Designing a Multiaxial Extensometric Force Platform: A Manufacturing Experience

: Studies that lead to the development of more accessible and low-cost electronic technologies and devices for biomechanical and biomedical analysis applications are becoming increasingly needed. In this work, the development of a multiaxial extensometric force platform will be addressed, aiming to improve the sensitivity and reduce the costs of existing platforms. Additionally, this platform can be used for analysis and characterization of ﬂight time and postural characterization of volleyball athletes. As a result, a functional and easily produced prototype was created, due to the processes used (ﬁnal cost of the developed platform—USD$100). The interfaces of visualization and analysis of the device functions were designed in LabView. The purpose of the experiments is to perform ﬂight analysis of athletes, and all functions designed for the platform strength and endurance are focused on that same purpose. The prototype’s functions were evaluated by applying loads from 700 to 1000 N (Newtons) and its future integration with other instruments such as the surface electromyography (EMG) and an electrocardiogram (ECG) is expected to form an instrument kit that improves the characterization of studies of balance, strength and muscular endurance.


Introduction
The demand for studies that promote the development of new electronic, biomechanical and other devices that will reduce the costs of analysis, treat postural problems and the degradation of muscle power in athletes and in the elderly population is increasing [1][2][3].
Applying several methods and techniques that include the use of force platforms for conducting postural analysis studies is not new. However, these studies are not focused on the improvement of force platforms, their precision and low cost, but only in their use as a product for sports professionals and physiotherapists.
As an example, some studies use force platforms to apply the method of ground reaction forces on each child's foot. Their objective is to apply a method that decomposes ground reaction forces (GRF) profiles, right and left, in relation to the GRF profile registered on the platform, to identify atypical postures [4]. In the study by P. Kutilek et al. [5], a force platform was used to assess the entire pathological prosthetic gait, which included groups of healthy people with prostheses. In the study that proposes the application of the GRF method by B. Samadi et al. [4] and, when it comes to the reconstruction of the foot-to-ground reaction forces from force platform records, the results suggested the efficient application of this method in the recovery of corrupted data due to incorrect stepping on a force platform while performing a certain analysis [6]. Some other studies have the objective of developing dynamic calibration methods [7,8], considering that the static method is the most used due to its low cost.
It is evident that, in clinical practice, postural stability is commonly assessed by the balance performance of body oscillation on a force platform. In these analyzes, individuals with different physical characteristics or pathologies are approached and some simplified commercial prototypes [9] are used, which are quite efficient, but limited in terms of the level of force that can be measured. There is a more extensive study in [10] that details, although in a very limited way, the development of a platform used for sports biomechanical evaluation in athletes. In M. J. Ameen et al. [11], the authors focused on evaluating and analyzing the forces obtained in rotational movements of sports activities using a circular force platform and the LabView software as an interface for data processing and analysis. They claim that the developed prototype can also be used in studies including torque, acceleration, displacement and others that allow measuring the performance of athletes.
Force platform designs that are applied in clinical gait analysis [12] are common, although they present weak details of the development process and a greater focus on data analysis and visualization. Finally, calibration aspects must always be addressed [7,8], including the development of new dynamic models that allow the global calibration of the force platform [13,14].

Literature Survey
Force platforms have several manufacturing and precision characteristics. Although there are a considerable number of initiatives regarding its use, there are few that present the development of new prototypes and fewer are the works that perform a detailed description of the process. Table 1 presents some of the initiatives that include the development of force platform projects in the literature. measuring quiet stance and dynamic standing balance in healthy subjects [17] The studies on postural analysis are focused only on the use of force platforms [18][19][20][21][22][23][24][25][26][27] and are much more numerous, differently from the projects and research that show greater emphasis on the development of these platforms. The works analyzed in [5,6,[9][10][11][12][15][16][17] present descriptions that are very superficial and difficult to reproduce, in addition to all making use of load cells for commercial use, significantly increasing the cost of prototypes.
Finally, and as evidenced in the literary review of Table 1, it is noted the difficulty in finding studies that include the complete and detailed design of force platforms, regardless of the technique or technology to be used, and that stimulate their quick and easy reproduction, as well as the customization of these instruments. The lack of more detailed studies ends up requiring the adaptation of postural analysis techniques to high-cost electronic devices and commercial force platforms that are difficult to customize to meet the demands of precision, resistance, dynamics and maximum load. It should be noted that, in most cases, all these aspects are necessary for conducting innovative clinical studies.
In this work, each of the processes involved in the design, simulation, fabrication, and testing of a low cost extensometric multiaxial force platform is described in detail. The objective is to facilitate the reproduction of this type of instrument, improvement, and suitability for new clinical projects at a low cost. All stages, 3D designs, schematics and source codes are shared throughout this work.

