Thank you for visiting nature.com. You are using a browser version with limited support for CSS. To obtain the best experience, we recommend you use a more up to date browser (or turn off compatibility mode in Internet Explorer). In the meantime, to ensure continued support, we are displaying the site without styles and JavaScript.

# Superelastic and pH-Responsive Degradable Dendrimer Cryogels Prepared by Cryo-aza-Michael Addition Reaction

## Abstract

Dendrimers exhibit super atomistic features by virtue of their well-defined discrete quantized nanoscale structures. Here, we show that hyperbranched amine-terminated polyamidoamine (PAMAM) dendrimer G4.0 reacts with linear polyethylene glycol (PEG) diacrylate (575 g/mol) via the aza-Michael addition reaction at a subzero temperature (−20 °C), namely cryo-aza-Michael addition, to form a macroporous superelastic network, i.e., dendrimer cryogel. Dendrimer cryogels exhibit biologically relevant Young’s modulus, high compression elasticity and super resilience at ambient temperature. Furthermore, the dendrimer cryogels exhibit excellent rebound performance and do not show significant stress relaxation under cyclic deformation over a wide temperature range (−80 to 100 °C). The obtained dendrimer cryogels are stable at acidic pH but degrade quickly at physiological pH through self-triggered degradation. Taken together, dendrimer cryogels represent a new class of scaffolds with properties suitable for biomedical applications.

## Introduction

In this work, we report that dendrimer cryogels can be prepared using the aza-Michael addition at subzero temperatures, namely cryo-aza-Michael addition. Cryopolymerization uses ice crystals as porogens to obtain macroporous materials11,12,13,14,15,16,17,18,19,20,21,22. There is a tremendous interest in developing macroporous monolithic elastic networks for various biomedical and tissue engineering applications23,24,25,26,27,28,29,30,31. We show that EDA-core PAMAM dendrimer G4 reacts with PEG DA via the cryo-aza-Michael addition to form a macroporous superelastic network, i.e., dendrimer cryogel. Dendrimer cryogels display distinctly different structure and properties including stiffness, flexibility, and resilience from dendrimer hydrogels prepared via the aza-Michael addition at room temperature. To the best of our knowledge, cryo-aza-Michael addition is a new method to prepare elastic dendritic networks. This method is simple and environmentally friendly. It can be employed to produce materials with tunable mechanical properties. The resulting dendrimer cryogels are highly macroporous, and they exhibit superelasticity, biologically relevant Young’s modulus, and high resilience over a broad temperature range and retains such properties following storage at various temperatures. Furthermore, the dendrimer cryogels show pH-dependent swelling and self-triggered degradation behaviors.

## Results and Discussion

### Characterization

Ethylenediamine core PAMAM dendrimer G4 and PEG diacrylate (575 g/mol) were mixed at the equimolar ratio of amine to acrylate in water. The mixture was incubated at a subzero temperature (−20 °C) overnight for cryopolymerization via the aza-Michael addition reaction (Fig. 1a). Ice crystal porogens form during the cryopolymerization. Upon the completion of the reaction, the ice crystals are removed by freeze-drying and leave behind interconnected pores. The dendrimer cryogel formed at 5 wt% (CG-G4-5%) is monolithic and ultralight (0.27 g/cm3) (Fig. 1b). The SEM images (Fig. 1c) reveal an interconnected micron-sized porous structure, which is attributed to the sublimation of ice crystals during the freeze-drying procedure. The inset amplifies the pore wall and discloses its anisotropic surface texture (Fig. 1d). The pore size of the dendrimer cryogel ranges from 25 to 135 μm, and the mean pore size is 60 ± 17 μm (Fig. 1e). The pore wall thickness range is 0.5–5 μm, and the average is 2.3 ± 1.3 μm (Fig. 1f). The dendrimer cryogels formed at 1 wt% and 10 wt% are also macroporous (Figure S1) but have different morphological structures and macroscopic appearances. CG-G4-1% is soft and fluffy (Figure S1a). It is because the concentration of dendrimer is too low to form a 3-dimensional scaffold. The morphology of CG-G4-1% looks like a piece of wrinkled paper, and its pore spatial distribution is random (Figure S1b). CG-G4-10% is light (Figure S1c) and exhibits a continuous porous network with the pore dimension smaller than that of CG-G4-5% (Figure S1d). The densities for CG-G4-1% and CG-G4-10% are 0.08 g/cm3, and 0.58 g/cm3, respectively.

