66]. This variation in electrical resistance as a function of strain if large, can be used to accurately measure strain. For piezoresistive polymer composites, sensitivity is maximum when the concentration of the filler approaches what is known as the percolation threshold. At this concentration, it is possible for agglomerations to form and impact the sensitivity. Thus, manufacturing methods for piezoresistive composites must ensure that agglomerations do not occur. Among the suitable manufacturing processes for piezoresistive composites, AM has emerged as one of the most important prospects because of the freedom in design, and because of the control of filler alignment possible in processes such as ME.
Piezoresistive soft polymer composites have been manufactured through ME using different matrix and filler systems
[67][68][69][70][71][67,68,69,70,71]. For example, sensors of TPU with CNT fillers were manufactured using FDM
[68]. The use of AM enabled new or enhanced properties in some cases. For example, biaxial strain sensors made of TPU with CNT fillers were manufactured using FDM
[68]. The different patterns of CNT electrode deposition allowed for different designs, each with its own sensitivities to axial and transverse deformations, with largely unaffected mechanical properties (all materials exhibited ≈50% axial strain at 4 MPa loading). In another work, a hierarchically porous lattice of TPU was printed and bonded to a stretchable matrix of the same TPU and used as a conformable sensor
[70]. The macroscale porosity was controlled by the spacing of the struts, while intermediate and small-scale porosities were achieved through sacrificial fillers burned out after printing. The hierarchical porosity achieved anisotropy in response allowing the sensor to be bonded to curved substrates without affecting its pressure sensitivity. This was not previously possible for conventionally casted sensors. Other approaches used in AM of piezoresistive polymer composites to enhance their performance have consisted of using particle–matrix interface modifiers
[67] and embedding CNTs to a printed elastomer lattice using partial melting
[69].
Piezoresistive soft polymer composites have been manufactured through ME using different matrix and filler systems
[67][68][69][70][71][67,68,69,70,71]. The use of AM enabled new or enhanced properties in some cases. For example, biaxial strain sensors made of TPU with CNT fillers were manufactured using FDM
[68]. The different patterns of CNT electrode deposition allowed for different designs, each with its own sensitivities to axial and transverse deformations, with largely unaffected mechanical properties (all materials exhibited ≈50% axial strain at 4 MPa loading). In another work, a hierarchically porous lattice of TPU was printed and bonded to a stretchable matrix of the same TPU and used as a conformable sensor
[70]. The macroscale porosity was controlled by the spacing of the struts, while intermediate and small-scale porosities were achieved through sacrificial fillers burned out after printing. The hierarchical porosity achieved anisotropy in response allowing the sensor to be bonded to curved substrates without affecting its pressure sensitivity. This was not previously possible for conventionally casted sensors. Other approaches used in AM of piezoresistive polymer composites to enhance their performance have consisted of using particle–matrix interface modifiers
[67] and embedding CNTs to a printed elastomer lattice using partial melting
[69]. Ionic gels are another class of piezoresistive materials that have been developed for AM. A group of researchers developed a shear-thinning ionic gel that could be patterned into 3D structures and studied how a reentrant honeycomb structure enabled 310% larger elongations and sensitivity as compared to a traditional film
[72]. Another group further developed ionic gels for printing using eutectic solvents as the media for better stability post-printing
[73]. Once again, the freedom of design from AM was used to construct auxetic structures that offered enhanced strain sensitivity with a max GF of 3.30 and a strain of 300%.
Piezoresistive polymers have been widely developed for AM using ME. Further control of the porosity, and design of metamaterial structures will enable enhanced sensitivity and a broader range of operation. However, other AM processes with higher resolutions such as VP will be needed to develop smaller piezoresistive polymer sensors for use in MEMS.
Piezoelectric materials possess a permanent polarization that when disturbed through mechanical loading produces a voltage across the material. These materials are electromechanically coupled so mechanical loads produce voltages and applied voltages cause strains. Because of this characteristic, piezoelectric materials can function as both electrically driven actuators
[74] and as mechanical sensors
[75].
