) to the simulated extremity. We then intentionally exceeded the maximum load by programming in loads in excess of the 445 N threshold. The system consistently exhausted the air by the 3-way valve when the 445 N threshold was exceeded. We next set the threshold at 423 N, 437 N, and 441 N and delivered a load of 445 N. Because of a one second delay in the release of pressure, the limb segment received 435 N, 445 N, and 448 N rather than the 423 N, 437 N, and 441 N that were intended. Thus, the safety shut off was effective to within 3% of the intended load.

We had no subjective complaints from any subjects during this testing. There were no tissue areas of reddening or indentations that support that mechanical load of vibration and compression can be delivered concurrently to human tissue.


Currently, there are no existing devices that can provide isolated mechanical loading to a human limb by delivering controlled vibration and/or compression. There are devices which can vibrate [18] or compress [38] the limb of a rodent but neither can deliver vibration and compression simultaneously. Many of the existing devices for humans are commercial vibration platforms that are inherently noisy [39] and typically used for whole body vibration and not localized vibration. The vibration system presented in this paper is servo-controlled and therefore provides a constant vibration using the feedback from the accelerometer to modulate the vibration. Vibration platforms have been widely used in human research; however, prior to the mechanical system presented in this article, there was not a device capable of delivering limb vibration with or without limb compression to an isolated segment.

Bridging the gap: engineering and bioscience

The primary purpose of this technological report was to present the development of an accurate, controlled, repeatable, and safe mechanical system that would be able to induce localized biological stress to tissues within a limb of humans. Based on our presentation of the findings, we are confident that this system can reliably deliver the stresses within the loads tested based on animal studies and preliminary human reports. Our secondary purpose was to use this report to appeal to the scientific community about the importance of inter-disciplinary teams partnering as cellular therapies are developed in the bioscience laboratories. Our ability to test and learn about the optimal methods to stress tissues is paramount for many new cellular therapies developing today. A brief review of the impact of mechanical stimuli on various tissues will be presented in the subsequent sections.

Mechanical stimuli and bone tissue adaptation

The relationship between mechanical loads and tissue adaptation is long standing. Wolff [10] and Frost [40, 41] demonstrated many years ago that bone tissue is highly mutable and adapts to mechanical stress. In recent years it is well documented that the musculoskeletal system deteriorates in people with SCI [4246], people on bed rest [47], or people exposed to spaceflight [48, 49]. In just two years after paralysis, people with spinal cord injury have 23%, 25%, and 19% less articular cartilage in the patella, medial tibia, and lateral tibia, respectively [50]. Timely mechanical stress reduced the loss of bone by 32% in people with SCI [40, 51], which may ultimately be lifesaving [52]. Even secondary systemic complications like renal failure and metabolic syndrome are linked to deteriorating skeletal muscle and bone tissues [5360].

Low-magnitude whole body mechanical oscillation (0.2-0.3 g, 30 Hz), which would be well tolerated in people who already have osteoporosis, has been shown to attenuate bone loss in women with low bone mineral density [26, 61]. Whole body vibration (0.3 g, 45 Hz), at doses similar to that tested in this study, led to 75% increase in trabeculae of the proximal metaphyses of rats [5, 19]. Vibration (0.3 g, 30 Hz) of the sheep hind limb showed 34.2% increase in femur bone density [1]. However, only one animal study delivered direct limb segment vibration in-vivo, but showed the tibia had a 88% higher rate of bone formation using the same 0.6 g force demonstrated in the technology presented in this report [62]. Because the vestibular system was likely activated during the weight bearing studies, it is possible that reflexes caused muscle activations that contributed to the tissue changes observed. These studies suggest that understanding the effects of mechanical stress on tissue is complicated and the field may benefit from technologies that isolate these mechanical stresses.

Mechanical stimuli and cartilage adaptations

Mechanical loading can alter articular cartilage, intervertebral discs, and menisci [6367]. Knee menisci are particularly susceptible to injury [68] and are often resistant to healing [69]. Cyclic loading and intermittent tensile strain up-regulates VEGF (vascular endothelial growth factor), a gene directly involved with blood vessel formation [70]. Importantly, regular mechanical load reduces inflammation initiated by interleukin-1 following menisci injury [21, 71]. A torn porcine meniscus exposed to various mechanical compressive loading conditions (1, 10, or 26% strain, and 4 h/day for 14 days) showed a reduced inflammatory response and repaired mechanical tissue shear strength [21]. The value of cyclic repetitive loads on meniscus health is well documented [72, 73]. Importantly, in the absence of natural mechanisms of meniscus tissue repair, regenerative rehabilitation engineers have developed a new scaffold consisting of viable undifferentiated cells that require a healthy environment (optimal stress) to proliferate and differentiate cells [74, 75]. Injured meniscus cartilage was merely removed from the knee as little as 25 years ago. Today, the emphasis is in preserving and healing the tissue; however, the effect of controlled dynamic loads with vibration has never been explored in humans with menisci injury or repair. Hence there is a need for technologies to better study the interface between mechanical stimuli and tissue repair in humans.