Using hexane uptake (a non-solvent commonly used to calculate the pore volume of hydrophilic gels) the porosities of CG-G4-1%, CG-G4-5%, and CG-G4-10% are 89.6 ± 8.8%, 68.8 ± 6.8%, and 61.7 ± 1.2%, respectively (Figure S2). The porosity of CG-G4-1% is the highest, followed by CG-G4-5% and CG-G4-10%, which is in agreement with the SEM morphologies. We applied FTIR to qualitatively monitor acrylate groups and primary groups in the cryogels. The N–H bending vibration of primary amines is observed at 1560 cm−1. The C=C stretching vibration of vinyl group in PEG DA has a peak at 1720 cm−1. Acrylate is fully used in the reaction as the C=C stretching peaks in all the three cryogels have vanished almost completely. However, the N–H bending peaks are still noticeable in the cryogels (Figure S3), indicating secondary amines may have participated in the aza-Michael addition reaction with PEG DA.

The cryogel swelling behaviors at 37 °C were examined at pH 7.4, pH 5.3, and pH 1.2. All the three cryogels, CG-G4-1%, CG-G4-5% and CG-G4-10%, show a rapid swelling rate in the first 1 h and reach equilibrium within 1 h (Fig. 2). It is worth noting that CG-G4-1% absorbs 23 times as many as its dry mass at pH 7.4 within 15 min. CG-G4-1% and CG-G4-10% exhibit the highest and lowest equilibrium swelling ratio at pH 7.4, respectively. The different swelling ratios are attributed to 3-dimensional structure and porosity of the cryogel. In general, a loosely cross-linked network with high porosity allows more PBS to be absorbed into the swollen gel. For all the three cryogels, the swelling equilibrium at pH 1.2 is higher than that at pH 5.3 or pH 7.4. The effect of pH on swelling is especially pronounced for CG-G4-1%. The equilibrium swelling ratios of CG-G4-1% at pH 1.2, pH 5.3 and pH 7.4 are, respectively, 5130%, 2760%, and 2590% (Fig. 2a). The equilibrium swelling ratios of CG-G4-5% at pH 1.2, pH 5.3 and pH 7.4 are 1800%, 1200%, and 1100%, respectively (Fig. 2b). The equilibrium swelling ratios of CG-G4-10% at pH 1.2, pH 5.3 and pH 7.4 are 900%, 700%, and 550%, respectively (Fig. 2c). CG-G4-5% and CG-G4-10% can absorb 1.6 times medium at pH 1.2 as much as they can at pH 7.4.

As shown in Fig. 3, the degradation rates of cryogel formulations at pH 7.4 from high to low are CG-G4-1%, CG-G4-5%, and CG-G4-10%. CG-G4-1% degrades completely within 24 h. CG-G4-5% shows 32% degradation in 24 h and 89% degradation in 48 h. Strikingly, there is no significant degradation of CG-G4-10% within 48 h. The degradation differences of the three cryogels at pH 7.4 are primarily caused by porosity and morphology. Dendrimer cryogels degrade much more slowly at pH 5.3 and pH 1.2 (Fig. 3a–c). Especially, the cryogels are most stable at pH 1.2. They had limited degradation even after 7-day incubation.

Dendrimer cryogels made of cationic dendrimer show pH-dependent swelling behavior. They have higher swelling ratios in acidic buffer than in neutral buffer. Polymeric networks possessing carboxylic acid or amine groups is capable of changing their swelling and disintegration behaviors in response to pH change. In general, the ionization of amines at low pH would make the polymer more hydrophilic, resulting in quicker swelling and degradation. Nonetheless, dendrimer cryogels degrade significantly slowly in acidic solutions. Especially, the degradation of all the three cryogels at pH 1.2 is almost suppressed within 7 days. We attribute the opposite degradation pattern of our dendrimer cryogels to the self-triggered degradation mechanism. Ester bonds form after the aza-Michael addition between PAMAM G4 and PEG-DA. The ammonolysis of ester bonds is triggered by the unreacted primary amine groups on dendrimer surface, thus leading to the degradation of the dendrimer cryogel network.