Flexible piezoelectric materials have been developed with the help of AM by printing polymers as well as nanocomposites with piezoelectric ceramic fillers. Optimization of concentration, along with intelligent structure design, has allowed materials to exhibit larger coupling coefficients as well as increased elongations. Strategies for AM of soft piezoelectrics have focused on intelligent structure design to overcome the inherent stiffness of common piezoelectric materials such as PVDF and ceramics. For example, Li et al. used electrical field-assisted FDM to produce piezoelectric sheets with designed deformations made with nanocomposites of sodium niobate ceramics and PVDF
[76]. Chiral patterns were built into the sheets to allow large deformations. Thus, once the sheets were rolled onto artery-like structures they could expand to sense radial pressures such as those found in blood flow inside the human body. Similarly, Yao et al. developed flexible and wearable piezoelectric sensors using lattice patterns through DLP
[77]. Highly sensitive but soft piezoelectric lattices were possible thanks to surface functionalization of the piezoelectric ceramic fillers, which enhanced mechanical energy transfer at lower solid loadings. Three-dimensional honeycomb structures were printed using the high-resolution photopolymerization printing method and the performance of the sensors surpassed piezoelectric polymers in sensitivity and compliance. Another approach towards building compliant piezoelectric structures through AM consisted of infiltration of a ceramic lattice with PDMS elastomer
[78]. This strategy allowed for complex structures to be built using only a ceramic-filled resin using SLA while still being able to obtain complaint structures afterwards.
Soft piezoelectric materials have been developed for AM despite the limited selection of polymer systems that exhibit piezoelectric polymers and the high stiffness of bulk nanocomposites of piezoelectric ceramics and elastomers. Continued development of metamaterial structures and identification of unique piezoelectric behaviors will continue to drive AM of soft piezoelectric structures composed of polymers and ceramic fillers.
Table 4 below summarizes the different efforts to print electronic polymers for sensing and actuation applications, highlights the specific elements fabricated using AM, their softness, and their individual performance.
Table 4. Summary of various soft electronic polymers recently manufactured through AM for use as sensors and actuators and their performances achieved.
Material |
Application |
Role of Printed Material |
Young’s Modulus or Elasticity |
Max Strain |
Printing Technique |
Performance |
Ref. |
Silicone elastomer |
Dielectric actuator |
Actuating layer |
≈700 kPa |
600% |
DOD |
A maximum areal strain of 6.1% at an electric field of 84.0 V/μm |
[61] |
Compliance up to 3 × 10 |
−8 |
Pa |
- |
Ceramic slurry DLP |
Variable piezoelectric charge constant up to 110 pC/N and sensitivity to pressure and extension with high conformability to surfaces |
[ |
77 |
] |
2.4. Chromic Materials
Chromic materials have the ability to change in appearance in their refractive index (e.g., color, fluorescence, brightness, transparency) when applying different stimuli such as temperature, mechanical stress, electricity, pH concentration, among others. Chromic materials are of interest due to their reversible optical mechanism that can be incorporated into wearable devices for sensing, and for soft robotics. Table 5 further summarizes AM processed SMPs, the AM method used for their fabrication, applied stimuli, color change, absorbance wavelength and reversibility.
Table 5. Summary of chromic materials and their properties that have been recently processed through AM techniques.