An Architecture Overview
The development of mechanical devices requires adequate attention in their measurements and analysis of the efforts applied to the elements that are part of the device structure. In general, all equipment and instruments are built from a series of structural calculations. Thus, it is possible to determine the maximum load allowed by the part and to consider the safety factor for analyzes of fatigue, rupture and resonance frequencies of the material, also known as modal analysis [28].
The development of the project begins with a functional representation ( Figure 1) of all the processes involved, its execution flow and emphasizing the main elements that determine the division of the device's prefabrication steps. The following are the steps that correspond to the prefabrication phase of the extensometric multiaxial force platform (Figure 2), which are: -The design of the load cells; -Simulation and optimization; -Evaluation and optimization of the force platform physical structure; -Sensor positioning project (strain gauges); -Implementation of simulated structures and systems.

Design and Manufacture of the Force Platform
In this work, the sensitivity improvement of the biomechanical device is highlighted, as well as the reduction of manufacturing costs when compared to the already existing force platforms.
In this section, there is a step-by-step description of the adopted techniques, tools and models built, which are detailed and made available to facilitate the reproduction of the project by other researchers.

Platform Design
The 3D design of the physical structure of the force platform was performed using the Autodesk Inventor TM . In this project, the force platform was divided into 3 parts: -Lower and upper bases; -Load cells; -Load cell mounting and bearing bracket 1.

Lower and Upper Bases
The upper and lower bases are dimensioned considering the area necessary to accommodate a person with the feet aligned to the hip. Hence, the dimensions of the bases are 400 × 400 mm ( Figure 3). Both bases (upper and lower) basically differ in two aspects: the type of material and the thickness. The upper base is composed of naval aluminum AN5052, due to the proven ability to conduct forces by load cells (400 × 400 × 10 mm). The bottom base is made of AISI 1020 steel, as it is a ductile material and contributes to the stability and fixation of the platform (400 × 400 × 5 mm).

Load Cells
The material chosen for the manufacture of load cells ( Figure 4) is AISI304 stainless steel. The choice was made based on its hardness and elasticity coefficient, which together improve the measurement of electrical signals in the strain gauges [29].

Load Cell Mounting and Bearing Bracket
The brackets are designed for fixing the load cells ( Figure 5). For manufacturing, a 3/4" × 1/8" carbon steel angle bracket is used, with well-dimensioned holes (the diameter of the holes is the same as the diameter of the load cells).

Design of the Conditioning Circuit and Amplification
The strain gauge [29] presents extremely low resistance variations (in the milli ohms range). Therefore, a Wheatstone bridge [30] is used to obtain these resistance variations. With the proportional change of the impedances that are part of the circuit, the bridge loses its equilibrium state and there is a potential difference between the blocks. This variation, although small, can be easily detected when coupled to an amplifier circuit.
The design of the Wheatstone bridge scheme can be seen in Figure 6. Figure 6a represents the initial distribution given to the strain gauge in the load cell, and in Figure 6b, the electrical circuit of the bridge can be observed. The analyzes performed for the disposition of the strain gauges are presented in Section 2.2.3 (a). The equations used to calculate the voltages in the circuit are described as follows (Equations (1)-(3)): where R is the constant resistance of each strain gauges; ∆R is the resistance variation given by the mechanical deformation; V REF is the supply voltage of the bridge; and A is the instrumentation amplifier gain. Therefore, it can be concluded that, in an ideal scenario, where the Wheatstone bridges provide perfect balance, the implementation of the following circuit shown in Figure 7 would be adequate.

Component Simulations and Validation
In this section, the formalisms used in the stress, safety and deformation experiments performed on the load cell elements and the complete structure of the extensometric multiaxial force platform will be described.

• Von Mises Stress Analysis
The Von Mises Stress test is known as the equivalent force applied to each infinitesimal element in the part. Such force is given by the combination of the main stresses on the X, Y and Z axes. The equation that defines Von Mises Stress is given by (Equation (4)) [31].
where σ represents the stresses in the different axial components.

