Long term orthotic bracing is a very common nonsurgical therapy for the treatment of spine diseases [1, 2]. Although there is evidence for the use of physiotherapy to address moderate spinal deformities, such as idiopathic scoliosis, brace treatment is preferred, often in combination with scoliosis specific daily rehabilitation, especially during the pubertal growth spurt [3, 4]. Scoliosis is defined as a structural abnormal curvature of the spine, typically over 10° for Cobb measurement in the frontal plane. Depending on type, localization, structural rigidity, and severity of scoliosis, the effects of orthopedic braces can be limited to stabilization or extended also to correction of spine and chest deformities. Braces are shaped as to produce forces in definite anatomical regions keeping others unloaded, typically with a three-point bending system configuration [5, 6].

The design and manufacturing of a customized scoliosis brace is a complex process. Orthotists rely on personal experience and patients expectations to design an effective device with acceptable comfort. There is currently no unique standard for producing scoliosis braces. All manufacturing methods are currently based on producing a positive mold of the patient’s body [4]. The mold can be realized either using plaster of Paris or via 3D scanning and computerized milling. In both cases, the orthotist manually adjusts the mold, sculpting and smoothing some regions according to medical prescriptions, manual measurements, and experience. The brace is then obtained by wrapping the positive mold with a preheated polymer sheet (thermoforming process). Sometimes, vacuum is used to improve adhesion. The brace is finalized by cropping and sanding the edges and applying straps for closing [7]. All these activities are currently performed manually by expert technicians with direct application on the patient. Thermoforming the plastic sheet does not allow to finely control the thickness and to obtain complex shapes or textures, with limitations of functionality, aesthetics, and comfort. Discomfort and unpleasantness lower the acceptance of braces by young patients, affecting their compliance to the therapy. In addition, due to the custom nature of these devices and the evolving conditions related to deformity correction and growth, each brace requires a new positive mold, whose disposal causes issues of waste management and costs.

Recently, the introduction of additive manufacturing, also known as three-dimensional printing (3DP), has shown a great potential for obtaining patient-specific solutions in the medical field [8, 9]. This technique enables to create complex and customized devices based on digital models [10,11,12]. 3DP is environmentally friendly, produces limited waste material, and does not require molds. Each part can be customized and replicated without additional preparation cost. Less handwork is needed, reducing the risks of human errors and improving interoperator repeatability [13, 14]. Several 3DP methods have been applied in healthcare, such as poly jet modeling (PJM), selective laser sintering (SLS), stereolithography (SLA), and fused deposition modeling (FDM).

Currently, the major limiting factors for producing large orthotic devices by 3DP are processing times and high equipment costs (in particular, for PJM and SLS). However, among these technologies, FDM is the least expensive and the most suitable to produce scoliosis braces, despite a slightly lower dimensional accuracy. A few papers proposed the use of 3DP to fabricate orthotic devices [15, 16]. Most of these studies focused on the possibility of obtaining devices with accurate shapes and geometrical dimensions, but only few considerations related to costs and mechanical performances of these devices are reported. Moreover, information on the mechanical properties in filament datasheets often refer to the bulk material before 3DP, while mechanical characterization of printed parts is scarce and mainly focused on tensile properties [17]. Furthermore, impact tests are important to quantify the toughness of a material, by measuring the amount of energy absorbed during high-strain-rate conditions before failure. This behavior certainly changes with different production technologies, such as 3DP [18]. For these reasons, it is not yet possible to predict how the combination of virtual modeling and additive manufacturing processes affects the mechanical properties of a 3D printed brace.

This work aims to evaluate the feasibility of producing a patient-specific orthopedic scoliosis brace by 3DP and to report on its competitiveness in terms of cost, performance, and acceptance compared to a thermoformed brace. To this purpose, the thermoformed brace of a volunteer patient affected by idiopathic scoliosis was reproduced by 3DP using reverse engineering techniques. Material selection, morphological and mechanical characterization of selected materials, as well as cost analysis of the process were carried out. The 3D printed brace was finally tested with the volunteer patient, and further deformation and morphological analyses were performed. Performance, acceptability, safety, and satisfaction of the brace were evaluated through a short questionnaire, and thermographic imaging was used to check mechanical effectiveness.