Mechanical stimuli and muscle/CNS adaptations

Localized limb vibration modulates several central nervous system and muscle signaling pathways in people with and without spinal cord injury [35, 36, 76, 77]. During single limb segment vibration, the activity of the soleus muscle was suppressed [76]. Vibration caused an 83% reduction in the Hoffmann reflex (H-reflex), but limb load facilitated segmental excitability (decreased H-reflex post activation depression) [35, 77]. Likewise, direct vibration over a muscle tendon increased pre-synaptic inhibition of the H-reflex [7882] and loading (standing) reduces H-reflex post activation depression [8385]. Recent research has shown that deficiencies in postural control were associated with brain activity during localized vibration of the foot [86].

Vibration platforms for balance control have been reported to cause increased skeletal muscle activity, strength, and power [28, 8789]. These whole body vibration protocols used 2.3 g-30 g at 15–50 Hz, parameters within the range tested in the technology reported in this paper. However, these findings are not supported with direct tendon or muscle vibration; subsequent studies with tendon vibration support a decrease in quadriceps muscle activity and force [90, 91]. Some intriguing findings suggest that localized vibration mitigates muscle atrophy during reduced activity [92, 93] and regulates certain genes associated with atrophy and synaptic plasticity [4, 77]. It may be that the same dose that is optimal for bone is also optimal for cartilage, muscle, and nervous system tissue.

Mechanical stimuli and stem cell stimulation

An in depth coverage of stem cells is beyond the scope of this technical report. However, a brief summary is warranted. We now know that stem cells require an environment with appropriate stresses to foster survival, proliferation, and ultimately specialization. We also know that vibration input at a 5 g force and 30 Hz frequency caused adult stem cells to differentiate into bone cells [94], and cartilage precursor cells differentiated into cartilage after cyclic mechanical loading (1 Hz, 10% strain rate) [95], similar to the stimuli that we tested in this technical report. Furthermore, recently, chondrocytes were shown to survive longer if they had been exposed to vibratory input and intermittent compressive loading [63, 96]. Quiescent satellite cells in skeletal muscle showed enhanced gene regulation for protein synthesis following vibratory input at 30 Hz frequency [4]. Clearly, the degree to which a satellite cell will evolve from the undifferentiated state to the specialized state is under the direction of the mechanical environment. Thus, the need for technology to translate these mechanical stresses is fundamental to establishing the efficacy for preserving health of tissues in the future.

In summary, the instrumentation presented in this technological report is novel, reliable, accurate, and safe for human tissues. To fully translate technology from the laboratory to human studies will require that experts from engineering, rehabilitation, and biosciences, work collaboratively to advance the field of human regenerative rehabilitation.


This report presents a novel example of how to deliver compressive and vibratory loads to the lower limb in humans via a new technology. Mechanical loads such as vibration and direct limb load have not been systematically studied in various combinations in humans. Importantly, the vibration stimuli developed in this report is directed to a single limb, rather than to the whole body, allowing a method to compare the direct effects of load to specific tissue. By delivering isolated therapeutic doses of mechanical stress to human tissues, we anticipate that the optimal methods of mechanically and physiologically stressing tissues may be ascertained in future studies.

Availability and requirements

Project name: Human Regenerative Rehabilitation

Project home page: Not applicable

Operating system (s): Platform independent

Programming language: Not applicable

Other requirements: Not applicable

License: Not applicable

Any restrictions to use by non-academics: Not applicable

Availability of supporting data

No supporting data will be submitted with this manuscript.



Spinal cord injury




Gravitational force of the Earth




Percent body weight




Fast Fourier transform


Root means square


Intra-class correlation coefficient


Vascular endothelial growth factor


Hoffmann reflex


Percent full scale


Data acquisition.


  1. Rubin C, Turner AS, Bain S, Mallinckrodt C, McLeod K: Anabolism. Low mechanical signals strengthen long bones. Nature. 2001, 412: 603-604.

    Article  PubMed  CAS  Google Scholar 

  2. Maddalozzo GF, Iwaniec UT, Turner RT, Rosen CJ, Widrick JJ: Whole-body vibration slows the acquisition of fat in mature female rats. Int J Obes (Lond). 2008, 32: 1348-1354. 10.1038/ijo.2008.111.

    Article  CAS  Google Scholar 

  3. Rubin CT, Capilla E, Luu YK, Busa B, Crawford H, Nolan DJ, Mittal V, Rosen CJ, Pessin JE, Judex S: Adipogenesis is inhibited by brief, daily exposure to high-frequency, extremely low-magnitude mechanical signals. Proc Natl Acad Sci U S A. 2007, 104: 17879-17884. 10.1073/pnas.0708467104.

