Skip to main content

Bioprinting Meets Synthetic Matrices: The Next Convergence

Team Dynamic Matrices | 14 December 2025

Bioprinting hardware has improved faster than the materials it prints. Resolution, multi-head extrusion and in-process imaging are all commercially available. What has not kept pace is a bioink that is printable, reproducible, cell-friendly and biologically instructive at the same time. We think that is the field's real bottleneck, and that it is a materials problem before it is an engineering problem.

What a bioink has to do

Extrusion bioprinting places three conflicting demands on a material:

  1. Flow under shear so it extrudes through a fine nozzle without excessive pressure that kills cells (shear stresses above roughly 5 kPa reduce viability; Blaeser et al., Advanced Healthcare Materials, 2016)
  2. Recover quickly after deposition so the strand holds its shape and supports the next layer
  3. Present the right biology so encapsulated cells survive, spread and function

The first two are rheology: shear-thinning and rapid self-healing, often summarised as a high yield stress with fast recovery of storage modulus. The third is biochemistry. Most materials do one or two well.

Where dECM struggles

Decellularised ECM bioinks (Pati et al., Nature Communications, 2014, is the landmark) deliver tissue-specific biochemistry. Their weaknesses are the same as any biological extract's: composition varies with donor and processing, rheology depends on that composition, and gelation is slow and thermally driven. Printability is tuned by adding thickeners or a second polymer, which changes the biology. Mechanical and architectural properties are hard to control precisely, and each new tissue type means sourcing and characterising new material. Regulatory familiarity with dECM is a real advantage; batch reproducibility is not.

What synthetic matrices bring

Programmable hydrogels are made rather than extracted, so rheology can be designed rather than inherited.

Self-healing crosslink chemistry. Reversible crosslinks (host-guest, boronate ester, hydrazone, DNA hybridisation) break under shear in the nozzle and re-form in seconds after deposition. Highley, Rodell and Burdick (Advanced Materials, 2015) showed guest-host HA gels printing into a self-healing support bath; the same logic applies to DNA-crosslinked networks, whose duplexes rupture under nozzle shear and re-hybridise on exit.

Independent tunability. Stiffness, stress relaxation, degradation rate and adhesion motifs are separate dials. A cartilage strand and a vascular strand can come from the same base polymer with different settings, instead of two different donor tissues.

Reproducibility. Every batch has the same rheology, so print parameters transfer between runs and between labs. This is the property that turns a printed construct from a demonstration into an assay.

Gentle post-processing. A DNA-crosslinked construct can be dissolved with a nuclease to recover cells for analysis, which a covalently photo-crosslinked ink cannot offer.

An honest account of the trade-offs

dECM keeps two advantages: out-of-the-box biochemical complexity for tissues whose ligand requirements are not yet enumerated, and a more established regulatory path. Synthetic inks require you to know which ligands your cells need. The field is converging rather than replacing: hybrid inks that carry defined synthetic rheology with a controlled dose of natural biology, and synthetic inks with increasingly complete peptide libraries. Printability, reproducibility and scalability now matter as much as biochemical fidelity, and that shift favours materials whose properties are specified rather than sampled.

Where DyNAtrix fits

DyNAtrix's DNA crosslinks make it shear-thinning and self-healing by nature, and its thermoresponsive backbone gives a simple temperature-triggered set after deposition. Stress relaxation is tunable over five orders of magnitude and stiffness independently, so the same ink can be set for soft neural constructs or firmer stromal ones. We are actively working with bioprinting groups on parameter windows; if you are printing and want to test it, talk to us.

References

  1. Pati F et al. Printing three-dimensional tissue analogues with decellularized extracellular matrix bioink. Nat Commun 5, 3935 (2014).
  2. Blaeser A et al. Controlling shear stress in 3D bioprinting is a key factor to balance printing resolution and stem cell integrity. Adv Healthc Mater 5, 326–333 (2016).
  3. Highley CB, Rodell CB, Burdick JA. Direct 3D printing of shear-thinning hydrogels into self-healing hydrogels. Adv Mater 27, 5075–5079 (2015).
  4. Malda J et al. 25th anniversary article: engineering hydrogels for biofabrication. Adv Mater 25, 5011–5028 (2013).
  5. Peng Y-H et al. Dynamic matrices with DNA-encoded viscoelasticity support the development of organoids and stem cells. Nat Nanotechnol (2023).

FAQs

Yes, and hybrid inks are one of the most active areas. A defined synthetic backbone provides rheology and mechanics; a controlled dose of dECM adds tissue-specific biochemistry. The trade is some batch variability for biological richness.

Storage modulus at rest, yield stress, degree of shear-thinning (viscosity at 1 and 100 s⁻¹), and recovery time of storage modulus after high shear. If they cannot provide them, printability will be trial and error.

Less, generally. A shear-thinning ink lowers the pressure and shear stress needed for extrusion, which is the main driver of cell death in the nozzle.