• Safety Factor Analysis
The safety factor indicates the ratio between the maximum stress supported and the current stress applied to the part. This value is necessary to assess structural failures arising from the application of forces. Its equation is given by (Equation (5)): where σ rup represents the breaking stress (maximum accepted by the part before breaking); σ adm is the voltage allowed by the part (the current applied voltage).

-Strain Analysis
Deformation analysis is crucial for this project once electrical signals can then be obtained to characterize the flight time and postural analysis of individuals.
Deformation is given by a dimensionless value, which relates the variation in length to the initial length. This value will be used directly on the equations related to the electrical resistance of the strain gauge. The equation used to characterize the deformation is given by Equations (6) and (7): where ∆d is the width variation of the piece; d is the initial width of the piece; ∆l é is the variation in length; and l is the starting length. From the strain equations, it is possible to obtain the Poisson's ratio equation, which relates the longitudinal and transversal deformations (Equation (8)) [32].
The data acquisition system is based on the manufacture and use of four hexagonal load cells distributed as support for a rectangular metal base. Each load cell must have four strain gauges distributed to offer thermal compensation and three-dimensional sensitivity. The strain gauges work from the variation of electrical resistance due to deformation. Therefore, a measurement alternative would be to use a Wheatstone bridge for every four sensors.
To validate the design of the load cells as well as their complete viability in the design of the force platform, a simulation environment is required for the design of the structure ( Figure 4). The analysis of the load cells is performed individually, thus characterizing the regions with the greatest strain and allowing the identification of the ideal regions for insertion of the strain gauges.

-Von Mises Stress Analysis
The first experiment is carried out applying a load of 700 N, which is shown in Figure 8. Analyzing Figure 8, it is possible to observe the points of the part that suffer the most equivalent effort and the intensity of the pressure submitted on each infinitesimal part, which makes it possible to compare with the stresses of plastic deformation and rupture of the material used. Table 2 shows the mechanical data for the materials used to feed the simulator when designing the load cells. Unlike the Von Mises stress analysis, the safety factor summarizes the possibility of failures, showing the direct relationship between the applied stress and the rupture stress. The results of the safety factor when applying a load of 700 N can be seen in Figure 9. When analyzing Figure 9, it is evident that the resulting minimum safety factor is equal to 3.28. This means that the current applied voltage is 3.28 times less than the maximum supported voltage. Therefore, the part is free from the possibility of breakage.

-Strain Analysis
With this analysis, it is possible to verify which points of the material will suffer the greatest deformation effect on the applied load conditions. This is a significant aspect for the current project, as it makes it possible to analyze the proper positioning of the Strain Gauges so that they obtain the greatest possible deformation, transmitting the electrical information with higher precision.
In Figure 10, it is possible to observe the deformation concentration points. On average, the greenish regions have a deformation equal to 1.22 × 10 −4 . This value will be directly related to the sensitivity equation of the Strain Gauge, which is later related to the variation in the voltage drop of the sensor. The equation that relates the deformation and the sensitivity of the sensor is given by Equation (9).
where GF is the gauge factor (given according to the component); ∆R is the resistance variation; R is the initial resistance of the component; and ε is the equivalent strain. Such equation makes it possible to calculate the resistance variation that will be directly linked to the signal acquired by the conditioning and amplification system. Evaluating the load cell individually to characterize the regions of greatest deformation is necessary to allow an effective location of the ideal regions for insertion of the strain gauges. To confirm the arrangement of the extensometers, the experiment in Figure 10 is repeated, now applying a load of 1000 N on the load cell.
It is possible to see in Figure 11 the deformation concentration on the sides of the load cell. This confirmation is used as a reference for the positioning of the extensors, as already observed in Figures 6 and 11.

(b) Lower and Upper Bases-Complete Platform
Autodesk Inventor was used to model and simulate the platform design (Figures 3-5). With the platform properly modeled and assembled in each of its projected parts, it is necessary to evaluate two mechanical characteristics. The first one refers to the regions of deformation concentration in the load cells and the second one, to the maximum loads supported.