    Article  PubMed  CAS  PubMed Central  Google Scholar 

  4. Ceccarelli G, Benedetti L, Galli D, Pre D, Silvani G, Crosetto N, Magenes G, Cusella De Angelis MG: Low-amplitude high frequency vibration down-regulates myostatin and atrogin-1 expression, two components of the atrophy pathway in muscle cells. J Tissue Eng Regen Med. 2012, 8: 396-406.

    Article  PubMed  Google Scholar 

  5. Xie L, Rubin C, Judex S: Enhancement of the adolescent murine musculoskeletal system using low-level mechanical vibrations. J Appl Physiol. 2008, 104: 1056-1062. 10.1152/japplphysiol.00764.2007.

    Article  PubMed  Google Scholar 

  6. Raju SG, Rogness O, Persson M, Bain J, Riley D: Vibration from a riveting hammer causes severe nerve damage in the rat tail model. Muscle Nerve. 2011, 44: 795-804. 10.1002/mus.22206.

    Article  PubMed  Google Scholar 

  7. Heaver C, Goonetilleke KS, Ferguson H, Shiralkar S: Hand-arm vibration syndrome: a common occupational hazard in industrialized countries. J Hand Surg Eur Vol. 2011, 36: 354-363.

    Article  PubMed  CAS  Google Scholar 

  8. Bovenzi M: Metrics of whole-body vibration and exposure-response relationship for low back pain in professional drivers: a prospective cohort study. Int Arch Occup Environ Health. 2009, 82: 893-917. 10.1007/s00420-008-0376-3.

    Article  PubMed  Google Scholar 

  9. Tiemessen IJ, Hulshof CT, Frings-Dresen MH: Low back pain in drivers exposed to whole body vibration: analysis of a dose–response pattern. Occup Environ Med. 2008, 65: 667-675. 10.1136/oem.2007.035147.

    Article  PubMed  CAS  Google Scholar 

  10. Wolff J: The Law of Bone Remodelling. 1986, Berlin, Heidelberg, New York: Springer-Verlag

    Book  Google Scholar 

  11. Akyuz E, Braun JT, Brown NA, Bachus KN: Static versus dynamic loading in the mechanical modulation of vertebral growth. Spine. 2006, 31 (Phila Pa 1976): E952-958.

    Article  PubMed  Google Scholar 

  12. Robling AG, Duijvelaar KM, Geevers JV, Ohashi N, Turner CH: Modulation of appositional and longitudinal bone growth in the rat ulna by applied static and dynamic force. Bone. 2001, 29: 105-113. 10.1016/S8756-3282(01)00488-4.

    Article  PubMed  CAS  Google Scholar 

  13. Churches AE, Howlett CR: Functional adaptation of bone in response to sinusoidally varying controlled compressive loading of the ovine metacarpus. Clin Orthop Relat Res. 1982, 168: 265-280.

    PubMed  Google Scholar 

  14. Rubin CT, Lanyon LE: Regulation of bone formation by applied dynamic loads. J Bone Joint Surg Am. 1984, 66: 397-402.

    PubMed  CAS  Google Scholar 

  15. Turner CH, Owan I, Takano Y: Mechanotransduction in bone: role of strain rate. Am J Physiol. 1995, 269: E438-442.

    PubMed  CAS  Google Scholar 

  16. Christiansen BA, Silva MJ: The effect of varying magnitudes of whole-body vibration on several skeletal sites in mice. Ann Biomed Eng. 2006, 34: 1149-1156. 10.1007/s10439-006-9133-5.

    Article  PubMed  Google Scholar 

  17. Garman R, Gaudette G, Donahue LR, Rubin C, Judex S: Low-level accelerations applied in the absence of weight bearing can enhance trabecular bone formation. J Orthop Res. 2007, 25: 732-740. 10.1002/jor.20354.

    Article  PubMed  Google Scholar 

  18. Ozcivici E, Garman R, Judex S: High-frequency oscillatory motions enhance the simulated mechanical properties of non-weight bearing trabecular bone. J Biomech. 2007, 40: 3404-3411. 10.1016/j.jbiomech.2007.05.015.

    Article  PubMed  Google Scholar 

  19. Xie L, Jacobson JM, Choi ES, Busa B, Donahue LR, Miller LM, Rubin CT, Judex S: Low-level mechanical vibrations can influence bone resorption and bone formation in the growing skeleton. Bone. 2006, 39: 1059-1066. 10.1016/j.bone.2006.05.012.

    Article  PubMed  Google Scholar 

  20. Bader DL, Salter DM, Chowdhury TT: Biomechanical influence of cartilage homeostasis in health and disease. Arthritis. 2011, 2011: 979032-

    Article  PubMed  CAS  PubMed Central  Google Scholar 

  21. McNulty AL, Estes BT, Wilusz RE, Weinberg JB, Guilak F: Dynamic loading enhances integrative meniscal repair in the presence of interleukin-1. Osteoarthritis Cartilage. 2010, 18: 830-838. 10.1016/j.joca.2010.02.009.

