Tendon-mimetic materials with anisotropic assembly of aramid nanofibers
The subject invention pertains to multifunctional tendon-mimetic hydrogels constructed from anisotropic assembly of aramid nanofiber composites. The stiff nanofibers and soft polyvinyl alcohol in these anisotropic composite hydrogels (ACHs) mimic the structural interplay between aligned collagen fibers and proteoglycans in tendons. The ACHs uniquely exhibit a high modulus of ˜1.1 GPa, strength of ˜72 MPa, fracture toughness of 7333 J/m 2 , and many additional characteristics matching those of natural tendons. The surfaces of ACHs can be functionalized with bioactive molecules to present biophysical cues for the modulation of morphology, phenotypes, and other behaviors of attached cells. Moreover, soft bioelectronic components can be integrated on ACHs, enabling in-situ stimulation and sensing of various physiological parameters. The outstanding mechanics and functionality of these tendon-mimetics can be advantageously applied to advanced tissue engineering, implantable prosthetics, human-machine interactions, and other technologies.
1 . A tendon-mimetic anisotropic composite hydrogel (ACH) that emulates the microstructural interplay between aligned collagen fibers and soft proteoglycans in native tissues to provide a useful implant for treatment of a patient, the ACH comprising an assembly of stiff aramid nanofibers (ANFs) and flexible polyvinyl alcohol (PVA) molecules attached thereto by intermolecular hydrogen bonding.
2 . The ACH of claim 1 , wherein the ACH has a water content between about 60% and about 74% by weight.
3 . The ACH of claim 2 , wherein the ACH has a primary fiber orientation direction, and the ACH exhibits an elastic modulus greater than or equal to about 490.1 megapascals (MPa) and an ultimate strength greater than or equal to about 52.6 MPa; the elastic modulus and the ultimate strength each, respectively, measured in a direction parallel to the primary fiber orientation direction.
4 . The ACH of claim 3 , wherein the ACH exhibits an elastic modulus greater than or equal to about 1114 MPa and an ultimate strength greater than or equal to about 72.1 MPa; the elastic modulus and the ultimate strength each, respectively, measured in a direction parallel to the primary fiber orientation direction.
5 . The ACH of claim 3 , wherein the ACH exhibits a fracture energy greater than about 3 kilojoules per square meter (kJ/m 2 ), measured in a direction parallel to the primary fiber orientation direction; and
wherein the ACH exhibits a fracture energy greater than about 3 KJ/m 2 , measured in a direction perpendicular to the primary fiber orientation direction.
6 . The ACH of claim 5 , wherein the ACH exhibits a fracture energy greater than or equal to about 4 KJ/m 2 , measured in a direction parallel to the primary fiber orientation direction; and
wherein the ACH exhibits a fracture energy greater than about 6 KJ/m 2 , measured in a direction perpendicular to the primary fiber orientation direction.
7 . The ACH of claim 3 , wherein the ACH exhibits a stiffness anisotropy ratio (Ep/En) greater than about 10; wherein the stiffness anisotropy ratio (Ep/En) is calculated between a first respective tensile modulus (Ep) measured parallel to the primary fiber orientation direction, and a second respective tensile modulus (En) measured perpendicular to the primary fiber orientation direction.
8 . The ACH of claim 3 , wherein the ACH is biofunctionalized, and the ACH exhibits:
an angular frequency distribution with a majority of cells oriented within +/−15 degrees with respect to the primary fiber orientation direction;
a surface topography measurement by atomic force microscope exhibiting a measured height variation equal to or less than about 500 nano meters (nm) over a measurement area of at least about 36 square micrometers (μm 2 );
a statistically significant difference (P<0.05) in mean fluorescent intensity (MFI) for cells having an M1 phenotype when compared to a similarly biofunctionalized isotropic ANF-PVA hydrogel; and
a statistically significant difference (P<0.05) in mean fluorescent intensity (MFI) for cells having an M2 phenotype when compared to a similarly biofunctionalized isotropic ANF-PVA hydrogel.
9 . The ACH of claim 3 , wherein the ACH is fitted with one or more integrated multifunctional bioelectronic circuits configured and adapted to obtain one or more measurements selected from the group consisting of electrocardiogram (ECG), electromyogram (EMG), deformation, strain, temperature, resistance, or voltage under cyclic motion up to 50% elongation of the ACH.