-Von Mises Stress Analysis
For the Von Mises simulation, it is observed (Figure 12) that the load distributions in the cells were concentrated in points closer to the center of the platform (where the force is applied). This was critical to distribute the strain gauges, as the simulation in a single cell does not present or represent the tendency of forces, since the load was distributed symmetrically. -Safety Factor Analysis In Figure 13, the analysis of the safety factor on the complete platform is presented with the application of two 700 N forces, one at each end of the platform, and the addition of the gravitational force. The analysis of the safety factor is crucial for preventing material breakage under mechanical stress. The calculation of the safety factor is obtained from the relationship between the maximum load supported by the material and the current load applied, as can be seen in Equation (10).
where F rup is the breaking force of the material, and F adm is the allowable force (current force applied to the material).
Examining the results in Figure 13, safety factors very close to 1 or less than 1 are considered risky factors, as the material will act at its load limit. From the simulations, it was observed that, for the application of a static equivalent load of 1400 N (700 N at each end), the minimum safety factor was 2.28. This means that the material is operating at less than half the maximum supported force; therefore, there is no risk of early breakage.

-Strain Analysis
In the strain analysis, a central load of 1000 N is applied to the platform, which is approximately equivalent to 5 µm. In the simulation (Figure 14), the most reddish regions vary from 80 to 100 µm. This happens because of the changes made in the geometry of the load cells in relation to the reference geometry. However, if the safety factor margin is greater than 2, greater deformations will provide better results in data acquisition. It is important to note that these deformations allow greater variation in electrical resistance, which, in turn, is directly linked to the variation in electrical voltage in the acquisition circuit.

(c) Amplification Circuit for Wheatstone Bridge
In the design of an amplification circuit, some procedures are repeated to validate the efficiency of the circuit regarding the function that it must fulfill with the component where it will be implemented. In Section 2.2.2 (Figure 7), an ideal amplification circuit for the Wheatstone bridge is presented. However, to validate the circuit application in this project, it is necessary to simulate it over several resistance variations. In the real system (Figure 7), there are small variations in resistance due to several factors, such as the length of the connectors and manufacturing errors of the components.
To exemplify the influence of the bridge imbalance in the last amplification stage, a simulation was performed with a variation of only 2 ohms in one of the extensometers on the bridge. The output signal for the balanced circuit is presented in Figure 15. Therefore, when considering the stages of amplification with a total gain of 2000 times the input signal, the output signal with 7 µV can be easily disregarded due to its tiny magnitude when compared to the total gain. However, observing the circuit for the ideal bridge, in Figure 16 it is presented the amplification sequence in the stages when there is a difference of only 2 ohms in one of the extensometers. In Figure 16, it is possible to observe that the variation of only 2 ohms reflected a small variation of 14.6 mV in the Wheatstone bridge. At first, such tension appears to be insignificant; however, when reaching the second amplification stage, it can be observed that there was saturation of the operational amplifier, since the gain of the input signal exceeded the amplifier's power.
Finally, due to the extremely small voltage variations in the bridge, it was necessary to build several amplification steps with the appropriate offset adjustments and removal of the DC level generated by the bridge instability (constant difference of the bridge).
In Figure 17, the circuit for the equivalent system applied to each load cell is presented. Finally, when observing the equivalent circuit, there are three essential steps: -Acquisition of the signal from the Wheatstone bridge; -DC level control (offset); -Amplification stages.
The circuit was divided into three stages of amplification, and each stage includes a distinct amplification gain to adapt the signal without saturation of the amplifiers.

Sampling System
At the end of the signal amplification and filtering stages, it is necessary to perform its sampling. Therefore, a low-cost development platform known as Arduino UNO was used, which includes a digital analog converter with 10 bits of resolution, enabling the sending of data via serial interface to the computer where the information will be properly processed.
When acquiring the data, some characteristics must be considered, such as the resolution of the digital converter, which must not be too high. Therefore, the oversampling technique will be used, which corresponds to the increase in the sampling rate of the circuit. Then, it will be necessary to evaluate the harmonic content of the characteristic signal from the Wheatstone bridges. A mathematical representation of the process can be formulated following Equation (11).
(a n cos mπt T + b n sen ntπ T The next step was to complete the spectral analysis in a digital oscilloscope, which allowed the characterization of the components in terms of frequency and amplitude. In addition to the Fourier analysis, the waveform generated by the jumps (jump over the force platform) was also observed. Then, the maximum necessary frequency to be sampled to extract the appropriate information about the jump was characterized. From such experiments, it was observed that the maximum frequency does not exceed 50 Hz.
After characterization, Nyquist's theorem is applied, stating that the sampling frequency must be at least twice the highest harmonic frequency with considerable amplitude.
Therefore, knowing the Nyquist frequency, it is possible to configure the frequency of the digital analog converter, in addition to enabling the analysis to perform oversampling. Consequently, the microcontroller was configured to perform sampling every 10 ms (100 Hz), respecting the Nyquist rule, given that the maximum signal frequency is 50 Hz.
To complete the sampling cycle, it is necessary to send the data to the computer. For this purpose, the Arduino serial interface was used. To send the information, it was necessary to define the package structure, which includes information about the load cells and the preambles for the start and end of the package to ensure that it was sent completely. Hence, the data package has the structure shown in Figure 18.

