Design and development of patient-specific prosthetic socket for lower limb amputation

1. Introduction

There is a major and rising socioeconomic problem in the treatment and recovery of individuals after lower limb amputation. The Prosthetics and Orthotics of International Society states that there is a validate requirement for availability of modern technology in prosthetic limb components and there is need to develop evidence based practice in the clinical community [1]. There is significant occurrence of skin disorders [2] due to this need to transfer the elevated forces of compressive and shear across the prosthesis and limb of residual. To bear regular loads of compressive and shear the tissues of residuum are not used as the tissues of plantar in the foot are [3, 4]. Predicting the tissue damage of maximum internal strain at present preferred to surface stresses [5] so suitable models of elasticity, pre-strain from socket donation are necessary.

Relevant research made by the following works referenced included the generation of all geometry sample loads and boundary conditions including all pre-stresses from wearing of the socket [6] and the quasi-dynamic loading [7-9] the use of soft tissue predicted models demonstrating and capability nonlinear hyper elasticity [9, 10] and the subject variability is assessed by simulating various cases [9, 11]. The comparison between BKA socket studies other papers that modeled the socket [6, 12] indicates that this expectation induced an increase in interface stresses then various factors that effects of prosthetic user socket liners complicate the result.

Rehabilitation after amputation is generally aimed at restoring functional independence by encouraging the use of a prosthetic limb for ambulation. It also involves an iterative and labor-intensive method to suit a traditional prosthetic limb using a suspension socket [13, 14]. Due to feverishness, movement and moisture or over many months these factors can differ over the course when post-operative swelling subsides, muscles deterioration and fleshy tissues remodeling to allow the transfer of socket-skeleton load [15-17]. This condition will impact on the quality of life of a person by inconvenience and physical restrictions causing minor problems in human body’s movement system such as lower back pain, osteoporosis and osteoarthritis [18]. Inappropriate joint fit may causes to dermatological issues where as contact keratosis and dermatitis [2, 19] and the interior tissue strain and ischemia may follow to severe material damage in extreme cases [20]. Due to suffocation and longer exposure to the harmful material of the prosthesis [21] irritation and risk of skin infections are increased in a humid environment.

For instance the mechanism by which victims put in a liner to their limbs of residual before applying a socket can add trapped air that can cause skin rubbing, heat and potentially contribute to burning sensation [22]. Significant developments have been made in knowing the level of strain severity and extent of tissues [5]. The adaptive mechanisms are extremely complex and do not know much. Finite element analysis (FEA) is method for computational modeling that can provide comprehension of magnitudes and load distributions of soft tissue which can produce a base of evidence to design an assist socket prosthetist enabling recovery to be accelerated with decreased pain and expense of treatment [23]. In the study [24] has examined numerically pressures that the method help for design of prosthetic socket the result is significance of the interface discussed in the previous section.

Interface modeling yields prosthetic limb strain, shear stress which is interesting finding as they correspond to calculated quantities and model validation assistance [25]. Sanders et al. [26] conducted static measurements of COF between skin, socks, traditional socket and liner materials and related dynamic COF measurements were performed by Zhang and Mak [27]. The models for future might consider the effects of form elevated temperatures and humidity and formation presence of moisture, grease and sweat on the surface of the skin which as examined by Derler and Gerhardt [28] have been shown to have a highly variable impact on COF.

In following research [29] the values of COF as low that as 0.22 could be created by artificial sweat and hair likely by adhesion inhibition of stratum corneum cells to the surface [26]. While sweat and sebum can produce effects of lubrication and shear stress reduction formed on the skin in adequate amounts the threshold strains can also be reduced sustainably before tissue damage occurs [30]. Tonuk and Silver-Thorn [31] for indentation test and FEA analysis a hyperelastic soft tissue model was used. Residuum Risk Factor Parameter Report the established methodology that informed the majority of successive studies was presented [32]. After inserting a socket [33] thermal conditions in residual limb tissues were considered and their models validated against experimental at rest for measurement of surface temperature.