### Rheological and elastic properties

An amplitude sweep was first carried out to make sure that the measurement was in the linear viscoelastic region (Figure S4). The frequency sweeps were then measured at a fixed strain of 1%. As shown in Fig. 4a–f, all the samples display typical viscoelastic behavior as their storage moduli (G′) are much higher than their loss moduli (G′′), and G′ is frequency-independent over the entire measured frequency range. It is interesting that the three hydrated cryogels have a higher modulus compared to their counterparts in the dry state, especially for CG-G4-5% and CG-G4-10% (Fig. 4g).

As shown in the compression stress-strain curve (Fig. 5a), there are two distinct stages of deformation observed. Dendrimer cryogel shows linear elasticity in stage I at low strains below 30%, which is attributed to the bending of the pore walls. Compression Young’s modulus (EC) is 72.5 ± 2.8 kPa. The work done by compression is used to compress the pores. The elastic deformation is recovered during the rebound phase (Figure S5). In contrast, at higher strains (30% to 70%) in stage II, stress increases abruptly. The work done by compression is responsible for the further buckling and densification of the pores. At 70% strain, dendrimer cryogel supports over 6400 times its weight without collapsing. This property is rarely seen in other polymeric elastomers16,22,29,32,33,34. Furthermore, the dendrimer cryogel exhibits excellent rebound performance and does not show significant stress relaxation under cyclic deformation at room temperature.

When compressed to at least 70% strain in the first cycle, the pores are closed and densificated (Fig. 5b). After unloading, it recovers quickly to its original shape. More impressively, this high resilience maintains even after many cycles of load-unload compression. As shown in Fig. 5c, the cryogel maintains open pores after recovery from a minimum of 100 cycles of compression. The cryogel recovers its initial shape and size instantly upon load removal following 100 times of manual compression (Fig. 5d,e and movie S1). The physical characteristics of the cryogel work done by compression, maximum stress, EC, energy loss coefficient are highly stable throughout the test (Fig. 5f).

We used the cryo-aza-Michael addition method to prepare and tested two aditional sets of crygels for comparision: chitosan-based cryogel CG-chitosan (non-dendrimer-based) and dendrimer cryogel using a lower generation dendrimer G1, i.e., CG-G1-5%. We tested the compression stress-strain properties on CG-G1-5% and CG-chitosan. CG-G1-5% exhibits a macroporous structure similar to that of CG-G4-5% (Figure S6a). Although CG-G1-5% has an EC of 30.4 ± 0.1 kPa, which is lower than that of CG-G4-5%, its resilience is comparable to the resilence of CG-G4-5%. The compression stress-strain curve of cycle 100 is nearly identical to that of cycle 1 (Figure S6b). The work done by compression, maximum stress, EC, energy loss coefficient of the CG-G1-5% are highly stable throughout the test (Figure S6c). The CG-chitosan shows a porous structure (Figure S7a). It shows an higher EC (333.6 kPa) than dendrimer cryogels. Different from dendrimer cryogels, CG-chitosan exhibits three stages of deformation (Figure S7b). The stress plateau in stage II is attributed to the elastic buckling of pore walls. However, CG-chitosan does not rebound (Figure S7b–d). The studies support the unique dendritic-linear cross-linked structure is primarily responsbile for the superior resilience property of dendrimer cryogels.