User Interface
Data processing will be based on the temporal analysis of the signal obtained by the ADC converter. From the derivation of the signal, it will be possible to analyze the points with the greatest variation, making it possible to detect the moments when the athlete started and returned on the platform (dynamic of the jump on the force platform). From the start and end points, it is possible to analyze the duration time between peaks, which characterizes the athlete's flight time. From the flight time, it will be possible to apply equations from classical physics and determine various information pertinent to the athletes' analysis, such as the starting power, vertical displacement speed, mechanical impact and displacement of the center of mass.
The data presented were defined based on scientific articles related to the force platform with an emphasis on jumping. Some of the formulas that will be presented later use the athlete's flight time as an unknown number. To calculate the flight time, it is necessary to vary the time between the blue point (dt3, observed in the graph of Figure 19), the contact point after the jump and the dt1, moment of the athlete's jumping on the platform. Therefore, after obtaining the flight time, we can perform the following calculations: Initial Speed Jump Height In Figure 19, it is possible to observe three steps during the jump: • Time of impulse for the jump, moment when the body prepares to jump (dt1); • Flight time, moment when the body is in the air (dt2); • Fall time, moment when forces dissipate (dt3).   The calibration process is an essential event and is necessary for the correct reading balance in the forces received, calculated and processed by the extensometric multiaxial force platform (Figure 22). All interfaces and functions of the platform for the user were built using LabView. The objective was to optimize and speed up the acquisition and treatment of the signals received by the platform, and to present them to the user in a straightforward manner and with self-describing functions.

Force Platform
The applied methodology allowed an adequate detailing of each of the processes adopted throughout the platform development project, from the design, specification of the material used, modeling and simulation of all parts, conditioning and acquisition circuit and, finally, the sampling method and interface. The final prototype (Figure 23) resulted in a very robust and widely functional force platform with a development cost of 100 USD (considering materials, machining, and electronic components). The 3D project for machining, simulation, development code for signal processing, platform calibration and data visualization (LabView) is available with free access and reproduction on the link https://github.com/HelderGualberto/PI-VIII (accessed on 25 July 2021).

-Load Cells and Extensometers
A very common problem encountered in the use of strain gauges is the great influence of small variations in electrical resistance (in the milli ohms range). Due to the extremely high gain, these small resistance variations provide high levels of tension in the final amplification stage. Therefore, the imbalance of the bridge (variable with the length of the connecting wires, and even with the error in the resistances of the components) led to the construction of an offset adjustment on the bridge so that it is possible to balance the bridge from a trimpot. The major disadvantage of using this technique is the need to maintain the trimpot (TRIMPOT-1 in the circuit in Figure 14) without vibrations that alter its resistance and, consequently, unbalance the bridge. From the balanced bridge, the signal is sent to the first stage of amplification, with a gain equal to 100 times the input signal and, subsequently, to the second stage, there is a gain of 10 times. After the initial two stages, the signal undergoes a post-amplification offset adjustment, which is controlled by the TRIMPOT-2 shown in the circuit (Figure 14). This step will ensure control of the DC level of the output signal. This is very important to avoid saturation of the third amplification stage and to control the DC level for signal sampling, which will be dealt with later.

-Sampling System
Initially, the data package did not include any preamble, only the sequences of the most and least significant bytes referring to the load cell data. However, the loss of bytes was observed during the sending phase, which compromised the identification of the cells in the processing program (computer). Therefore, 4 bytes were added to identify the beginning and end of the packet, guaranteeing the sequence of its internal information. To perform serial communication between the microcontroller and the computer, an SDK called VISA (Virtual Instrument Software Architecture) was used in LabView. As the packets arrive, it is necessary to identify their order to ensure data synchrony and make corrections in case of packet loss.
A ring-shaped data structure was used to process the received data. This was necessary because LabView contexts work in an atomic way and even though the packages are coming out of order, there was no model implemented natively.
After the data sequences are validated, the information begins to pass through software filters. The first 10 s of the application consist of a calibration stage. This stage is performed to calculate an average of the signals received from the load cells so that it is possible to adjust the residual DC level in the data analysis steps.
-User Interface (Data Normalization) Due to the high instability of the measuring circuits, it was necessary to develop dedicated circuits for each load cell. As a result, it was possible to minimize errors arising from ambient noise and sudden variations in the electrical resistance of the circuit components. However, due to the non-standardization of the circuits, signals with distinct gains were obtained for each load cell. Therefore, to ensure that the system interprets the signals with the same proportion, it was necessary to perform a calibration, using a known weight, and the characteristic equation of each cell.