In conjunction with structural research such simulations are of future use for determining the combined effect of mechanical deformation. By influencing its mechanical stiffness and strength [34] high temperatures have an impact on the skin thereby raising the risk of tissue damage [35]. High humidity can also soften the skin and increase cellular permeability resulting in an increased susceptibility to skin irritation [36]. Moist skin will also have an increased friction coefficient in certain cases resulting in elevated shear forces at the device-skin interface [38]. In the 1980’s researchers in Texas [38] and University College London [24, 39] made the CAD/CAM based prosthesis fitting method and Goh et al. showed FE code could be combined directly with a CAD software package [40] contrasting experimental measurements of pressure with FE predictions at different locations of socket sites. To test goodness-of-fit they suggested predefine pressures by using FEA to iterate the socket design and noted need for more work to correlate the pressure to a customized measurement of ache [41].

This study focused on different technique for design and fabrication of the specific socket. In this method simple and easy procedure were used for converting the scan CT images of stump which is in DICOM (Digital Imaging and communication in medicine) format to .STL file format for designing of socket. In this method designing of socket for patient as explained below and static structural and explicit dynamics analysis were analyzed. Fabrication of socket by using additive manufacturing technology.

The source of data for medical model which can be customized in future of various patients additive manufacturing which helps in solving different medical problems [42]. During COVID-19 pandemic mainly the shortage of medical equipment the personal protective equipment. To develop complex products in short time with minimal human effect by using the 3D printing can develop medical equipment easily [43]. Polylactic acid which is used for developing of 3D printing product. The behavior and mechanical properties are high which can print the 3D printing product easily [44, 45].

2. Methodology

2.1. Geometry creation using reverse engineering technique

This study focused on developing a stump-socket model using a subject specific CT (Computed tomography) image. Next step is to convert the scan CT images which are in DICOM (Digital Imaging and communication in medicine) format to an nrrd (nearly raw raster data) file by using 3D Slicer software. By importing CT images folder into 3D Slicer software and save that file in nrrd format. Embodi3D is the free service that will convert the scan into a 3D printable model file and Converts an nrrd (nearly raw raster data) file to STL format. The stump was obtained using 3D Slicer and embodi3D image processing software. As shown in Fig. 1 is the stump model which is generated by reverse engineering technique.

Fig. 1Stump model

The stump model which is obtained is then imported into Meshmixer software. By using the design tools in Meshmixer created socket model with reference to stump model. The stump-socket models were imported into Solidworks for converting into solid model and assembled. The assembled model is later imported into ANSYS for simulation. As shown Fig. 2 below is geometry model of stump-socket.

Fig. 2Stump-socket CAD model

2.4. Experimental setup

During the preparation of socket the comfort and flexibility of socket for patient is to be consider in order to reduce stress on the stump. For exactly fitting of socket to the patient stump is prepared by using 3D printing by printing technology of fused filament fabrication. Specification for the 3D printer for preparing socket is diameter for filament extruder is 1.75 mm, filament diameter is about 1.75+0.1 mm and operation temperature about 260 °C. This 3D printer is used for reduction cost for the patient socket. Socket is mainly prepared by the material acrylonitrile butadiene styrene. For this 3D printer Replicator G software is used for printing process in 3D printer. The 3D printer supports STL and g code files and print files upload through SD card or over USB devices. As shown in Fig. 3 is preparation setup of software for 3D printing.

Fig. 3Socket model in 3D printer

3. Results and discussion

3.1. Meshing and boundary conditions

In workbench the mesh element used here is Hexagonal in nature and the size of the mesh (face mesh) is about 0.01 m. The number of nodes is 8144 whereas the number of elements is 29379. Now the loads have to be applied for the meshed volume. For simulation, the degrees of freedom (DOF) of one end of the socket is constrained and force of 500 N for static structural and velocity of 10 m/s for explicit dynamics were applied to the stump. In Fig. 4 as shown represents the direction of force applied in static structural.

Fig. 4Static structural force direction

3.2. Analysis type

Here Static analysis and explicit dynamic analysis were carried out to determine the deformation, stresses between stump and socket under the given loading conditions. The Static Structural analysis and explicit dynamics can be found in the software toolbox in Ansys software.