    Article  PubMed  CAS  PubMed Central  Google Scholar 

  22. Flieger J, Karachalios T, Khaldi L, Raptou P, Lyritis G: Mechanical stimulation in the form of vibration prevents postmenopausal bone loss in ovariectomized rats. Calcif Tissue Int. 1998, 63: 510-514. 10.1007/s002239900566.

    Article  PubMed  CAS  Google Scholar 

  23. Judex S, Lei X, Han D, Rubin C: Low-magnitude mechanical signals that stimulate bone formation in the ovariectomized rat are dependent on the applied frequency but not on the strain magnitude. J Biomech. 2007, 40: 1333-1339. 10.1016/j.jbiomech.2006.05.014.

    Article  PubMed  Google Scholar 

  24. Rubinacci A, Marenzana M, Cavani F, Colasante F, Villa I, Willnecker J, Moro GL, Spreafico LP, Ferretti M, Guidobono F, Marotti G: Ovariectomy sensitizes rat cortical bone to whole-body vibration. Calcif Tissue Int. 2008, 82: 316-326. 10.1007/s00223-008-9115-8.

    Article  PubMed  CAS  Google Scholar 

  25. Belavy DL, Beller G, Armbrecht G, Perschel FH, Fitzner R, Bock O, Borst H, Degner C, Gast U, Felsenberg D: Evidence for an additional effect of whole-body vibration above resistive exercise alone in preventing bone loss during prolonged bed rest. Osteoporos Int. 2011, 22: 1581-1591. 10.1007/s00198-010-1371-6.

    Article  PubMed  CAS  Google Scholar 

  26. Gilsanz V, Wren TA, Sanchez M, Dorey F, Judex S, Rubin C: Low-level, high-frequency mechanical signals enhance musculoskeletal development of young women with low BMD. J Bone Miner Res. 2006, 21: 1464-1474. 10.1359/jbmr.060612.

    Article  PubMed  Google Scholar 

  27. Torvinen S, Kannus P, Sievanen H, Jarvinen TA, Pasanen M, Kontulainen S, Nenonen A, Jarvinen TL, Paakkala T, Jarvinen M, Vuori I: Effect of 8-month vertical whole body vibration on bone, muscle performance, and body balance: a randomized controlled study. J Bone Miner Res. 2003, 18: 876-884. 10.1359/jbmr.2003.18.5.876.

    Article  PubMed  Google Scholar 

  28. Verschueren SM, Roelants M, Delecluse C, Swinnen S, Vanderschueren D, Boonen S: Effect of 6-month whole body vibration training on hip density, muscle strength, and postural control in postmenopausal women: a randomized controlled pilot study. J Bone Miner Res. 2004, 19: 352-359.

    Article  PubMed  Google Scholar 

  29. Ward K, Alsop C, Caulton J, Rubin C, Adams J, Mughal Z: Low magnitude mechanical loading is osteogenic in children with disabling conditions. J Bone Miner Res. 2004, 19: 360-369. 10.1359/JBMR.040129.

    Article  PubMed  Google Scholar 

  30. Kiel DP, Hannan MT, Barton BA, Bouxsein ML, Lang TF, Brown KM, Shane E, Magaziner J, Zimmerman S, Rubin CT: Insights from the conduct of a device trial in older persons: low magnitude mechanical stimulation for musculoskeletal health. Clin Trials. 2010, 7: 354-367. 10.1177/1740774510371014.

    Article  PubMed  PubMed Central  Google Scholar 

  31. Pollock RD, Woledge RC, Martin FC, Newham DJ: Effects of whole body vibration on motor unit recruitment and threshold. J Appl Physiol. 2012, 112: 388-395. 10.1152/japplphysiol.01223.2010.

    Article  PubMed  PubMed Central  Google Scholar 

  32. Elmantaser M, McMillan M, Smith K, Khanna S, Chantler D, Panarelli M, Ahmed SF: A comparison of the effect of two types of vibration exercise on the endocrine and musculoskeletal system. J Musculoskelet Neuronal Interact. 2012, 12: 144-154.

    PubMed  CAS  Google Scholar 

  33. Totosy De Zepetnek JO, Giangregorio LM, Craven BC: Whole-body vibration as potential intervention for people with low bone mineral density and osteoporosis: a review. J Rehabil Res Dev. 2009, 46: 529-542. 10.1682/JRRD.2008.09.0136.

    Article  PubMed  Google Scholar 

  34. Rubin C, Pope M, Fritton JC, Magnusson M, Hansson T, McLeod K: Transmissibility of 15-hertz to 35-hertz vibrations to the human hip and lumbar spine: determining the physiologic feasibility of delivering low-level anabolic mechanical stimuli to skeletal regions at greatest risk of fracture because of osteoporosis. Spine. 2003, 28 (Phila Pa 1976): 2621-2627.

    Article  PubMed  Google Scholar 

  35. Tseng SC, Shields RK: Limb segment load inhibits post activation depression of soleus H-reflex in humans. Clin Neurophysiol. 2012, 124: 982-990.

