Recent Development and Applications of Polydopamine in Tissue Repair and Regeneration Biomaterials

Abstract

The various tissue damages are a severe problem to human health. The limited human tissue regenerate ability requires suitable biomaterials to help damage tissue repair and regeneration. Therefore, many researchers devoted themselves to exploring biomaterials suitable for tissue repair and regeneration. Polydopamine (PDA) as a natural and multifunctional material which is inspired by mussel has been widely applied in different biomaterials. The excellent properties of PDA, such as strong adhesion, photothermal and high drug-loaded capacity, seem to be born for tissue repair and regeneration. Furthermore, PDA combined with different materials can exert unexpected effects. Thus, to inspire researchers, this review summarizes the recent and representative development of PDA biomaterials in tissue repair and regeneration. This article focuses on why apply PDA in these biomaterials and what PDA can do in different tissue injuries.

Graphical Abstract

Keywords:

• polydopamine
• biomaterial
• tissue damage
• tissue regeneration

Introduction

Accident trauma, inflammation, aggressive tumors, infectious diseases, and acquired or congenital abnormalities may cause severe damage to tissue.^1–3 Unfortunately, the limited self-healing ability of tissues means that if the damage surpasses the ability of self-healing, the tissue damage will not heal, the healing process will be prolonged, and tissue function will be compromised. Biomaterials can play a role in various tissue repair and regeneration stages, such as carrying drugs to promote tissue growth, providing antibacterial, antioxidant, anti-inflammatory properties, and substituting defective tissue, among others.^4–8 To achieve optimal healing of damaged tissues, it is essential to match the functions of the biomaterial to the multiple factors influencing the healing process. Moreover, it is crucial for biomaterials to be low-toxic or, ideally, non-toxic. Thus, researchers prefer materials that possess a range of properties suitable for tissue repair and regeneration, such as materials inspired and derived from nature.

Over the past decade, mussel-inspired and melanin-like materials have gained increasing attention in the biomaterials science community.^9,10 The reality is that despite being inspired by different natural entities, the functional chemical components of these two types of materials are the same. Marine mussels are capable of secreting various types of foot proteins that allow them to adhere to different foreign surfaces, including the skin of marine animals, rocks, and metal ships.¹¹ Six types of mussel foot proteins have been identified, with the most abundant being 3,4-dihydroxy-l-phenylalanine (DOPA), glycine, lysine, tyrosine, and asparagine.^12,13 Melanin-like materials typically encompass eumelanin, neuromelanin, allomelanin, and pheomelanin.^14,15 A schematic representation of the elements of melanin-like and mussel-inspired materials as Figure 1. The high concentration of catechol from DOPA and amine groups in these foot proteins gives them strong adhesive properties.¹⁶ They can convert specific spectrum’s photon energy into heat and chemical energy.^17,18 Additionally, the polymer’s possession of free phenolic groups confers it with the ability to scavenge various reactive oxygen and nitrogen species.^19,20 Moreover, owing to the abundance of binding groups, such as amines and catechols, among others, they exhibit exceptional chelating capacity.²¹ The aforementioned properties make mussel-inspired and melanin-like materials promising platform for several important biomedical applications, including tissue adhesion, drug-delivery systems, antioxidant therapy, and phototherapy systems. These materials were initially obtained from sources such as human hair, sepia ink, grape extracts, oligomeric proanthocyanidins, and others.^22–24 The limited availability of raw materials and the difficulty in obtaining them are two significant challenges for their usage in clinical applications. According to Lee et al, dopamine (DA) was found to be a suitable replacement for natural materials, as it possesses both catechol and amine functionalities.²⁵ DA is well-known as a neurotransmitter in human body and associate with disease like Parkinson’s disease.²⁶ Surprisingly, they discovered that the straightforward structure of DA serves as a potent building block, facilitating the spontaneous deposition of thin polymer films on nearly any material surface. Moreover, these deposited films can be readily tailored to fulfill a wide array of functional applications.²⁵ Commercial DA hydrochloride is produced by chemical synthesis and can be stored easily.²⁷ The DA hydrochloride will self-polymerize into PDA nanoparticles (NPs) in alkaline environment. PDA NPs with mesoporous structures were obtained after removing the alkaline solution.^28,29 Zeng et al reported an average nanoparticle diameter of approximately 200 nm,³⁰ and while Yuan et al measured the average pore diameter to be around 16.676 nm in their study.²⁸ Even though many details of the PDA function and structure still remain to explore, there is little doubt that PDA have same properties for tissue repair and regeneration as mussel-inspired and melanin-like materials.