We went on examining how temperature change affects the dynamic mechanical properties and the compression properties of dendrimer cryogel using dynamic mechanical analysis (DMA). The changes of storage modulus (E’), loss modulus (E”) and loss tangent (Tanδ) over a broad temperature range (−80 to 200 °C) are shown in Fig. 6a. The temperature corresponding to the peak value of tanδ, −14 °C, is identified as glass transition temperatures (Tg). The dendrimer cryogel has high E’ values (>104 kPa) at temperatures below Tg, which is 2 orders of magnitude higher than at temperatures above Tg. The dendrimer cryogel shows excellent elasticity below 190 °C. At the end of the DMA test, we noticed that the sample was carbonized with permanent necking deformation (Fig. 6b). The carbonized dendrimer cryogel maintains a macro-porous but anisotropic structure (Fig. 6c). Carbonized dendrimer cryogel is an entirely new type of material. There is no significant structural change in the direction perpendicular to necking (Fig. 6d); however, the densification of pores is seen in the direction of necking (Fig. 6e). Further investigation on the carbonized dendrimer cryogelis warranted but beyond of the scope of this paper. The rebound performance of the elastomer at non-ambient temperatures, i.e., −20 and 100 °C, was investigated. The elastomer at −20 °C is much stiffer than at the ambient temperature as its peak stress increases nearly 5 folds to 811 kPa (Fig. 6f). Also, the hysteresis loop is larger. The elastomer recovers its high elasticity quickly upon cyclic compression. The energy loss coefficient is 15.3% in cycle 1 (Fig. 6h). It goes higher as the elastomer receives 10 cycles of compression and remains constant at 30% even under a higher number of cyclic compression. The initial work done by compression and maximum stress quickly drop to a stable level after cyclic compression is applied 10 times or more. The dendrimer cryogel shows suboptimal elasticity and resilience property at −20 °C compared to itself at ambient temperature. Nonetheless, its overall rebound performance at −20 °C is superior to what most elastomers exhibit at ambient temperature. It was worth noting that the stress-strain behaviors of the elastomer (green and blue lines in Fig. 6f) almost recover to its initial state upon extra cycles of load-unload compression when the temperature is increased immediately to 25 °C. There is no significant difference in hysteresis loop between cycle 1 and cycle 10. The morphological structure of the dendrimer cryogel at the end of the experiment (Fig. 6g) looks similar to what is observed in the untreated sample. In contrast, the dendrimer cryogel quickly loses its elastomeric characteristics at 100 °C (Fig. 6i and k). The sample was crushed after 12 cyclic compressions accomplished with loss of porous structure (Fig. 6j).

### Fast recovery of superelasticity after storage

Encouraged by the observation of the rapid recovery from 100 cycles of compression at −20 °C, we studied the performance after storage at −80, −20, and 100 °C for 24 h, respectively. The studies show that the dendrimer cryogel rapidly restores high resilience property after storage at different temperatures. One hundred relatively constant manual compressions were applied to illustrate the resilience properties of the stored elastomers recovering at ambient temperature. After 24 h storage at −80 °C, the sample can be only compressed to approximately 5% strain in cycle 1. Approximately 50% strain and 60% strain could be compressed in cycle 2 and cycle 3, respectively. It recovered its high elasticity in cycle 4 with no less than 70% strain (Fig. 7a, movie S2). Similarly, the dendrimer cryogel restores its excellent elasticity immediately at ambient temperature after being stored at either −20 °C (Fig. 7e, movie S3) or 100 °C (Fig. 7i, movie S4) although the color changed to yellow after storage at 100 °C for 24 h. Quantitative cyclic compression tests confirm that the dendrimer cryogels retain the superelasticity at ambient temperature (Fig. 7b,f,j). No significant decreases in work done by compression, maximum stress, Young’s modulus, and energy loss coefficient are observed after 100 cycles of compression (Fig. 7d,h,l). The porous structures of the samples stay unchanged after storage and subsequent cyclic compressions (Fig. 7c,g,k).

From the molecular perspective, single dendrimer molecule is elastic35. The cryopolymerization organizes the randomly dispersed dendritic nanoelastomers into a more relatively organized cross-linked network knotted with linear PEG chains. The subsequent freeze-drying endows it with a macroporous structure upon the removal of ice crystals. The bulky macroporous structure made of cross-linked nano-elastomer–linear polymer collectively contribute to a hierarchical elasticity across different lengths of scale (Fig. 8). It is well accepted that cross-linking can affect the flexibility of polymer chains and hence Tg. When the degree of cross-linking is high, the conformational change of polymer segments would be difficult, thus cuasing Tg to increase significantly or disappear. Due to the 3-D spherical nanostructure of the dendrimer, the dendritic-linear network greatly reduces the effect of cross-linking on the movement of polymer segments. This unique hierarchical elasticity coupled with unrestricted segmental motion between cross-links accounts for a very low Tg of the resulting dendrimer cryogel. We are currently exploring dendrimer cryogels for drug delivery.