Materials |
Matrix |
Response Type |
Technique |
Applied Stimuli |
Color-Change |
Absorbance Wavelength (nm) |
Reversibility |
Ref. |
Spiropyran |
Polydimethylsiloxane |
Mechanochromic |
DIW |
|
Off-white to Purple |
|
Yes |
10 |
76 |
97 |
48 |
700 |
[ | 25 | ] |
28 |
] |
poly(dimethyl acrylamide-costearyl acrylate and/or lauryl acrylate) (PDMAAm-co-SA) |
SLA |
- |
- |
- |
3 |
99.8 |
87.6 |
- |
- |
[29] |
2-Methacryloyloxy 4-formylbenzoate |
DLP |
57 |
57 ± 4.0 |
39.30 ± 1.0 |
3 |
97.5 ± 0.30 |
91.4 ± 0.20 |
57 ± 4.0 |
39.30 ± 1.0 |
[30] |
Poly(ethylene terephthalate) (PET) |
FDM |
85–100 |
- |
45 |
7 |
100 |
90–98 |
- |
45 |
[31] |
poly(ethylene glycol) dimethacrylate (PEGDMA), isobornyl acrylate and 2-ethylhexyl acrylate |
DLP |
125 |
- |
- |
10 |
92.6 |
95.3 |
- |
- |
[32] |
SMPs have recently gained significant attention due to diverse advantages such as their light weight, flexibility of programming mechanisms, high shape deformability, biocompatibility, and biodegradability for actuator applications. SMPs are also attractive materials to fabricate diverse types of sensors for soft robotics and aerospace applications and for minimally invasive surgery devices for biomedical purposes. 3D printing offers an effortless way to fabricate more elaborate designs, AM has the flexibility to control some of the factors that have been found to affect SME’s performance including geometry, print path direction, and thickness of the sample
[33]. VP has been of interest for processing SMPs due to its in-situ polymerization process that allows the fabrication of elaborate geometries for very specific applications. SLA and DLP have been reported in the fabrication of origami structures, biomimetic, and soft robotic devices. Choong et al. evaluated the use of nanosilica dispersed in tBA-co-DEGDA photocurable resin using DLP to enhance nucleation and accelerate the polymerization rate, which significantly reduced fabrication time with Rs of 100% and Rr of 87%
[24]. For ME, FDM and UV-assisted DIW have been reported in the fabrication of SMPs with biomedical purposes and soft robotics application
[25]. Villacres et al. used the FDM technique to print a semi-crystalline TPU where they evaluated the effect of printing orientation and infill on the SME. It was found that a print angle orientation of 60° and 100% infill resulted in an increment of failure strain and strength where the infill content had a higher influence on mechanical properties
[34]. Chen et al. fabricated tough epoxy and N-butyl Acrylate SMPs composites by UV-assisted DIW with Rs of 97.1% and Rr of 98.5%
[26]. Lastly, Jeon et al. fabricated multicolored photo responsive SMP structures through Polyjet printing that showed different geometries when triggered by assorted color lights of different wavelengths
[35].
There are two main classifications by stimuli response known as thermal-responsive and chemo-responsive. Thermal-responsive SMPs are triggered by applying heat to the material and raising their temperature up to their Ttrans. However, using a direct heating method could restrict their applications, which has led to the use of functional fillers to fabricate SMPs composites that trigger SME by alternative methods, such as electricity, magnetism, light, and ultrasound. Liu et al. fabricated multi-responsive SMPs using Polycyclooctene with boron nitride and multi-wall carbon nanotubes (MWCNTs) by the FDM technique. By using 20 wt.% MWCNTs in the composite, the SME could be triggered by heat (under water at 70 °C), light (100 mW·cm
2), and electricity (5 V) with outstanding properties, Rs of 98.9% and Rr of 99.2%
[27] Zhang et al. fabricated PLA-Fe
3O
4 composites by FDM using magnetism (27.5 kHz) as an alternative stimulus for SME. It was found that a higher content of Fe
3O
4 led to a higher Rr, where PLA-Fe
3O
4-20% mass fraction gave the best results with Rs of 96.8% and Rr of 96.3%
[28].
In chemo-responsive SMPs, the SME is triggered by altering the ionic strength to promote plasticizing and lower Ttrans below room temperature
[36]. The most common method consists of submerging the SMP in a medium, such as an organic solvent or water, that triggers the plasticizing. Recovery time can be decreased by reducing the dimensions of the polymers to micro-fibers
[37]. Solvent-responsive SMPs commonly report the use of organic solvents such as ethanol, dimethyl sulfoxide methanol, and N-N dimethylformamide (DMF) [3, 12]. Some water responsive SMPs includes hydrogels (Polyvinyl alcohol, polyethylene glycol)
[38] and TPUs
[37]. Shiblee et al. fabricated water-responsive shape memory gels by SLA process using poly (dimethyl acrylamide-costearyl acrylate and/or lauryl acrylate) (PDMAAm-co-SA) by incorporating hydrophilic and hydrophobic monomers in the formulation. This shape-memory gel showed an Rs of 99.8% and Rr of 87.6% after the first cycle and Rr of 99.8% after the second cycle, the authors attributed the change of Rr to the training phenomenon
[29].