Materials and methods

Preliminary material screening

A preliminary comparison of the most common commercial filaments available for FDM 3DP was performed using a software database (CES Edupack, Granta Design, UK) and the fabricants’ datasheets. The following features were assessed on a scale from 1 to 3 (acceptable, good, and excellent): durability, printability, toughness, hydrophobicity, chemical inertness, flexibility, and fatigue resistance. Scoliosis braces are typically used over a t-shirt and not directly in contact with the patient’s body; nevertheless, biocompatibility is still of concern. For this reason, availability of medical grade filaments was also reported.

Reverse engineering and 3D model preparation

A virtual replica of the custom-thermoformed brace worn by a patient affected by scoliosis was created by reverse engineering. An infrared triangulation scanner (Structure Sensor, Occipital Inc., USA), adequate for orthopedic applications, connected to a computer via USB and controlled via software (Skanect, Occipital Inc., USA) was used [19]. The initial scan was processed with the general-purpose sculpting CAD software Meshmixer (Autodesk, USA).

Printer settings and test samples

A Delta 4070 Pro (Wasp, Italy) FDM printer was used. This machine has a large cylindrical build volume (400-mm diameter and 670-mm height) that well complies with the dimensions of back braces. It is a delta-style printer, preferred for rounded shapes (e.g., cylinders) with respect to Cartesian-style printers [20]. The printer was equipped with a nozzle with a diameter of 1.2 mm, which was the largest available for filaments of 1.75 mm, with the goal of reducing the printing time as much as possible.

The settings were preliminary tested by printing hemicylinder samples (Fig. 1a and b), representative of a section of the back brace. The hemicylinders of 150-mm diameter, 50 mm in height, and 2 mm of thickness were created with the CAD software Autodesk Inventor and exported as STL file with the preset high level of accuracy, thus obtaining 1190 triangles. The dimensions were decided after measuring the section of a real brace on the reverse engineered 3D model. A short straight part of 30 mm was extruded on an end of the hemicylinder as it is representative of the regions on the back of the brace, where the curvature decreases and tends to zero. The basic printing parameters for the filament were 240 °C for extruder temperature, 90 °C for build plate temperature, and 50 mm/s for print speed. To evaluate the effect of increasing layer height on the resulting quality and the mechanical properties, three nominal layer thicknesses were considered: 0.4, 0.6, and 0.8 mm. The g-code files were prepared with the slicing software Cura (Ultimaker, the Netherlands).

Fig. 1
figure 1

a Sliced CAD hemicylindrical model ready for printing, where the model is depicted in red and the brim support in blue on the grid of the printing bed, and b printed PETG sample

Characterization of 3D printed test samples

Surface analysis of the 3D printed hemicylindrical samples was performed with a FEI Quanta 200 FEG (Thermo Fisher Scientific, USA) scanning electron microscope (SEM) operating at 20 kV. The pieces were coated with gold with a sputter coater (SC500, Emscope, UK) before being observed under the microscope.

Tensile properties were evaluated at room temperature by an Instron machine using a load cell of 1kN and a crosshead speed of 1 mm/min. Dumbbell shape specimens were cut from the 3D printed samples and from of the thermoformed polypropylene (PP) and polyethylene (PE) braces according to the ASTM D1708 standard. The study was carried out analyzing five samples for each specimen type. The test was performed considering two fiber orientations: longitudinal (L) and transversal (T) to the loading direction (Fig. 2a). The tensile modulus was calculated between 0.05 and 0.20% strain by a linear regression calculation. Then, mean values and standard deviations were calculated for each specimen series.