In conclusion, the aza-Michael addition-based cryopolymerization of super atomistic dendritic building blocks and flexible linear PEG chains leads to the development of dendrimer cryogels with superelasticity, high resilience, and pH-dependent swelling and degradation. The dendrimer cryogels have ultralightweight, an extremely high recovery rate after storage at various temperatures. Dendrimer cryogels are a new class of materials for drug delivery and tissue engineering applications.

## Methods

### Materials

EDA-core PAMAM dendrimer G4.0 (G4) and G1.0 (G1) were purchased from Dendritech (Midland, MI). Polyethylene glycol diacrylate (PEG DA, Mn = 575 g/mol) and chitosan (Mw = 50 000 −190 000 Da) were purchased from Sigma-Aldrich.

### Fabrication of Dendrimer Cryogels

PAMAM G4 at different concentrations (1, 5, and 10 w%) were dissolved in deionized water equilibrated at 25 °C. The prepared PAMAM G4.0 aqueous solution and PEGDA were precooled to 4 °C before use. PEGDA was added to the dendrimer aqueous solution (the molar ratio of amine/acrylate = 1/1), and the mixture was vortexed for 30 s at 25 °C. The mixture was then transferred to a 5 ml Teflon beaker (20 mm OD, 17 mm ID, 26 mm H) and kept at −20 °C to allow for the cryopolymerization. After 17 h cryopolymerization, the resulting dendrimer cryogels (CG-G4-1%, CG-G4-5%, and CG-G4-10%) were obtained after freeze-drying. CG-G1-5% was prepared following the same procedure as CG-G4-5%. Chitosan cryogel (CG-chitosan) was prepared mixing 2 mL of saturated chitosan solution (approximately 17 mg chitosan) in pH 2 buffer (Na2HPO4-citric acid) with 28 mg of PEG DA. The mixture was vortexed for 30 s at 25 °C, transferred to a 5 ml Teflon beaker and kept at −20 °C to allow for cryopolymerization. After 17 h cryopolymerization, the resulting CG-chitosan was obtained after freeze-drying.

### Scanning Electron Microscopy (SEM)

The morphological features of the cryogels were examined under a scanning electron microscope JEOL LV-5610 or a field emission SEM microscope (Hitachi FE-SEM Su-70). Lyophilized cryogels mounted on carbon tapes were coated with platinum for 90 seconds using an ion sputter. To image compressed dendrimer cryogel samples with SEM, the samples were placed in a clamp to maintain a strain of approximately 70% as determined by using a caliper. SEM images were analyzed using ImageJ2 software analysis to determine the pore size and wall thickness of the dendrimer cryogel. The analysis was performed on at least three samples and at least 20 measurements per sample.

### Porosity Measurements

The porosity of the cryogel was estimated by using the hexane uptake method. The freeze-dried cryogels were first weighed and then immersed in hexane for 1 h, excess hexane was removed, and the samples were weighted. Porosity was calculated using the following equation:

$$P \% =\,\frac{\frac{{m}_{{\rm{s}}}-{m}_{{\rm{d}}}}{{\rho }_{{\rm{Hex}}}}}{\frac{{m}_{{\rm{d}}}}{{\rho }_{{\rm{CG}}}}}\times 100$$

where md and ms are the weights of the cryogels before and after saturated hexane uptake, ρHex and ρCG are the density of hexane and cryogels. The densities of cryogels were calculated by the ratio of mass to volume of the cylindrical cryogels with defined dimensions.

### Swelling Studies

Water absorption kinetics of cryogels (CG-G4-1%, CG-G4-5%, and CG-G4-10%) was determined. Each lyophilized cryogel was immersed and incubated in 1 mL of PBS (pH = 7.4) at 37 °C. The supernatant was gently sucked out at different time intervals, and the swollen hydrogel sample was weighed. The measurement period was up to 12 h to reach the maximum absorption. The swelling ratio (%) = (WtW0)/W0 × 100, where Wt represents the mass of the swollen sample and W0 represents the initial mass of the dry sample. The swelling kinetics of all the three cryogel in pH 5.3 PBS and pH 1.2 PBS were also studied following the same procedure as above.