Thermal-responsive SMPs are mainly activated by hot programming, which consists of heating the material to its T
trans. The main advantage of hot programming is a high R
s, a minimal springback and it usually requires a small amount of applied stress to produce a plastic deformation
[39]. Li et al. fabricated Bisphenol-A glycerolate diacrylate (BPAGA) SMPs by DLP technique using hot programming method at glass transition temperature obtaining R
r of about 97% and R
s of 100%
[40]. On the other hand, chemo responsive SMPs are activated by either hot or cold programming. Cold programming is possible below T
trans and usually occurs at room temperature. However, cold programming is usually more challenging since some thermosets are brittle at their rubbery point leading to possible fractures
[39]. Keshavarzan et al. evaluated hot programming and cold programming methods for BCC and rhombic structures using 3DM-LED.W, which is a commercial SMP resin for DLP. It was found that cold programming is beneficial for higher energy absorption while hot programming obtained a higher shape fixity ratio, it was also noticed that rhombic structures have a better energy absorption and recovery due to higher strength and stiffness
[32].
SMPs show different behaviors according to the number of geometries that can be stored in memory, which depends on the network elasticity of the material
[36]. Lastly, multi-SMPs are materials that can learn more than three geometries additionally to their permanent shape. Peng et al. synthesized triple SMPs by using poly(ethylene glycol) dimethacrylate (PEGDMA), isobornyl acrylate and 2-ethylhexyl acrylate through DLP. The SMPs were able to store two different geometries in memory with an Rs of 92.6% and Rr of 95.3% without a significant degradation after 10 cycles, proving the effectiveness of SMPs
[41].
SMPs with chemical crosslinking are usually thermosets and have stronger bonds than physically crosslinked polymers and higher shape recovery. However, SMPs with chemical crosslinks cannot be reprocessed unless they have dynamic bonds. Some SMPs with chemical crosslinking take advantage of dynamic chemistries such as transesterification, transcarbamoylation, Diels–Alder bonds, disulfide bonds, diselenide bonds, and imine bonds
[38]. Thermadapts are a type of SMPs with dynamic covalent bonds that have recently gained attention due to their capability to change the temporary shape after curing. Some of the dynamic covalent bonds used to fabricate SMPs are hindered urea bonds and triazolinedione. Miao et al. developed thermadapt SMPs (2-Methacryloyloxy and 4-formylbenzoate) with dynamic imine covalent bonds using DLP that allowed changing the temporary shape after printing for different actuation purposes that can be useful for soft robotics applications
[30]. Davidson et al. used LCEs to develop thermadapt SMPs by radical-mediated dynamic covalent bonds using the hot DIW technique. When exposed to UV light during actuation, the exchangeable bonds that allow the change of the permanent shape of LCE are activated
[42]. Some SMPs that reported the use of physical crosslinking include hydrogen bonds, ionic bonds, π-stacking, charge transfer interactions
[38]. Chen et al. synthetized PET copolyester using π-stacking synergistic crosslinking to induce enhance shape memory properties by the FDM technique. The optimal copolyester was P(ET-co-PN) 20 with an Rs of 100% and Rr of 98%, it was also found to have some levels of self-healing due to π-stacking crosslinking and flame retardant properties due to the nature of PET
[31].
SMPs have a diverse range of applications due to their unique mechanism, where 3D printing contributes to the evolution of elaborate designs. Many efforts to control the responsiveness by alternative methods besides direct heating have been made. An interesting research direction could be the development of SMPs with dual responsive mechanisms for different purposes that expand their fields of application. Furthermore, multi-material printing may allow the fabrication of SMPs that can store multiple geometries in memory. The evaluation of 3D printing structures to fabricate reprocessable SMPs with dynamic covalent bonds is another interesting research direction that can redefine SMPs’ functionality.
2.2. Self-Healing Materials
Self-healing polymers are a branch of functional materials designed to take advantage of intricate physical or chemical processes to reform broken bonds caused by mechanical damage. The ability of self-healing polymers to respond to damage that may be difficult to detect, helps prevent the propagation of cracks or ruptures that result from the polymer’s exposure to fatigue, abrasion, and other deteriorating forces during regular operation. Recent advances in AM have led to an increase in the development of self-healing materials that overcome the design limitations of traditional casting methods, resulting in self-healable structures with increased complexity and tunable properties. For this reason, the application of self-healing polymers has extended beyond protective coatings to wearable devices, implantable biomedical devices, health monitors, and electronic skins.