Fig. 2
figure 2

Fiber orientation with respect to force direction in dumbbell specimens for tensile tests (a) and in V-notched specimens for impact tests (b)

Charpy impact tests were performed to compare the energy absorption (Ec) of the different samples, verifying also the effects of fiber orientation and layer thickness. Specimens (13.0-mm wide, 2.5-mm thick, and 60.0-mm long) with a notch depth-to-width ratio of 0.3 were tested at room temperature by using an instrumented apparatus (CEAST Mod. 6545, Instron, Italy) equipped with a Charpy pendulum hammer, setting an impact energy of 3.6 J and an impact speed of 1 m/s. Also impact tests were performed considering two different fiber orientations: longitudinal (L) and transversal (T) to the impact force (Fig. 2b). Each set consisted of five specimens for a given material sample, which enabled to compute average and standard deviations of Ec.

Cost model

A cost model was developed by combining different cost calculation models described in the literature, adapting it for the specific case of back braces [21, 22]. The model parameters included printer type, materials, and back brace geometry.

The overall cost (Cbrace [€]) was estimated by accumulation of four subcosts: machine purchase cost (P), machine operation cost (O), material cost (M), and labor cost (L), as shown in Eq. 1.

$$ {C}_{\mathrm{brace}}=P+O+M+L $$

We considered the total build time (Tb [h]) depending on processing time (Ts) and delay time (Td), where Td is the accumulation of delays before and after printing each layer (Lp) and start-up time (Tstartup).

$$ {T}_b={T}_d+{T}_s=\left\{{L}_p\times \left({T}_{\mathrm{pre}}+{T}_{\mathrm{post}}\right)+{T}_{\mathrm{startup}}\right\}+{T}_s $$

P was thus computed as the product of Tb and purchase cost (Pc [€]) normalized over useful hours, as shown in Eq. 3. We assumed that orthotists would use the machine 20% of its useful life (Ylife [years]), due to their weekly schedule.

$$ P=\frac{T_b\times {P}_c}{0.2\times 24\left[\frac{\mathrm{hours}}{\mathrm{day}}\right]\times 365\left[\frac{\mathrm{day}\mathrm{s}}{\mathrm{year}}\right]\times {Y}_{\mathrm{life}}} $$

The machine operation cost (O) was computed as the product of operation rate (Co [€/h]) and build time (Tb), as shown in Eq. 4. Co is an empirically determined constant, correlated to maintenance, consumption of utilities, and cost of space.

$$ O={T}_b\times {C}_o $$

The material subcost (M) was computed on the material purchase cost (Cm [€/kg]). In particular, Cm is weighted by the support structure factor (Ks), which captures the percentage of additional material for support structures. Ks is equal to 1 without supports, but typically ranges from 1.1 to 1.5 (i.e., 10 to 50% for supports). The other factors N, ν, and ρ represent number of parts, part volume [cm3], and material density [kg/cm3], respectively.

$$ M={K}_s\times N\times \upnu \times \rho \times {C}_m $$

Finally, labor cost (L) was computed as product of labor time (Tl [h]) and labor rate (Cl [€/h]), representing the salary of the orthopedic technician (Eq. 6).

$$ L={T}_l\times {C}_l $$

Pilot patient case

The printed brace was tested by a patient affected by scoliosis, who had been already using the corresponding custom-thermoformed brace for 1 year. The patient wore the 3D printed brace continuously for 2 weeks, with a clinical indication to wear the brace for at least 22 h per day like the traditional one. At the end of the 2 weeks, the patient completed a short questionnaire about acceptance, safety, and satisfaction of the 3D printed brace, compared with the traditional brace produced by thermoforming. Moreover, thermographic images were obtained using an infrared thermal camera (One, Flir, USA) to objectively compare braces performances [18]. This study was performed in accordance with the Declaration of Helsinki, and the protocol was approved by the IRCCS E. Medea Ethics Committee. The patient gave written informed consent in accordance with the Declaration of Helsinki.

Analysis of the back brace after the pilot patient test

3D scanning of the brace after use was performed with a commercial scanner (Sense™ 3D scanner, 3D Systems Inc., USA). The 3D scanner was operated in the handheld mode, held at a suitable height and fixed distance (0.5 m), and moved around the brace.