3.2.1. Static structural analysis

In static structural analysis force of 500 N is applied in direction towards stump as shown in Fig. 4. The extreme and lowest deformation of the prosthetic socket and stump model made of the acrylonitrile butadiene styrene and Mooney Rivlin model under the given boundary conditions was shown in the Fig. 5. The different colour indicates values of deformation as shown in left side portion of Fig. 5. In this static structural total deformation obtained maximum at 3.5172e-006 m due to maximum load acting at that portion of socket.

Fig. 5Total deformation of the stump-socket interface

As shown in Fig. 6 the Von-Mises Stress of the stump-socket model made of the acrylonitrile butadiene styrene and Mooney-Rivlin model under the given boundary conditions. Minimum of von-mises stress was found to be 2124.9 Pa and maximum of von-mises stress was found to be 6.5857e+006 Pa respectively.

Fig. 6Von-Mises stress of the stump-socket interface

In static structural analysis graph plotted between force and time as shown in the Fig. 7. Force is linearly increased with increasing of time. The force 500 N maximum is obtained at time 1 sec. In the Fig. 7, the linear relationship is follow as increasing of force with an increase of time may slope constant.

Fig. 7Static structural analysis force vs time

3.2.2. Explicit dynamics analysis

In explicit dynamics analysis velocity of 10 m/s for were applied to the stump down towards the socket. The extreme and lowest deformation of the prosthetic socket and stump model made of the acrylonitrile butadiene styrene and Mooney Rivlin model under the given boundary conditions was found to be 0 m and 3.539e-002m respectively as shown in Fig. 8. Obtained total deformation maximum at 0.03539 m.

In Explicit dynamics analysis of total deformation graph is plotted between deformation and time. In Fig. 9, as Increasing of time the deformation also increasing linearly but deformation is slightly increase high at time period of 2.4e-03 to 3.0001e-02.

The extreme and lowest Von-Mises Stress of the stump-socket model made of the acrylonitrile butadiene styrene and Mooney-Rivlin model under the given boundary conditions as shown in Fig. 10. From the results observed that maximum obtain Von-Mises stress at 3.5893e5 Pa.

In Explicit dynamics analysis of total deformation graph is plotted between equivalent stress and time which is varying (Increasing and decreasing) along with the time as shown in Fig. 11.

Fig. 8Total deformation of the stump-socket interface

Fig. 9Dynamic structural analysis deformation vs time

Fig. 10Von-Mises stress of the stump-socket interface

Fig. 11Dynamic structural analysis equivalent stress vs time

4. Experimental analysis

Preparing of socket by using 3D printer for the dimensional accuracy. It is the best process for simple, easy and takes less time for of making socket. In the experimental analysis power input for 3D printer is 220 V/110 V and output about 200 W. The layer thickness is about 0.1-0.5 mm (100 microns). Maximum extrusion temperature is 230 °C. $X$, $Y$ axis positioning resolution is about 0.02 mm and $Z$ axis positioning resolution is 0.005 mm. The socket model is manufactured by using 3D printer by using material of acrylonitrile butadiene styrene as shown in the Fig. 12 below. Finally printed socket by using 3D printer as shown in Fig. 13.

Fig. 12Printing of socket on 3D printer

Fig. 13Final socket prepared by using 3D printing

5. Conclusions

The pressures exhibited tendency obtained from the results for both the static structural and explicit dynamics sockets were shown. The shape of the sockets ensures the behavior of the stump for every subject was mostly similar. Measurement differences of static structural analysis and explicit dynamics were observed. The reason is because of the period during which the subject wearing the socket. Due to reducing in elasticity of the muscle prosthetic socket user experiencing continuous fluctuations of shape and volume daily. The elasticity of the soft tissue reduction contributes to maximization of the tri-axial force. It was known according to the FEA, to the stump model remained acrylonitrile butadiene styrene with viscoelastic, homogenous and the elasticity. Acrylonitrile butadiene styrene is the material which is primarily used for the fabrication of the prosthetic socket was examined to study the consequence of materials on the mechanical behavior of the stump-socket interface under given loading conditions. In addition, with static structural analysis explicit dynamic analysis was also assessed to study the outcome of dynamic simulations. The results obtained manifest that the stump-socket interface has a significant impact on the deformation and von-mises stress between stump and socket.