-Application of the Force Platform in the Flight Analysis of Volleyball Athletes
The project was designed to meet two objectives. The first objective is to improve the sensitivity and reduce the costs of the existing platforms. In this way, it is possible to make a more detailed reading due to the improvement in sensitivity presented in the developed project of the platform, where it was possible to evidence that this objective was achieved. The second objective is to use the platform for analysis and characterization of flight time and postural characterization of volleyball athletes. This postural characterization was used only to validate the function of the designed instrument and the parameters and methods chosen in the design and manufacture of the platform [33].
Research directed to the development of equipment that allows a postural and strength assessment are extremely necessary not only for health professionals in the process of rehabilitation of patients with postural and strength analysis, as well as sports professionals and athletes who seek to improve their performance with decreased chance of injury. As a result, there is an increase in physical strength with biomechanical correction, corroborating the delay in muscle fatigue and stress [34,35].
Experiments on a larger population, such as a volleyball team, should be the subject of further research in which a study and sampling model that can be submitted to the ethics board is considered, allowing a more extensive analysis of the developed instrument. The expectation is that there will be integration with two instruments already developed as part of a parallel study, such as surface electromyography (EMG) [36] and a low-cost portable electrocardiogram (ECG).
The ECG developed by our group as part of a parallel project [37] is a mobile device that uses a standard 12-lead ECG at a sampling frequency of 250 Hz per lead. There is a connection via Bluetooth 4.0 used as a communication and data transfer interface. Furthermore, the EMG has typical operating frequencies ranging from 10 Hz to 1 kHz (the EMG of our current prototype ranges between 3 and 50 Hz), it is portable and easy to communicate [36]. In the future, the objective is to integrate both the ECG and EMG with the force platform, thus compose a kit of instruments that allow a complete and adequate study of the impacts of muscle degradation on different types of individuals, not just athletes.

Conclusions
Currently, there are several tools and instruments for evaluating the performance of athletes; however, they have many limitations, either regarding the operation or their high acquisition cost. For this reason, it is necessary to design new tools that can monitor and provide reliable data and that are sensitive to configuration changes during the performance of experiments.
In this project, an accurate and low-cost instrument was developed, accessible to healthcare professionals specializing in rehabilitation and, in particular, for use in research laboratories in biomechanics of the body and biomedical engineering. In this project, we focused mainly on load cells, from which all readings were extracted as a result of the deformation these cells undergo during operational use of the force platform. The geometry of the load cell design facilitates the use and arrangement of the extensometers, as well as the reading of the received and processed signals through amplification and conditioning circuit that, in a simple way, guarantees the reliable and adequate reading of both extensometers and load cells. Studies in the literature present some force platform projects and their use; however, the detailing of the platform manufacturing process is deficient and quite restricted to the use of commercial load cells, easily adapted to any platform. In addition, they have a high cost, which makes them often inaccessible.
In this project, the suggested force platform is made from low-cost, common and non-exclusive materials, as they can be purchased at any machining company and even at recycling centers. All modeling, simulation, circuits and source code projects were shared in detail throughout this work with the objective not only of facilitating reproduction, but also the customization and optimization of the instrument and its functions. The choice of LabView as the language for the development of signal processing and user interface software was due to the researchers' familiarity with the language and the possibility of generating an executable file that does not need a license for its use, thus ceasing to be a restricted character solution.
Finally, the importance of developing force platforms to assess balance and strength goes beyond their exclusive use in athletes or in different types of diseases associated with the elderly population. Nowadays, diseases resulting from poor posture and muscle strength degradation affect not only middle-aged people, but also the younger generation, due to back pain and other types of illnesses, where some problems may be related to working conditions or sedentary lifestyle. Symptoms associated with a specific disease can be identified by assessing body balance, strength, muscle strength or flexibility, which could lead to the developed platform, considered a tool for early diagnosis, and thus can help in preventing some diseases from becoming chronic.