Figure 1 Schematic representation of the elements of melanin-like and mussel-inspired materials.

Several researchers have reviewed the PDA biomaterials related to tissue repair and regeneration.^31–33 However, the emphasis of these reviews has been primarily on the wound-healing properties inherent in PDA or on the overall ability of these biomaterials composed of multiple materials and PDA to facilitate tissue regeneration. However, as the application of PDA becomes more widespread, recent articles on biomaterials incorporating PDA have investigated additional strategies for applying PDA. These strategies are not just simple combinations of different functional materials with PDA to enhance its ability to promote tissue repair, but rather incorporating PDA as a part of a biological material system, leveraging not only its own function but also the interaction between PDA and other materials for greater impact. Therefore, this review analyzes the latest representative PDA application strategies in biomaterials (Table 1) incorporating PDA for tissue regeneration and provides some inspiration for subsequent researchers who want to use PDA for tissue regeneration.

Table 1 Selected and Representative PDA Related Materials in Tissue Repair and Regeneration

Application	Materials	Mechanism	Ref
Tissue adhesive and hemostasis
Tissue adhesive	Introduced PDA on HA adhesion system	Adhesive	[43]
Hemostasis	Hydroxyapatite hemostatic material with PDA	Adhesive	[53]
Hemostasis	PDA modified carboxymethyl chitin microspheres	Adhesive, Modification	[55]
Hemostasis	Hemostatic sponge modified by PDA	Adhesive, Modification	[56]
PDA carries a comprehensive range of drugs
Mandibular Bone Defects	GPEGD hydrogel with BMP-2 loaded PDA/heparin NPs	Antioxidation, Protein Loaded	[71]
Bone regeneration	PHA scaffolds coat with PDA-captured BMP-2	Modification, Protein Loaded	[77]
Bone regeneration	PDA and TA microspheres with exosomes	Exosomes Loaded	[78]
Osseointegration, Antibacterial	PDA with LUT modified Ti substrate	Modification, Drugs Loaded	[57]
Radiation pneumonitis	Curcumin-loaded mesoporous PDA NPs	Drugs Loaded	[99]
PDA applications for building controlled drug release materials
Temperature-response	PDA coating with TSLs and teriparatide	PTT, Drugs Loaded	[105]
Ag self-rechargeable	Electrospun scaffold and PDA coated MX@AgP bio-HJs	PTT, Chelate Ag	[114]
pH-Responsive	TCPP-loaded PDA introduced PLU@PTc hydrogels	PTT	[124]
pH-Responsive	ZIF-8-coated PDA and loaded PES	PTT and Drugs loaded	[123]
Multi-layers structure tissue regeneration biomaterials with PDA
Auricle reconstruction	Multilayer EPL and FIB modification with PDA coating	Modification	[125]
Orthopedic implants	PDA immobilized on β-TCP scaffold modified by chitosan	Modification	[126]
Osseointegration	Multilayer COL1 constructed by PDA	Modification	[139]
Wound healing	PPy/PDA/PLLA three-layer core-shell structure	Modification	[128]
Self-healing and shape-memory PDA biomaterials
Wound dressing	Carboxymethyl chitosan-PDA hydrogels with PAM networks	Adhesive	[148]
Implant	PCL-PDA polyurethane	PTT	[153]
PDA absorbs some of the inflammatory factors
Rheumatoid arthritis	Dimethylamino group modified PDA NPs	Biodegradability, Adhesion	[160]
Bone regeneration	PDA-mediated GO and nanohydroxyapatite-incorporated conductive scaffold	Antioxidation	[166]
Spinal cord injury	PDA NPs with rapamycin	Antioxidation	[168]
Internal organs repairment and regeneration
Kidney	Injectable PDA-encapsulated MF NPs nanocomposites	Antioxidant	[161]

The Biomaterial for Wound Closure and Hemostasis with Adhesion Ability of PDA

As the scientists first noticed, PDA is an excellent adhesion material. PDA contains quinone, catechol, imine, amine functional groups and abundant π-conjugated structures.³⁴ The abundant π electrons in PDA confer it with a strong binding capacity for various molecules possessing π electrons through π-π stacking and π-cation interactions.³⁵