Each lyophilized cryogel was weighed as m0 and then saturated with PBS (pH = 7.4, 5.3, 1.2) at 37 °C. After the saturation, 2 mL fresh PBS (pH = 7.4, 5.3, 1.2) was added and incubated at 37 °C for 24 h, 48 h and 7 days, respectively. At different time intervals PBS was gently sucked out and samples were freeze-dried and re-weighed as mde. The degree of degradation (%) = (m0mde)/m0 × 100.

### Fourier Transform Infrared Spectroscopy (FTIR)

FTIR spectra of PAMAM dendrimer G4, PEG DA, CG-G4-1%, CG-G4-5%, and CG-G4-10% in dry state were recorded on Nicolet iS5 (ThermoFisher Scientific) equipped with iD7 ATR.

### Rheological Measurements

The rheological test was performed on samples (20 mm diameter disks). The test was conducted on both dry and hydrated samples on a temperature controlled plate of a Discovery Hybrid Rheometer (HR-3, TA instruments). Hydrated samples were immersed in 1 mL of PBS for 1 h before blot drying. Each set of samples on the plate at 37 °C was subjected to compression and shear stress by a 20 mm diameter parallel plate. An amplitude sweep was performed to confirm that all the measurements were conducted within the linear viscoelastic region. Oscillatory frequency sweeps were then carried out with a constant strain of 1% in the frequency region of 0.1–100 rad/s.

### Compression Testing

Cylindrical dendrimer cryogels with defined dimensions were subjected to compression test on a TA Instruments RSA-III dynamic mechanical analyzer (DMA). The samples (~12 mm in diameter and 8 mm in height) for compression tests were compressed up to 70% of their original length at the rate of 0.01 mm/s. The compression modulus was calculated from the slope of the linear section of the stress-strain curve. For cyclical compression test at −20 °C, 25 °C, and 100 °C, the rate of 0.2 mm/s was adopted. The strain of cyclical compression was fixed to 70%. The specimens (~7 mm in diameter and 9 mm in height) for dynamic temperature ramp tests were carried out under a nitrogen atmosphere from −80 °C to 240 °C at a temperature ramp of 5 °C/min. The frequency and strain were set at 1 Hz and 1%, respectively. One hundred relatively constant manual compressions were applied to CG-G4-5% after 24 h storage at −80, −20, and 100 °C, respectively.

## References

1. Mather, B., Viswanathan, K., Miller, K. & Long, T. Michael addition reactions in macromolecular design for emerging technologies. Prog Polym Sci 31, 487–531, https://doi.org/10.1016/j.progpolymsci.2006.03.001 (2006).

2. Nair, D. et al. The thiol-Michael addition click reaction: a powerful and widely used tool in materials chemistry. Chem Mater 26, 724–744, https://doi.org/10.1021/cm402180t (2014).

3. Lynn, D. & Langer, R. Degradable poly(beta-amino esters): synthesis, characterization, and self-assembly with plasmid DNA. J Am Chem Soc 122, 10761–10768, https://doi.org/10.1021/ja0015388 (2000).

4. Hoffmann, C., Stuparu, M., Daugaard, A. & Khan, A. Aza-Michael addition reaction: post-polymerization modification and preparation of PEI/PEG-based polyester hydrogels from enzymatically synthesized reactive polymers. J Polym Sci Pol Chem 53, 745–749, https://doi.org/10.1002/pola.27498 (2015).

5. Wang, J., He, H., Cooper, R. C. & Yang, H. In situ-forming polyamidoamine dendrimer hydrogels with tunable properties prepared via aza-Michael addition reaction. ACS Appl Mater Inter 9, 10494–10503, https://doi.org/10.1021/acsami.7b00221 (2017).

6. Tomalia, D. A. et al. Dendritic macromolecules: synthesis of starburst dendrimers. Macromolecules 19, 2466–2468, https://doi.org/10.1021/ma00163a029 (1986).

7. Tomalia, D. A. & Khanna, S. N. A systematic framework and nanoperiodic concept for unifying nanoscience: hard/soft nanoelements, superatoms, meta-atoms, new emerging properties, periodic property patterns, and predictive mendeleev-like nanoperiodic tables. Chem Rev 116, 2705–2774, https://doi.org/10.1021/acs.chemrev.5b00367 (2016).