The captured 3D image was exported to Rhinoceros CAD Software (Robert McNeel & Associates, USA) to extract the final 3D model. A Boolean difference operation was applied between the 3D model of the brace before and after use. The resulting object surface encloses a volume which is the volume belonging to the brace after use but not to that of the original 3D model. For illustrative purposes, the resulting surface was used to create a colored deformation map on the 3D model of the original brace. Moreover a morphological analysis of the back brace after the pilot patient test has been conducted by SEM. Two samples have been cut from the most deformed zone as indicated in Fig. 10, and they have been analyzed by SEM as described in paragraph 2.4.


Preliminary material screening

Common materials used in the thermoforming of braces include polyethylene (PE), polypropylene (PP), and polyethylene foam.

Among the materials listed in Table 1, polylactic acid (PLA) and polyethylene terephthalate glycol-modified (PETG) show the best combination of mechanical properties, processing parameters and low purchase cost; in particular, PETG presents mechanical properties more appropriate for the application (e.g., toughness and hydrophobicity). Therefore, a commercial 1.75-mm diameter PETG filament (Zhuhai Sunlu Industrial Co., China) was selected for the realization of the 3D printed back brace.

Table 1 Preliminary comparison and assessment of typical materials available for FDM 3D printers, using data from the database CES EduPack (Granta Design, UK) and filament datasheets.

Reverse engineering of the traditional scoliosis brace

The initial 3D scan of the brace took 1 min. The mesh was repaired, and the model was cleaned by removing artifacts. The shape of the frontal straps was removed from the external surface. The inner surface was then used as reference to generate the correct external surface. Finally, the model was completed by deleting the internal surfaces, by cropping the border and by applying a uniform thickness of 2.2 mm to produce the final solid model. Figure 3 shows the main steps required to obtain the 3D model ready for the slicing software. One hour of working was necessary for the model preparation.

Fig. 3
figure 3

Reverse engineering steps on the existing patient-specific thermoformed brace. The initial mesh was repaired and artefacts were removed (a), frontal straps were removed from the external surface (b), and the new outer surface was regenerated using as reference the inner surface, which was then removed (c). Finally, the border was cropped and a uniform thickness of 2.2 mm was applied (d)

Printer settings

The printer settings in terms of print speed, nozzle temperature, bed temperature, layer height, and extrusion rate were experimentally determined by printing hemi-cylindrical samples (Fig. 1a–b).

Layer height has a direct impact on the printing duration: 23, 15, and 11 min are required to print hemicylinders with 0.4-, 0.6-, and 0.8-mm layer height, respectively.

Characterization of 3D printed test samples

Figure 4 shows the SEM images of the PETG samples surface with different layer thicknesses and of a thermoformed PP sample. At × 100 magnification (Fig. 4a, c, and e), the PETG samples present a uniform surface finishing, without evident defects (e.g., holes or inclusions) for all the three layer heights. The images at higher resolution (× 1000—Fig. 4b, d, and f) also revealed that all samples presented a correct continuous interface between layers.

Fig. 4
figure 4

Scanning electron microscopy image of 3D printed PETG samples and PP thermoformed sample showing roughness and layer interfaces quality at × 100 (a, c, e, g) and at × 1000 (b, d, f, g). PETG samples with different layer heights (ab 0.4 mm; cd 0.6 mm; ef 0.8 mm) and reference thermoformed PP (g, h)