    Article  PubMed  PubMed Central  Google Scholar 

  36. Tseng SC, Shields RK: Limb compressive load does not inhibit post activation depression of soleus H-reflex in indiviudals with chronic spinal cord injury. Clin Neurophysiol. 2013, 124: 982-990. 10.1016/j.clinph.2012.10.020.

    Article  PubMed  PubMed Central  Google Scholar 

  37. Portney LG, Watkins , Mary P: Foundations of Clinical Research: Applications to Practice. 1993, Norwalk: Connecticut: Appleton & Lange

    Google Scholar 

  38. De Souza RL, Matsuura M, Eckstein F, Rawlinson SC, Lanyon LE, Pitsillides AA: Non-invasive axial loading of mouse tibiae increases cortical bone formation and modifies trabecular organization: a new model to study cortical and cancellous compartments in a single loaded element. Bone. 2005, 37: 810-818. 10.1016/j.bone.2005.07.022.

    Article  PubMed  Google Scholar 

  39. Pel JJ, Bagheri J, Van Dam LM, van den Berg-Emons HJ, Horemans HL, Stam HJ, van der Steen J: Platform accelerations of three different whole-body vibration devices and the transmission of vertical vibrations to the lower limbs. Med Eng Phys. 2009, 31: 937-944. 10.1016/j.medengphy.2009.05.005.

    Article  PubMed  CAS  Google Scholar 

  40. Frost HM: Vital biomechanics: proposed general concepts for skeletal adaptations to mechanical usage. Calcif Tissue Int. 1988, 42: 145-156. 10.1007/BF02556327.

    Article  PubMed  CAS  Google Scholar 

  41. Frost HM: Bone's mechanostat: a 2003 update. Anat Rec A Discov Mol Cell Evol Biol. 2003, 275: 1081-1101.

    Article  PubMed  Google Scholar 

  42. Eser P, Frotzler A, Zehnder Y, Wick L, Knecht H, Denoth J, Schiessl H: Relationship between the duration of paralysis and bone structure: a pQCT study of spinal cord injured individuals. Bone. 2004, 34: 869-880. 10.1016/j.bone.2004.01.001.

    Article  PubMed  CAS  Google Scholar 

  43. Wilmet E, Ismail AA, Heilporn A, Welraeds D, Bergmann P: Longitudinal study of the bone mineral content and of soft tissue composition after spinal cord section. Paraplegia. 1995, 33: 674-677. 10.1038/sc.1995.141.

    Article  PubMed  CAS  Google Scholar 

  44. Shields RK, Dudley-Javoroski S, Boaldin KM, Corey TA, Fog DB, Ruen JM: Peripheral quantitative computed tomography: measurement sensitivity in persons with and without spinal cord injury. Arch Phys Med Rehabil. 2006, 87: 1376-1381. 10.1016/j.apmr.2006.07.257.

    Article  PubMed  PubMed Central  Google Scholar 

  45. Modlesky CM, Majumdar S, Narasimhan A, Dudley GA: Trabecular bone microarchitecture is deteriorated in men with spinal cord injury. J Bone Miner Res. 2004, 19: 48-55.

    Article  PubMed  Google Scholar 

  46. Modlesky CM, Slade JM, Bickel CS, Meyer RA, Dudley GA: Deteriorated geometric structure and strength of the midfemur in men with complete spinal cord injury. Bone. 2005, 36: 331-339. 10.1016/j.bone.2004.10.012.

    Article  PubMed  Google Scholar 

  47. Leblanc AD, Schneider VS, Evans HJ, Engelbretson DA, Krebs JM: Bone mineral loss and recovery after 17 weeks of bed rest. J Bone Miner Res. 1990, 5: 843-850.

    Article  PubMed  CAS  Google Scholar 

  48. LeBlanc AD, Spector ER, Evans HJ, Sibonga JD: Skeletal responses to space flight and the bed rest analog: a review. J Musculoskelet Neuronal Interact. 2007, 7: 33-47.

    PubMed  CAS  Google Scholar 

  49. LeBlanc A, Schneider V, Shackelford L, West S, Oganov V, Bakulin A, Voronin L: Bone mineral and lean tissue loss after long duration space flight. J Musculoskelet Neuronal Interact. 2000, 1: 157-160.

    PubMed  CAS  Google Scholar 

  50. Vanwanseele B, Eckstein F, Knecht H, Stussi E, Spaepen A: Knee cartilage of spinal cord-injured patients displays progressive thinning in the absence of normal joint loading and movement. Arthritis Rheum. 2002, 46: 2073-2078. 10.1002/art.10462.

    Article  PubMed  CAS  Google Scholar 

  51. Dudley-Javoroski S, Saha PK, Liang G, Li C, Gao Z, Shields RK: High dose compressive loads attenuate bone mineral loss in humans with spinal cord injury. Osteoporos Int. 2011, 23: 2335-2346.