8. Desai, P. N., Yuan, Q. & Yang, H. Synthesis and characterization of photocurable polyamidoamine dendrimer hydrogels as a versatile platform for tissue engineering and drug delivery. Biomacromolecules 11, 666–673, https://doi.org/10.1021/bm901240g (2010).

9. Lee, C. C., MacKay, J. A., Frechet, J. M. & Szoka, F. C. Designing dendrimers for biological applications. Nat Biotechnol 23, 1517–1526, https://doi.org/10.1038/nbt1171 (2005).

10. Yang, H., Tyagi, P., Kadam, R. S., Holden, C. A. & Kompella, U. B. Hybrid dendrimer hydrogel/PLGA nanoparticle platform sustains drug delivery for one week and antiglaucoma effects for four days following one-time topical administration. ACS Nano 6, 7595–7606, https://doi.org/10.1021/nn301873v (2012).

11. Ertürk, G. & Mattiasson, B. Cryogels-versatile tools in bioseparation. J Chromatogr A 1357, 24–35, https://doi.org/10.1016/j.chroma.2014.05.055 (2014).

12. Carvalho, B. M. A. et al. Cryogel poly(acrylamide): synthesis, structure and applications. Sep Purif Rev 43, 241–262, https://doi.org/10.1080/15422119.2013.795902 (2014).

13. Zeng, Y. et al. Injectable microcryogels reinforced alginate encapsulation of mesenchymal stromal cells for leak-proof delivery and alleviation of canine disc degeneration. Biomaterials 59, 53–65, https://doi.org/10.1016/j.biomaterials.2015.04.029 (2015).

14. Kumar, A. & Srivastava, A. Cell separation using cryogel-based affinity chromatography. Nat Protoc 5, 1737–1747, https://doi.org/10.1038/nprot.2010.135 (2010).

15. Ozmen, M. M., Fu, Q., Kim, J. & Qiao, G. G. A rapid and facile preparation of novel macroporous silicone-based cryogels via photo-induced thiol-ene click chemistry. Chem Commun 51, 17479–17482, https://doi.org/10.1039/C5CC07417G (2015).

16. Savina, I. N., Ingavle, G. C., Cundy, A. B. & Mikhalovsky, S. V. A simple method for the production of large volume 3D macroporous hydrogels for advanced biotechnological, medical and environmental applications. Sci Rep 6, 21154, https://doi.org/10.1038/srep21154 (2016).

17. Ak, F., Oztoprak, Z., Karakutuk, I. & Okay, O. Macroporous silk fibroin cryogels. Biomacromolecules 14, 719–727, https://doi.org/10.1021/bm3018033 (2013).

18. Kumari, J., Karande, A. A. & Kumar, A. Combined effect of cryogel matrix and temperature-reversible soluble–jnsoluble polymer for the development of in vitro human liver tissue. ACS Appl Mater Inter 8, 264–277, https://doi.org/10.1021/acsami.5b08607 (2016).

19. Oelschlaeger, C., Bossler, F. & Willenbacher, N. Synthesis, structural and micromechanical properties of 3D hyaluronic acid-based cryogel scaffolds. Biomacromolecules 17, 580–589, https://doi.org/10.1021/acs.biomac.5b01529 (2016).

20. Sedlačík, T. et al. Macroporous biodegradable cryogels of synthetic poly(α-amino acids). Biomacromolecules 16, 3455–3465, https://doi.org/10.1021/acs.biomac.5b01224 (2015).

21. Shirbin, S. J., Karimi, F., Chan, N. J.-A., Heath, D. E. & Qiao, G. G. Macroporous hydrogels composed entirely of synthetic polypeptides: biocompatible and enzyme biodegradable 3D cellular scaffolds. Biomacromolecules 17, 2981–2991, https://doi.org/10.1021/acs.biomac.6b00817 (2016).

22. Welzel, P. B. et al. Macroporous starPEG-heparin cryogels. Biomacromolecules 13, 2349–2358, https://doi.org/10.1021/bm300605s (2012).

23. Béduer, A. et al. A compressible scaffold for minimally invasive delivery of large intact neuronal networks. Adv Healthc Mater 4, 301–312, https://doi.org/10.1002/adhm.201400250 (2015).