An extensive experimental section was designed to study the effects of layer thickness on ultimate strength and elastic modulus of printed specimens at a range of layer thicknesses. Stress-strain (σ-ε) curves of 3D printed PETG samples are reported in Fig. 5a and b. The mechanical characteristics of 3D printed specimens were compared with samples obtained from thermoformed PE and PP sheets. Given the stress-strain curves, it was possible to calculate some significant parameters, which characterize each sample such as the tensile strength (σmax) elongation at break (εmax) and the Young modulus (E’). From the σ-ε curve depicted in Fig. 5a, it is possible to assess that 3D printed PETG in L direction showed a typical ductile behavior similar to the one of PP and PE polymers. All the samples exhibit at first a quasi-linear increase of stress as function of strain. After this elastic area, the samples undergo plastic deformation, and stress increases less rapidly until the point of maximum stress (σmax). Finally, stress decreases as strain increases, until the specimen reaches failure (εmax). Figure 5b reports the elastic part of the σ-ε curve to better understand the different mechanical behavior of the analyzed materials. PETG showed higher elastic modulus in respect to the other two polymers and lower deformation at break. This means that the back brace 3D printed in PETG results stiffer if compared with the thermoformed PP and PE. In particular, PE showed the lowest elastic modulus, but the highest value of elongation at break that resulted to be one order of magnitude higher if compared with the other materials, which is out of scale in Fig. 5a with a value of about 13 mm/mm.

Fig. 5
figure 5

a Stress vs strain curves for 3D printed PETG samples tested in L direction compared with thermoformed samples obtained from a commercial back brace; b elastic region of the stress-strain curves

To better understand the correlation between different thicknesses and mechanical properties, mean and standard deviation of test results have been reported in Fig. 6. The data show the large variation of properties of samples between L and T direction. Regarding the test in L direction (Fig. 6a, b, and c), the average values among the selected layer heights showed no large discrepancies. The elastic modulus averages varied from 1.48 ± 0.05 GPa of the 0.6-mm samples to the 1.37 ± 0.07 GPa of the 0.4-mm ones, while tensile strength varied from 56.26 ± 0.57 MPa of the 0.6-mm samples to the 48.30 ± 7.64 MPa of the 0.4-mm ones. Regarding the elongation at break 0.4-mm samples showed the highest value of εmax equal to 2.11 ± 0.108. Thus, it is possible to assess that PETG samples, tested in L direction, produced higher values of E’ and σmax close to the declared values of the datasheets of the bulk material (E’ = 2.1 GPa, σmax = 50 MPa). On average, the mechanical property values of 3D printed samples in L direction resulted comparable with the properties of PP and PE samples. In particular, PETG resulted similar in terms of elastic modulus and elongation at break with PP, but more rigid and brittle if compared with PE. When the force applied was transversal (T) to the fibers (Fig. 6d, e, and f) E’ and σmax slightly decreased but remained comparable with the values of PP and PE. On the contrary, εmax was lower of about two orders of magnitude in respect to the values in L direction, varying between 0.037 ± 0.003 mm/mm for 0.4-mm sample to 0.019 ± 0.002 mm/mm for 0.6-mm sample.

Fig. 6
figure 6

Results of tensile tests on dumbbell shape specimens. Effect of layer thickness and fiber orientation on printed PETG samples compared with thermoformed PP and PE samples. a, b, and c The tests with fibers longitudinal to the loading direction (L); d, e, and f the tests with fibers in the transverse direction (T)

The impact test results of printed PETG show that, by increasing the layer thickness, the absorbed energy (Ec) decreases in both cases of fiber orientation. Moreover, the build orientation significantly influenced the resistance, highlighting a remarkable anisotropy. In the case of impact loading parallel to the fibers (L), the absorbed energy (Ec) was about 2 orders of magnitude lower than the one measured for the transverse direction (T), as reported in Table 2. Tests have been performed also on PP and PE, but the samples did not break because the impact energy was below the value necessary for fracture [23]. For this reason, Table 2 reports literature results which are one order of magnitude higher than the best PETG.