The healing efficiency of AM processed self-healing polymers is often measured through the restoration percentage of physical properties such as fracture strain and corresponding tensile or compressive stress. Additionally, the recovery time can also be an indicator of performance and in the case of non-autonomic processes, the activation energy required to trigger the self-healing process, which can be calculated through the Arrhenius equation. Table 3 further summarizes AM processed self-healing polymers, the AM method used for their fabrication, their functional chemistry, recovery performance, recovery conditions, and applications.
Table 3. Summary of recent studies on AM processable self-healing polymers highlighting mechanical robustness and healing efficiency.
Materials |
Tensile Strength |
Max Strain |
Technique |
Application |
Self-Healing |
Stimulus |
Healing Time |
Efficiency |
Ref. |
Semi-interpenetrating polymer network elastomer |
5 MPa |
600% |
UV-assisted DIW |
Biomedical Devices |
Embedded semicrystalline thermoplastic |
Heat at 80 °C |
20 min |
<30% |
[43] |
Ferrogel |
- |
288% |
DIW Bioprinting |
Drug Delivery and Tissue Engineering |
Reversible Imine Bond Formation |
No Stimulus |
10 min |
Reduced graphene oxide-elastomer nanocomposites |
Dielectric actuator~95% |
[44] |
Flexible electrode layer |
- |
104% |
Aerosol Jet Printing |
Electrodes with a maximum stretchability of 100% could be bonded to dielectric layers without losing conductivity |
[ |
Vat Photopolymerization |
Stereolithography |
Light single point |
62 | ] |
N-butyl Acrylate | ≈50 µm [ |
UV-assisted DIW15] |
95.2 | Thermoset Elastomers |
610 | Acrylate resins Nanoparticles |
|
25.4 (Ultimate strain) |
-
High resolution
-
Close tolerances |
Thermoplastic polyurethane/carbon nanotubes/silver nanoparticles composites |
Dielectric actuator | |
Actuating material | | |
3.44 MPa in print direction | |
Up to 800% in print direction | |
FDM |
Dielectric constant of 6.32 and a radial extension of 4.69% at an applied 4.67 kV |
[79] |
Barium titanate filled silicone elastomer |
Dielectric actuator |
Actuating layer |
39.82 kPa |
>100% |
DIW |
Maximum tip displacement of 6 times its thickness at 5.44 kV Blocking force of 17.27 mN and deflection of 0.85 mm under a 0.12 g mass with a 5 kV applied |
[63] |
[ | 80 | ] |
[ |
Poly(butyl acrylate) |
Polyacrylamide |
Mechanochromic and Hydrochromic |
DIW |
Compression: 5.7 kPa |
Entire Wavelength Spectrum Colors |
500–900 |
Yes |
[81] |
|
|
3 |
97.1 |
98.5 |
610 |
25.4 |
| (Ultimate strain) |
Dynamic Covalent Polymer Networks |
3.3 MPa | [ |
140% |
FDM |
- |
Diels–Alder Reaction |
Heat at 80 °C Deionized Water at RT | 26 | ] |
Polyethyleneimine-co-poly(acrylic acid) |
Polyethylene glycol diacrylate |
Hydrochromic |
DIW |
| 12 h |
Blue-Green, and Red | 96% |
|
400–650 |
Yes |
[81] |
Micro-Stereolithography |
Light single point |
≈10 µm [16] |
~70% |
[ |
Polycyclooctene with boron nitrate and MWCNT |
FDM |
70 |
3.85 (Storage modulus) |
- |
- |
98.9 |
99.2 |
3.85 (Storage modulus) |
- |
[27] |
Polyurethane acrylate |
Isobornyl acrylate |
Thermochromic |
Projection Micro Stereolithography |
74.2–81.7 °C |
Black, Red, Blue, Yellow, White |
Two-Photon Polymerization |
Light single point |
≈0.3 µm [17] |
45 | ] |
Photoelastomer Ink |
16 kPa |
130% |
SLA |
Soft Actuators, Structural Composites, Architected Electronics |
Disulfide Exchange |
Heat at 60 °C |
2 h |
100% |
[ |
400–80046] |
Yes |
[82] |
Polylactic acid (PLA)/Fe3O4 composites |
FDM |
66.6 |
1600 (Storage modulus) |
- |
- |
96.8 |
96.3 |
1600 (Storage modulus) |
- |
Fluid Elastic Actuators |
13–129 kPa | [ |
45–400% |
SLA |
Soft Robotics |
Unreacted Prepolymer Resin |
Thermoplastic elastomer |
Dielectric actuator |
Elastic frameSunlight ~15,000 cd m2 |
- |
- |
FDM30 s |