    Article  PubMed  PubMed Central  Google Scholar 

  52. Dudley-Javoroski S, Shields RK: Muscle and bone plasticity after spinal cord injury: review of adaptations to disuse and to electrical muscle stimulation. J Rehabil Res Dev. 2008, 45: 283-296. 10.1682/JRRD.2007.02.0031.

    Article  PubMed  PubMed Central  Google Scholar 

  53. Bagley WH, Yang H, Shah KH: Rhabdomyolysis. Intern Emerg Med. 2007, 2: 210-218. 10.1007/s11739-007-0060-8.

    Article  PubMed  CAS  Google Scholar 

  54. Welk B, Fuller A, Razvi H, Denstedt J: Renal stone disease in spinal-cord-injured patients. J Endourol. 2012, 26: 954-959. 10.1089/end.2012.0063.

    Article  PubMed  Google Scholar 

  55. Gorgey AS, Shepherd C: Skeletal muscle hypertrophy and decreased intramuscular fat after unilateral resistance training in spinal cord injury: case report. J Spinal Cord Med. 2010, 33: 90-95.

    PubMed  PubMed Central  Google Scholar 

  56. Vestergaard P, Krogh K, Rejnmark L, Mosekilde L: Fracture rates and risk factors for fractures in patients with spinal cord injury. Spinal Cord. 1998, 36: 790-796. 10.1038/

    Article  PubMed  CAS  Google Scholar 

  57. Beck BR: Muscle forces or gravity–what predominates mechanical loading on bone? Introduction. Med Sci Sports Exerc. 2009, 41: 2033-2036. 10.1249/MSS.0b013e3181a8c4b6.

    Article  PubMed  Google Scholar 

  58. Robling AG: Is bone's response to mechanical signals dominated by muscle forces?. Med Sci Sports Exerc. 2009, 41: 2044-2049. 10.1249/MSS.0b013e3181a8c702.

    Article  PubMed  PubMed Central  Google Scholar 

  59. Kohrt WM, Barry DW, Schwartz RS: Muscle forces or gravity: what predominates mechanical loading on bone?. Med Sci Sports Exerc. 2009, 41: 2050-2055. 10.1249/MSS.0b013e3181a8c717.

    Article  PubMed  PubMed Central  Google Scholar 

  60. Judex S, Carlson KJ: Is bone's response to mechanical signals dominated by gravitational loading?. Med Sci Sports Exerc. 2009, 41: 2037-2043. 10.1249/MSS.0b013e3181a8c6e5.

    Article  PubMed  Google Scholar 

  61. Rubin C, Recker R, Cullen D, Ryaby J, McCabe J, McLeod K: Prevention of postmenopausal bone loss by a low-magnitude, high-frequency mechanical stimuli: a clinical trial assessing compliance, efficacy, and safety. J Bone Miner Res. 2004, 19: 343-351.

    Article  PubMed  Google Scholar 

  62. Garman R, Rubin C, Judex S: Small oscillatory accelerations, independent of matrix deformations, increase osteoblast activity and enhance bone morphology. PLoS One. 2007, 2: e653-10.1371/journal.pone.0000653.

    Article  PubMed  PubMed Central  Google Scholar 

  63. Waldman SD, Spiteri CG, Grynpas MD, Pilliar RM, Kandel RA: Long-term intermittent compressive stimulation improves the composition and mechanical properties of tissue-engineered cartilage. Tissue Eng. 2004, 10: 1323-1331. 10.1089/ten.2004.10.1323.

    Article  PubMed  CAS  Google Scholar 

  64. Fan JC, Waldman SD: The effect of intermittent static biaxial tensile strains on tissue engineered cartilage. Ann Biomed Eng. 2010, 38: 1672-1682. 10.1007/s10439-010-9917-5.

    Article  PubMed  Google Scholar 

  65. Puetzer JL, Ballyns JJ, Bonassar LJ: The effect of the duration of mechanical stimulation and post-stimulation culture on the structure and properties of dynamically compressed tissue-engineered menisci. Tissue Eng Part A. 2012, 18: 1365-1375. 10.1089/ten.tea.2011.0589.

    Article  PubMed  CAS  Google Scholar 

  66. Ballyns JJ, Bonassar LJ: Dynamic compressive loading of image-guided tissue engineered meniscal constructs. J Biomech. 2011, 44: 509-516. 10.1016/j.jbiomech.2010.09.017.

    Article  PubMed  Google Scholar 

  67. Woiciechowsky C, Abbushi A, Zenclussen ML, Casalis P, Kruger JP, Freymann U, Endres M, Kaps C: Regeneration of nucleus pulposus tissue in an ovine intervertebral disc degeneration model by cell-free resorbable polymer scaffolds. J Tissue Eng Regen Med. 2012, [Epub ahead of print]

    Google Scholar 

  68. Makris EA, Hadidi P, Athanasiou KA: The knee meniscus: structure-function, pathophysiology, current repair techniques, and prospects for regeneration. Biomaterials. 2011, 32: 7411-7431. 10.1016/j.biomaterials.2011.06.037.