10 . A method for creating a tendon-mimetic anisotropic composite hydrogel (ACH) that emulates the microstructural interplay between aligned collagen fibers and soft proteoglycans in native tissues to provide a useful implant for treatment of a patient, the method comprising:
mixing an aramid nanofiber (ANF) in dimethyl sulfoxide (DMSO) and stirring for a time sufficient to produce an ANF dispersion in DMSO;
dissolving polyvinyl alcohol (PVA) in dimethyl sulfoxide (DMSO) and stirring for a time sufficient to produce a PVA dispersion in DMSO;
mixing together the ANF dispersion in DMSO and the PVA dispersion in DMSO to form a moldable composite dispersion;
casting the moldable composite dispersion into one or more molds and immersing in deionized water for a time sufficient to produce an isotropic ANF-PVA hydrogel;
stretching the isotropic ANF-PVA hydrogel to create a stretched hydrogel;
fixing the length of the stretched hydrogel to create a fixed length;
drying the stretched hydrogel at the fixed length to create a dried stretched hydrogel; and
reswelling the dried stretched hydrogel to create the ACH.
11 . The method of claim 10 , wherein the ANF comprises a first mass of para-aramid pulp, and the ANF dispersion in DMSO comprises a second mass of sodium hydroxide (KOH) mixed in the DMSO with the ANF.
12 . The method of claim 11 , wherein the first mass of para-aramid pulp and the second mass of KOH are about equal in mass.
13 . The method of claim 12 , wherein the ANF dispersion in DMSO comprises at least about 30 milliliters (mL) of DMSO for every gram (g) of para-aramid pulp.
14 . The method of claim 13 , wherein the PVA dispersion in DMSO comprises about 15 wt. % PVA.
15 . The method of claim 14 , wherein the moldable composite dispersion comprises about a 1:1 mass ratio of the ANF dispersion in DMSO and the PVA dispersion in DMSO.
16 . The method of claim 15 , wherein the dried stretched hydrogel is released from the fixed length prior to reswelling.
17 . The method of claim 16 , comprising chemical functionalization to present arginylglycylaspartic acid (RGD) motifs for binding with a cell membrane.
18 . The method of claim 17 , wherein the chemical functionalization comprises benzophenone (BPh) functionalized amphiphilic block copolymers involving linear polyglycerol (LPG) adsorbed on the surface of the ACH in an aqueous environment.
19 . The method of claim 15 , comprising bonding the isotropic ANF-PVA hydrogel with one or more serpentine electronics circuits to create an integrated soft bioelectronic enabled ACH.
20 . A tendon-mimetic anisotropic composite hydrogel (ACH) that emulates the microstructural interplay between aligned collagen fibers and soft proteoglycans in native tissues to provide a useful implant for treatment of a patient, the ACH comprising:
an assembly of stiff aramid nanofibers (ANFs) and flexible polyvinyl alcohol (PVA) molecules attached thereto by intermolecular hydrogen bonding;
wherein the ACH has a water content between about 60% and about 74% by weight;
wherein the ACH has a primary fiber orientation direction, and the ACH exhibits an elastic modulus greater than or equal to about 1114 megapascals (MPa) and an ultimate strength greater than or equal to about 72.1; the elastic modulus and the ultimate strength, each respectively, measured in a direction parallel to the primary fiber orientation direction;
wherein the ACH exhibits a fracture energy greater than about 4 kilojoules per square meter (kJ/m 2 ), measured in a direction parallel to the primary fiber orientation direction;
wherein the ACH exhibits a fracture energy greater than about 6 kJ/m 2 , measured in a direction perpendicular to the primary fiber orientation direction;
wherein the ACH exhibits a stiffness anisotropy characterized by the ratio (Ep/En) greater than about 10, wherein the ratio (Ep/En) is calculated between a first respective initial tensile modulus measured parallel (Ep) and a second respective tensile modulus measured perpendicular (En) to the primary fiber orientation direction;
wherein the ACH is biofunctionalized, and the ACH exhibits:
an angular frequency distribution with a majority of cells oriented within +/−15 degrees with respect to the primary fiber orientation direction;
a surface topography measurement by atomic force microscope exhibiting a measured height variation equal to or less than about 500 nano meters (nm) over a measurement area of at least about 36 square micrometers (μm 2 );
a statistically significant difference (P<0.05) in mean fluorescent intensity (MFI) for cells having an M1 phenotype when compared to a similarly biofunctionalized isotropic ANF-PVA hydrogel; and
a statistically significant difference (P<0.05) in mean fluorescent intensity (MFI) for cells having an M2 phenotype when compared to a similarly biofunctionalized isotropic ANF-PVA hydrogel; and
wherein the ACH is fitted with one or more integrated multifunctional bioelectronic circuits configured and adapted to obtain one or more measurements selected from the group consisting of electrocardiogram (ECG), electromyogram (EMG), deformation, strain, temperature, resistance, or voltage under cyclic motion up to 50% elongation of the ACH.