Table 2 Results of absorbed energy (Ec) in Charpy impact tests on the V-notched specimens of 3D printed PETG samples with the two fiber orientations (parallel to loading L and transversal T). The values for PP and PE were taken from literature 19, because the specimens did not break in our experiments for limited impact energy

Cost model

Table 3 shows a detailed breakdown of the costs and the printing parameters associated with the 3DP process when printing the back brace on the WASP Delta 4070 PRO FDM printer. The machine purchase price (Pc) was 7000 € and its useful life (Ylife) is expected to be 7 years. Tb was obtained by Eq. 2, where Tpre and Tpost are equal to zero for FDM technology, as the printing is continuous, while Tstartup is about 30 minutes for calibration and warm-up. In this study, we set the scanning time (Ts) equal to the estimated time needed to print the back brace, obtained from the g-code file, as it strongly depends on process parameters (e.g., layer height and printing speed).

Table 3 Detailed cost breakdown of the proposed cost model for producing a back brace in PETG with an FDM 3D printer, in the three selected cases of 0.4, 0.6, and 0.8 mm for the layer height

To compute the machine operative cost O, we empirically determined an operation rate (Co) of 4.75 €/h. The material cost (M) was computed with a support structure factor equal to 1.2 and we expect to print one brace at a time (N = 1). Part volume was obtained from the CAD file (417 cm3). The PETG filament had a cost of 30 €/kg, while its declared density was 1.27 g/cm3. Finally, the labor rate for the orthopedic technician is 25 €/h and labor time was 2 h, including model preparation, printer setup and manual operations on the printed back brace.

By combining the different contributes, the overall cost (C) of the back brace would be 109.57, 94.93, and 90.05 € when printed with a layer height of 0.4 mm, 0.6 mm, and 0.8 mm, respectively.

Back brace manufacturing and patient test

The final back brace was printed in PETG with a layer height of 0.6 mm, to comply with the time limit of a working day, having a printing time of 4 h and 33 min. The brace was printed with two walls equal to the nozzle diameter and printed upside-down to limit the required supports (Fig. 7a–c). A small support was produced with a single line deposition with “zig-zag” path, as a compromise between good stability and ease to remove the supports from the brace. The bounding box containing the brace measures 302 mm in vertical direction, 298 mm in the lateral direction and 216 mm in the front-to-back direction.

Fig. 7
figure 7

Brace 3D printing and patient test. Printing setup of the brace in Ultimaker CURA (a), where the model is depicted in red and the supports in blue. A detailed view of the “zig-zag” path for the support structure (b). 3D printed brace on build plate inside the large 4070 delta printer (c) and worn by the volunteer patient after final refinement by the orthotist (d)

The brace was then removed from the 3D printer build plate, and the supports were easily detached manually. The mass of the final brace is 530 g after removing the supports (16 g), comparable with the 510 g of the thermoformed version, both considered without the closure straps. An experienced orthotist completed the finishing of the borders and applied the closure straps, using routine tools (grinder, drill, and riveter) available in orthopedic workshops, for additional 30 min. Finally, the brace was worn by the subject, and minor adjustments were done.

The patient was compliant and wore the 3D printed brace continuously for 2 weeks. With respect to the traditional thermoformed orthosis, the patient reported less discomfort and an increased supporting action due to the higher stiffness of the brace. An improved wearability and a greater ease in performing activities of daily living were also conveyed through the short questionnaire. In contrast, the patient reported the feeling that the 3D printed brace was more brittle compared with the traditionally manufactured orthosis. Infrared thermography images did not show significant differences in superficial temperature between the two brace types (Fig. 8a and b).

Fig. 8
figure 8

Infrared thermographic images of the posterior side of the patient wearing the traditional thermoformed brace (a) and the 3D printed brace (b) with relative temperature scale bar

A deformation analysis of the 3D printed back brace after the patient test has been conducted in order to understand any macrorelaxation/deformation of the structure (Fig. 10). The back brace after the patient test have been scanned and compared with the 3D back brace before the test.

In Fig. 9, the different colors indicate the distribution of deformations over the entire structure after use. It is quite evident that the deformations are homogeneous and symmetrical on the whole brace. In particular, all the contours are deformed outward due to the tensions produced during use (green area). High levels of deformation are located at the rear where the brace is most mechanically stressed during the wear process. Localized deformations are also present on the front of the brace. The stress produced by the presence of the closing straps is probably responsible for these deformations. In any case, the total deformations are small and unable to compromise the structural functionality of the brace. It can be concluded that the 3D printed structure is able to properly resist the fatigue produced during use by the patient, which is a very important result. In fact, an uncontrolled mechanical relaxation of the structure would have compromised the functionality of the orthopedic device.