A tilt angle of 128° and a blocked force of 24 mN were measured when driven by 6 kV |
[64]- |
[47] |
Continuous Liquid Interface Production |
Poly(N-isopropylacrylamide) |
Silica-alumina based gel |
Thermochromic and Electrochromic |
DIW |
Yes |
Light entire layer |
≈0.4 µm [18] |
Thermoplastic Acrylate resins Nanoparticles |
|
Physically Crosslinked Hydrogels | | |
95 kPa | |
1300% | |
SLA |
|
|
Flexible Devices, Soft Robotics, Tissue Engineering |
|
Hydrophobic Association |
Contact |
6 h |
~100% |
[ | 48 | ] |
Digital Light Processing |
Light entire layer |
≈200 µm [19] |
[ | 83 | ] |
Thermoplastic polyurethane |
Poly(3,4 ethylenedioxythiophene)-poly(styrene sulfonate) (PEDOT:PSS)/silver (Ag) | Dielectric actuator |
Elastic frame |
- | 67 | ] |
>60 °C and 0.6–1.8 Amp (2~6 V) |
Transparent to Opaque State |
1400–1900 |
- |
FDM |
Honeycomb structures could achieve a longitudinal strain of 15.8% and transverse strain of −0.97% at a driving voltage of 7.5 kV |
[ | 65] |
Grid/polyethylene terephthalate |
Electrochromic |
IJ |
−0.6–0 V |
Transparent, Black |
633 |
Yes |
[ | 84] |
Silicone Elastomer |
~225 kPa |
~330% |
SLA |
Endurable Wearables, Flexible Electronics |
Ionic Bonding |
Heat at 100 °C |
12 h |
>90% |
[ |
Thermoplastic polyurethane and multiwalled carbon nanotubes |
The use of AM for soft chromic materials provides an effortless method to explore different geometrical designs and obtain tunable, mechanically activated chromic (also known as mechanochromic) responses with reversible optical properties. For example, Rohde et al. used the DIW technique to explore different geometries for mechanochromic composite elastomers, using PDMS microbeads as a matrix with spiropyran aggregates as a functional filler
[80]. Activation of the chromic mechanism was possible by applying either a low mechanical strain under uniaxial tension or compression. The soft elastomer composite showed reversible mechanochromic properties displaying a purple color in the area of applied mechanical force and returning to white after releasing such force. Chen et al. fabricated highly stretchable photonic crystal hydrogels with reversible mechanochromic properties by DIW technique
[81]. The physically crosslinked poly(butylacrylate) (PBA) composites provided a high elongation at break of 2800% and reversible color change from blue to grey under tension and compression.
Additionally, AM has contributed to the fabrication of complex inks with moisture-activated chromic properties (often referred to as hydrochromism) that allow the obtainment of multiple color changes. For example, Yao et al. developed a 3D printable hydrogel ink for the DIW technique to develop soft actuators with shape memory and appearance tuning properties
[85]. By using polyethyleneimine-co-poly (acrylic acid) (PEI-co-PAA), hydrochromism was produced, showing tunable luminescence from blue to green, which can be controlled by water absorption of the actuators in the range of 20% to 90% relative humidity. Moreover, by the incorporation of fluorophore-lanthanide an additional red color was also tunable by water absorption in the sample. The hydrochromic soft actuators also showed a reversible change in opacity from opaque to transparent produced by phase separation caused by dehydration.
Thermally activated chromic (often referred to as thermochromic) are the most reported chromic materials due to the simplicity of their chromism mechanism tuning. One example is Chen et al. who developed a 3D printable resin with polyurethane acrylate (PUAs) oligomer and isobornyl acrylate (IBOA) monomer with shape memory properties for the µSL process
[82]. By the addition of thermochromic microcapsules, it was possible to fabricate self-actuating devices with reversible change colors from red to white with tunable glass transition temperature from 74.2 to 81.7 °C.