    Article  PubMed  CAS  PubMed Central  Google Scholar 

  69. Arnoczky SP, Warren RF: Microvasculature of the human meniscus. Am J Sports Med. 1982, 10: 90-95. 10.1177/036354658201000205.

    Article  PubMed  CAS  Google Scholar 

  70. Frost HM: Bone "mass" and the "mechanostat": a proposal. Anat Rec. 1987, 219: 1-9. 10.1002/ar.1092190104.

    Article  PubMed  CAS  Google Scholar 

  71. Shin SJ, Fermor B, Weinberg JB, Pisetsky DS, Guilak F: Regulation of matrix turnover in meniscal explants: role of mechanical stress, interleukin-1, and nitric oxide. J Appl Physiol. 2003, 95: 308-313.

    Article  PubMed  CAS  Google Scholar 

  72. Ferretti M, Madhavan S, Deschner J, Rath-Deschner B, Wypasek E, Agarwal S: Dynamic biophysical strain modulates proinflammatory gene induction in meniscal fibrochondrocytes. Am J Physiol Cell Physiol. 2006, 290: C1610-1615. 10.1152/ajpcell.00529.2005.

    Article  PubMed  CAS  Google Scholar 

  73. Deschner J, Wypasek E, Ferretti M, Rath B, Anghelina M, Agarwal S: Regulation of RANKL by biomechanical loading in fibrochondrocytes of meniscus. J Biomech. 2006, 39: 1796-1803. 10.1016/j.jbiomech.2005.05.034.

    Article  PubMed  Google Scholar 

  74. Rodkey WG, DeHaven KE, Montgomery WH, Baker CL, Beck CL, Hormel SE, Steadman JR, Cole BJ, Briggs KK: Comparison of the collagen meniscus implant with partial meniscectomy. A prospective randomized trial. J Bone Joint Surg Am. 2008, 90: 1413-1426. 10.2106/JBJS.G.00656.

    Article  PubMed  Google Scholar 

  75. Monllau JC, Gelber PE, Abat F, Pelfort X, Abad R, Hinarejos P, Tey M: Outcome after partial medial meniscus substitution with the collagen meniscal implant at a minimum of 10 years' follow-up. Arthroscopy. 2011, 27: 933-943. 10.1016/j.arthro.2011.02.018.

    Article  PubMed  Google Scholar 

  76. Chang SH, Dudley-Javoroski S, Shields RK: Gravitational force modulates muscle activity during mechanical oscillation of the tibia in humans. J Electromyogr Kinesiol. 2011, 21: 847-853. 10.1016/j.jelekin.2011.06.001.

    Article  PubMed  PubMed Central  Google Scholar 

  77. Chang SH, Tseng SC, McHenry CL, Littmann AE, Suneja M, Shields RK: Limb segment vibration modulates spinal reflex excitability and muscle mRNA expression after spinal cord injury. Clin Neurophysiol. 2012, 123: 558-568. 10.1016/j.clinph.2011.08.001.

    Article  PubMed  CAS  PubMed Central  Google Scholar 

  78. De Gail P, Lance JW, Neilson PD: Differential effects on tonic and phasic reflex mechanisms produced by vibration of muscles in man. J Neurol Neurosurg Psychiatry. 1966, 29: 1-11. 10.1136/jnnp.29.1.1.

    Article  PubMed  CAS  PubMed Central  Google Scholar 

  79. Rymer WZ, Hasan Z: Prolonged time course for vibratory suppression of stretch reflex in the decerebrate cat. Exp Brain Res. 1981, 44: 101-112.

    Article  PubMed  CAS  Google Scholar 

  80. Hultborn H, Meunier S, Pierrot-Deseilligny E, Shindo M: Changes in presynaptic inhibition of Ia fibres at the onset of voluntary contraction in man. J Physiol. 1987, 389: 757-772.

    Article  PubMed  CAS  PubMed Central  Google Scholar 

  81. Lance JW, De Gail P, Neilson PD: Tonic and phasic spinal cord mechanisms in man. J Neurol Neurosurg Psychiatry. 1966, 29: 535-544. 10.1136/jnnp.29.6.535.

    Article  PubMed Central  Google Scholar 

  82. Martin BJ, Roll JP, Gauthier GM: Inhibitory effects of combined agonist and antagonist muscle vibration on H-reflex in man. Aviat Space Environ Med. 1986, 57: 681-687.

    PubMed  CAS  Google Scholar 

  83. Kawashima N, Sekiguchi H, Miyoshi T, Nakazawa K, Akai M: Inhibition of the human soleus Hoffman reflex during standing without descending commands. Neurosci Lett. 2003, 345: 41-44. 10.1016/S0304-3940(03)00485-3.