Fig. 9
figure 9

Deformation analysis of the 3D printed back brace after the patient test a back lateral view; b front lateral view, c front view, and d back view of the back brace. Positive deformation with outward direction (green), null deformation (pink), and negative deformation (blue)

Starting from these results, an analysis of the morphology of the brace surface was conducted. The aim was to verify the state of the structure at the microscopic level near the highest deformations. Figure 10 shows SEM images of material samples taken from two different positions as showed from in Fig. 10, corresponding to two extreme deformations (outward and inward).

Fig. 10
figure 10

SEM images of samples cut from the 3D printed back brace after the patient test in the two extreme deformation areas, at × 100 of magnification (Scale bar represents 1 mm)

From the SEM images shown in Fig. 10, it is evident that after two weeks of testing the structure of the brace at the microscopic level is intact. In fact, there are no visible microcracks or delamination between the different printed layers. This means that the structure of the brace did not change during use, maintaining its mechanical integrity.

Even comparing the images of Fig. 10 with those of Fig. 4, there are no differences. The only difference is given by the presence of small fragments or dirt particles present on the surface of the brace. These are probably the result of daily patient use.


Reverse engineering and 3D printing

The 3D model preprocessing phases (smoothing, artifact removal, external surface creation, and thickening) of the brace took approximately 1 h, which is comparable with the time required to prepare a CAD model and set the CAM module for the milling machine, obtaining the positive mold in the current production process.

Printing tests showed that layer height greatly affected results in terms of printing duration, while surface quality and mechanical parameters were only partially influenced by this parameter. However, this is a crucial aspect to consider when scaling up the production and further tests are required to establish the optimal tradeoff between printing duration and product quality.

The overall production time from initial scanning to delivery to the patient took approximately a full working day, similarly to what is required by the modern thermoforming process. However, the total man-hours are reduced because of the minimal supervision necessary during the 3D printing.

The machinability of the 3D printed brace was slightly lower than that of traditional thermoformed braces: the jigsaw was not used for the possible delamination of printed layers, and holes for the rivets that hold the closure straps were performed more carefully and with a lower drilling speed. However, no limitations in using the grinder were found, both with sandpaper wheels for removing material and with a felt grinder wheel for smoothing the borders.

Characterization of 3D printed test samples

The SEM analysis revealed that the 3D printed samples showed a roughness due to the layer-by-layer nature of the 3D printing technique. However, the surface of the 3D printed samples resulted acceptable for absence of holes and limited inclusion, if compared with the PP sample. Moreover, the morphological analysis showed that the interface and the surface quality were not dependent from the layer thickness.

As expected, tensile tests results showed that FDM specimens presented different mechanical responses depending on fiber direction (almost not depending on layer height). When the load was applied longitudinally to the fibers, the behavior was comparable to that of PP and PE, thanks to the cross-sectional resistance of the fibers. When the fibers were orthogonal to the loading direction, the sample strength depended mainly on the inter-fiber bonding, reducing the overall resistance. However, the higher elastic modulus could be exploited to reduce the brace thickness, improving the overall comfort.

The absorbed energy (Ec) for PETG printed samples resulted to be inversely proportional to layer height and lower than PP and PE. When higher layers are printed for a given dimension, the same layers create a larger macroroughness with possible notch effect on the surface, influencing fracture mechanics. Moreover, Ec for PETG with transverse fibers resulted about two orders of magnitude higher than in longitudinal direction. This confirms the results obtained from the tensile test, providing evidence for the quality of interface bonding between adjacent layers. When the fiber connection has to withstand the load, the adhesion resistance decreases the bulk material properties to the point that the printed components result brittle. Considering that brace replacement must occur both in case of critical breaks with undesired impacts and plastic deformations, PETG is adequate for this application.