24. Bencherif, S. A. et al. Injectable cryogel-based whole-cell cancer vaccines. Nat Commun 6, 7556, https://doi.org/10.1038/ncomms8556 (2015).

25. Han, M.-E., Kang, B. J., Kim, S.-H., Kim, H. D. & Hwang, N. S. Gelatin-based extracellular matrix cryogels for cartilage tissue engineering. J Ind Eng Chem 45, 421–429, https://doi.org/10.1016/j.jiec.2016.10.011 (2017).

26. Henderson, T. M. A., Ladewig, K., Haylock, D. N., McLean, K. M. & O’Connor, A. J. Cryogels for biomedical applications. J Mater Chem B 1, 2682–2695, https://doi.org/10.1039/C3TB20280A (2013).

27. Neo, P. Y., Shi, P., Goh, J. C. & Toh, S. L. Characterization and mechanical performance study of silk/PVA cryogels: towards nucleus pulposus tissue engineering. Biomed Mater 9, 065002, https://doi.org/10.1088/1748-6041/9/6/065002 (2014).

28. Newland, B. et al. Tackling cell transplantation anoikis: an injectable, shape memory cryogel microcarrier platform material for stem cell and neuronal cell growth. Small 11, 5047–5053, https://doi.org/10.1002/smll.201500898 (2015).

29. Priya, S. G. et al. Bilayer cryogel wound dressing and skin regeneration grafts for the treatment of acute skin wounds. ACS Appl Mater Inter 8, 15145–15159, https://doi.org/10.1021/acsami.6b04711 (2016).

30. Pumberger, M. et al. Synthetic niche to modulate regenerative potential of MSCs and enhance skeletal muscle regeneration. Biomaterials 99, 95–108, https://doi.org/10.1016/j.biomaterials.2016.05.009 (2016).

31. Raina, D. B. et al. Biocomposite macroporous cryogels as potential carrier scaffolds for bone active agents augmenting bone regeneration. J Control Release 235, 365–378, https://doi.org/10.1016/j.jconrel.2016.05.061 (2016).

32. Sahiner, N., Sagbas, S., Sahiner, M. & Silan, C. P(TA) macro-, micro-, nanoparticle-embedded super porous p(HEMA) cryogels as wound dressing material. Mater Sci Eng C 70, 317–326, https://doi.org/10.1016/j.msec.2016.09.025 (2017).

33. Thönes, S. et al. New e-beam-initiated hyaluronan acrylate cryogels support growth and matrix deposition by dermal fibroblasts. Int J Biol Macromol 94, 611–620, https://doi.org/10.1016/j.ijbiomac.2016.10.065 (2017).

34. Xu, C. et al. Development of dopant-free conductive bioelastomers. Sci Rep 6, 34451, https://doi.org/10.1038/srep34451 (2016).

35. Tomczak, N. & Vancso, G. J. Elasticity of single poly(amido amine) dendrimers. Macromol Rapid Comm 28, 1640–1644, https://doi.org/10.1002/marc.200700202 (2007).

## Acknowledgements

The authors thank Prof. Kenneth J. Wynne and Dr. Chengyu Wang (Department of Chemical and Life Science Engineering, Virginia Commonwealth University) for the use of TA Instruments RSA-III dynamic mechanical analyzer (DMA). This work was supported, in part, by the National Institutes of Health (R01EY024072).

## Author information

Authors

### Contributions

J.W. and H.Y. conceived the project, designed the experiments and wrote the manuscript. J.W. conducted all the experiments.

### Corresponding author

Correspondence to Hu Yang.

## Ethics declarations

### Competing Interests

The authors declare no competing interests.

Publisher's note: Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.

## Rights and permissions

Reprints and Permissions

Wang, J., Yang, H. Superelastic and pH-Responsive Degradable Dendrimer Cryogels Prepared by Cryo-aza-Michael Addition Reaction. Sci Rep 8, 7155 (2018). https://doi.org/10.1038/s41598-018-25456-y

• Accepted:

• Published:

• DOI: https://doi.org/10.1038/s41598-018-25456-y

• ### Dendrimer-based drug delivery systems: history, challenges, and latest developments

• Juan Wang
• Boxuan Li
• Hu Yang

Journal of Biological Engineering (2022)