Electrically activated chromic materials (also known as electrochromic) have been of interest for soft functional devices as an alternative method to used temperature to trigger a color change. For example, Zhou et al. used DIW technique to fabricate a device using poly(N-isopropylacrylamide) (PNIPAm) as functional particles dispersed in an Si/Al sol-gel, producing a hybrid hydrogel (PSAHH) with reversible appearance properties from opaque to translucent that could be triggered by heat or electricity
[83]. These reversible thermochromic and electrochromic properties could be triggered by heating the samples above 60 °C or by increasing current from 0.6 to 1.8 Amp (2~6 V). The change in the sample’s appearance was due to the temperature-induced dehydration of PNIPAm particles, which acted as light scattering fillers. Cai et al. used ink-jet printing to fabricate electrochromic WO3-PEDOT:PSS composites printed on flexible substrates with electrochromic properties
[84]. The flexible device showed a fast electrochromic response even under bending conditions in the range of −0.6 to 0 V transitioning from transparent to black and with good electrochemical stability up to 10,000 cycles.
Chromic materials are an emerging research area that has recently found its way into AM techniques for the fabrication of soft functional devices. Due to the high potential of chromic to fabricate wearable devices, it is expected to see future research trends taking advantage of AM to develop multi-responsive devices with reversible chromic properties.
2.5. Multifunctional Soft Materials
Multifunctional materials are those that present two or more functionalities due to their inherent properties or when combined with other functional materials as composites. The functionalities that make up multifunctional materials can be a combination of shape memory, self-healing, actuation, sensing, optical, biological, elastic, etc. In engineered multifunctional material systems, properties are carefully selected to achieve the desired multifunctionalities based on the field of applications. For example, multifunctional biomaterials must first present a therapeutic functionality and then may present added functionality including sensing of body temperature and pressure, or actuation
[86]. Other engineered multifunctional materials can provide structural support in demanding environments while providing additional functionality to address very strict requirements
[87]. The applications of such materials include energy
[88], medicine
[87], nanoelectronics, aerospace, defense, semiconductor, and other industries.
Multifunctional materials reduce system complexity by having one material perform functions that would be otherwise performed by multiple different materials. This is beneficial in applications such as soft robotics where weight reduction and simplicity are some of the key characteristics and the use of the least number of materials ensures the best performance possible
[89]. The integration of multifunctional materials into structures requires material compatibility and adhesion between different components. AM allows a seamless transition from structural to functional sections through material gradients
[90]. Thus, the combined development of materials with multiple functionalities together with the development of AM techniques that easily transition between materials allows for the simplest, most size effective structures.
Table 6 below summarizes the different multifunctional materials and composites that have recently been developed using a variety of AM processes.
Table 6. Different multifunctional soft materials recently manufactured using AM techniques and their applications.
Materials |
Modulus |
Max Strain (%) |
Technique |
Application |
Functionalities |
Ref. |
Polyacrylamide |
17 KPa |
574 |
DIW |
Biocompatible Soft Robotics |
Magnetic response |
[91] |
Polyacrylamide with Carbomer |
40 KPa |
260 |
DIW |
Biocompatible Soft Robotics |
Magnetic response |
[91] |
PLA-PEA |
125 MPa |
2.5 |
DIW |
Actuation and Sensing |
Shape memory effect and piezoelectric effect |
[92] |
Polypyrrole (PPy) |
498 kPa |
1500 |
DIW |
Sensor |
Self-healing |
[93] |
Polydimethylsiloxane (PDMS) |
160 kPa |
210 |
DIW |
Sensor |
Superhydrophobicity |
[94] |
Piezoresistive sensors |
Sensor and electrodes |
- |
>100% |
FDM | 49 | ] |
Material Jetting |
Drop on Demand |
Drop |
≈32 µm [20] |
Polymers Thermoplastic Acrylate resins Elastomers Nanoparticles |
-
High accuracy
-
Little to no post-processing
-
Capability to fabricate functionally graded materials
-
Potential for multi-material printing
|
Host–Guest Supramolecular Hydrogel | |
|
0.3–0.5 MPa |
70% |
|
DIW |
|
Biomedical |
Nanoparticle Jetting |
Drop |
≈10 µm [21] |