Cost model

The cost analysis showed that about half of the cost was attributed to labor cost. This preliminary analysis evidenced also the significant influence of the build time (Tb) on the operative costs, highlighting the importance of high printing speeds. Moreover, it has to be noticed that the accurate estimation of operative rate (Co) highly depends on the cost structure of the company that owns the FDM machine. However, the back brace cost resulting from the model is very competitive compared to the production cost of a thermoformed back brace, that typically ranges from 250 to 500 € due to the long labor time.

Pilot patient case

The brace was worn successfully for 2 weeks, and the device did not show any sign of delamination. According to the patient, the 3D printed brace was stiffer than the thermoformed one, with an improved supporting action. The patient also reported an increased sensation of brittleness which caused some slight concern during activities of daily living, with the fear of breaking the brace. However, this did not result in any adverse event during the 2 weeks of test. Longer tests should be performed in future works.

In our study, superficial temperature was used as an indirect indication of brace adhesion and contact, highlighting no significant differences between the 3D printed and the thermoformed device, with negligible temperature differences. Overall, the study showed that the production of 3D printed braces is feasible and was positively assessed by patient and orthotist. Our results provide encouraging preliminary findings and a clear direction for further improving and using virtual modeling and 3D printing in the field of orthotic bracing for the treatment of spine diseases.

The orthopedic physician agreed on the sensation of the patient about the material properties, the brace is effectively stiffer. However, the important feedback regards the good function of a stiffer material for applying a stronger correction, also in those cases of older patients with AIS where the spine becomes less flexible. Moreover, the physician noticed how this solution could be comparable to the stiff braces with metal rods (e.g., Milwaukee and Sforzesco braces) but with the advantage of a reduced mass and an increased acceptability.

The orthopedic technicians who postprocessed the brace found some differences also in terms of machinability. The use of the jig saw had to be avoided, because of possible delamination of the printed layers. The creation of the holes for the rivets that hold the closure straps had to be performed more carefully and with a lower drilling speed. Nevertheless, they found no limitation in using the grinder, both with rough and fine sandpaper wheels for removing material and with a felt grinder wheel for smoothing the border.

Moreover the morphological and deformation analysis of the back brace after the patient test confirm that the brace presented no morphological and structural modification after it use. Small and evenly distributed deformations found on the brace structure ensure its mechanical stability during use.


In this study, an innovative production process of orthopedic scoliosis braces based on FDM 3D printing is proposed and analyzed. The aim of the manuscript is not limited to the demonstration of the feasibility of the 3D printing process to produce scoliosis back braces, but it is meant to evaluate the effectiveness and the efficiency of such technology in terms of material behavior, costs, clinical applicability, and patient’s satisfaction.

After a screening of commercial materials, a PETG filament was chosen. Printed samples were characterized in terms of mechanical and morphological properties. PETG samples revealed mechanical properties similar to PP samples in terms of elastic modulus and ultimate tensile strength. The PE samples performed better in terms of elongation at break but resulted less stiff than PETG. A 3D printed brace was produced by reverse engineering based on an existing thermoformed brace. The main differences with respect to the thermoformed brace were related to lower machinability during postprocessing (requiring to be more careful in using the common tools), higher stiffness and higher apparent brittleness. The test on a patient with scoliosis showed both the feasibility of the manufacturing process and the competitiveness in terms of costs using 3D printing with respect to classic thermoforming procedure.

All the involved people (patient, physician, and technicians) noticed the stiffer behavior of the brace, but they did not evaluate this as a disadvantage. PETG has indeed an elastoplastic behavior with a reduced elongation to rupture in respect to the thermoformed PE. Nevertheless, the brace should not work beyond the yield stress otherwise the shape would be modified and the physician stated that PETG is a good compromise between completely rigid braces with metal rods and softer braces made in PE or PP.

Future studies will need to provide further evidence for long-term reliability of the technology, patient acceptance and clinical efficacy.