    Article  PubMed  CAS  Google Scholar 

  84. Nakazawa K, Miyoshi T, Sekiguchi H, Nozaki D, Akai M, Yano H: Effects of loading and unloading of lower limb joints on the soleus H-reflex in standing humans. Clin Neurophysiol. 2004, 115: 1296-1304. 10.1016/j.clinph.2004.01.016.

    Article  PubMed  Google Scholar 

  85. Hwang S, Jeon HS, Kwon OY, Yi CH: The effects of body weight on the soleus H-reflex modulation during standing. J Electromyogr Kinesiol. 2011, 21: 445-449. 10.1016/j.jelekin.2010.11.002.

    Article  PubMed  Google Scholar 

  86. Goble DJ, Coxon JP, Van Impe A, Geurts M, Doumas M, Wenderoth N, Swinnen SP: Brain activity during ankle proprioceptive stimulation predicts balance performance in young and older adults. J Neurosci. 2011, 31: 16344-16352. 10.1523/JNEUROSCI.4159-11.2011.

    Article  PubMed  CAS  Google Scholar 

  87. Lamont HS, Cramer JT, Bemben DA, Shehab RL, Anderson MA, Bemben MG: Effects of a 6-week periodized squat training with or without whole-body vibration upon short-term adaptations in squat strength and body composition. J Strength Cond Res. 2011, 25: 1839-1848. 10.1519/JSC.0b013e3181e7ffad.

    Article  PubMed  Google Scholar 

  88. Torvinen S, Kannu P, Sievanen H, Jarvinen TA, Pasanen M, Kontulainen S, Jarvinen TL, Jarvinen M, Oja P, Vuori I: Effect of a vibration exposure on muscular performance and body balance. Randomized cross-over study. Clin Physiol Funct Imaging. 2002, 22: 145-152. 10.1046/j.1365-2281.2002.00410.x.

    Article  PubMed  Google Scholar 

  89. Cardinale M, Bosco C: The use of vibration as an exercise intervention. Exerc Sport Sci Rev. 2003, 31: 3-7. 10.1097/00003677-200301000-00002.

    Article  PubMed  Google Scholar 

  90. Rice DA, McNair PJ, Lewis GN: Mechanisms of quadriceps muscle weakness in knee joint osteoarthritis: the effects of prolonged vibration on torque and muscle activation in osteoarthritic and healthy control subjects. Arthritis Res Ther. 2011, 13: R151-10.1186/ar3467.

    Article  PubMed  PubMed Central  Google Scholar 

  91. Bongiovanni LG, Hagbarth KE, Stjernberg L: Prolonged muscle vibration reducing motor output in maximal voluntary contractions in man. J Physiol. 1990, 423: 15-26.

    Article  PubMed  CAS  PubMed Central  Google Scholar 

  92. Falempin M, In-Albon SF: Influence of brief daily tendon vibration on rat soleus muscle in non-weight-bearing situation. J Appl Physiol. 1999, 87: 3-9.

    PubMed  CAS  Google Scholar 

  93. Kyparos A, Feeback DL, Layne CS, Martinez DA, Clarke MS: Mechanical stimulation of the plantar foot surface attenuates soleus muscle atrophy induced by hindlimb unloading in rats. J Appl Physiol. 2005, 99: 739-746. 10.1152/japplphysiol.00771.2004.

    Article  PubMed  Google Scholar 

  94. Pre D, Ceccarelli G, Visai L, Benedetti L, Imbriani M, Cusella De Angelis MG, Magenes G: High-Frequency Vibration Treatment of Human Bone Marrow Stromal Cells Increases Differentiation toward Bone Tissue. Bone marrow research. 2013, 2013: 803450-

    Article  PubMed  CAS  PubMed Central  Google Scholar 

  95. Huang CY, Hagar KL, Frost LE, Sun Y, Cheung HS: Effects of cyclic compressive loading on chondrogenesis of rabbit bone-marrow derived mesenchymal stem cells. Stem cells. 2004, 22: 313-323. 10.1634/stemcells.22-3-313.

    Article  PubMed  CAS  Google Scholar 

  96. Kaupp JA, Waldman SD: Mechanical vibrations increase the proliferation of articular chondrocytes in high-density culture. Proc Inst Mech Eng H. 2008, 222: 695-703. 10.1243/09544119JEIM376.

    Article  PubMed  CAS  Google Scholar 

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This project was supported by grants from the NIH (R01-HD-062507) and the Neilsen Foundation.

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CM helped implement the system, collected and analyzed data, and drafted the manuscript. JW provided technical assistance to implement the system and assisted with editing the manuscript. RKS conceived and developed the technology, provided oversight of all testing, procured funding, and edited/ approved the final draft of the manuscript. All authors read and approved the final manuscript.

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McHenry, C.L., Wu, J. & Shields, R.K. Potential regenerative rehabilitation technology: implications of mechanical stimuli to tissue health. BMC Res Notes 7, 334 (2014).

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