Tissue Adhesion Biomaterials with PDA for Wound Closure

Over the past few decades, medical tissue adhesives have been applied in surgical operations, especially when traditional suturing is not impractical or ineffective.³⁶ Currently, in many surgical procedures, the most commonly used tissue adhesives include fibrin glues, albumin-glutaraldehyde adhesives, and cyanoacrylates.³⁷ Nevertheless, the unstable efficacy, potential allergic reactions, and high toxicities associated with aldehyde-containing products severely restrict the clinical application of these tissue adhesives.^38–40

As early as 2016, Fan et al designed a DA conjugated gelatin macromer double-crosslinked tissue adhesive intended for internal medical use.⁴¹ Chen et al reported a strategy by horseradish peroxidase cross linking γ-glutamic acid conjugated with DA as a tissue adhesive for wound closure.⁴² Pandey et al introduced PDA on the simple HA and cross-linker adhesion system resulting in a significant increase in the adhesion of the material. To create a mussel-inspired HA-DA product, DA was grafted onto the hyaluronic acid (HA) backbone through (1-ethyl-3-(3-dimethylaminopropyl) carbodiimide-N-hydroxy-succinimide) EDC-NHS carbodiimide chemistry under aqueous conditions.⁴³ Upon introducing PDA to this HA-DA adhesive, the adhesion capability of the glue experiences a significant enhancement. The tissue adhesive properties of PDA NPs exhibit a correlation between higher adhesive strength and smaller particle size (Figure 2A). Although the adhesive ability of PDA still remains a lot to explore, the current studies are enough to prove PDA is an excellent material for wound closure, even better than some conventional materials.

Figure 2 (A) Schematic illustration of the usage and probable working principle of cross-linker adhesion system. The tissue adhesive properties of PDA NPs exhibit a correlation between higher adhesive strength and smaller particle size (*p<0.05). Reproduced with the permission from Pandey N, Soto-Garcia L, Yaman S, et al. Polydopamine nanoparticles and hyaluronic acid hydrogels for mussel-inspired tissue adhesive nanocomposites. Biomater Adv. 2022;134:112,589.⁴³ Copyright © 2022, with permission from Elsevier. (B and C) Porous carboxymethyl chitin microspheres with PDA (CMCHm-PDA) have better hemostatic performance (clotting time and blood loss) than a wide use commercial hemostatic agents Yunnan Baiyao^® (*p<0.05). Adapted from Carbohydrate Polymers, Volume 270, Leng F, Chen F, Jiang X. Modified porous carboxymethyl chitin microspheres by an organic solvent-free process for rapid hemostasis. Pages 118348. ⁴⁴ Copyright © 2021, with permission from Elsevier.

However, there are still some problems waiting to be solved, such as making products more conventional to apply in clinics and easily stored. Experiments should not only focus on the mechanical strength and physicochemical properties of PDA, but also consider its ability to support cell proliferation and tissue regeneration for effective wound closure. The process of wound closure not only closes the wound by adhesive simply, but also includes the following cell proliferation and tissue regeneration to close the wound in a real sense. Therefore, in addition to just in vitro tissue, we should test the healing effects of adhesion materials in vivo.

Hemostatic Biomaterials with PDA

PDA not only has the ability to adhere broken vessels and stop bleeding, but also effectively combines with conventional hemostatic materials that lack tissue and vessel adhesion abilities, such as chitosan,⁴⁵ silica NPs,⁴⁶ and graphene oxide (GO).⁴⁷ Furthermore, PDA can endow various clinical tools with hemostatic properties, such as needles,⁴⁸ hydrogels, and sponges.⁴⁹

The widely used commercial hemostatic materials have certain drawbacks. For instance, QuickClot^©, which has been extensively used in warfare and saved many soldiers during the Gulf War,⁵⁰ can cause scorching of the wound area and trigger allergic reactions due to heat release during the hemostatic process.⁵¹ In addition, the presence of oxygen-containing groups in a new promising hemostatic agent, GO, raises concerns about toxicity.⁵²

Gong et al designed a hydroxyapatite hemostatic material with PDA.⁵³ They work out that the best ratio of nano hydroxyapatite and DOPA hydrochloride is 20:1. The hemostatic capacity between a popular commercial production Celox and this composite was studied. The PM has better performance in the longest hemostatic time, the blood loss and uncontrolled bleeding circumstance than Celox and control. Although Celox is popular in clinical use, it was reported to perform poorly on uncontrolled bleeding.⁵⁴ For this circumstance, Leng et al modified porous carboxymethyl chitin microspheres with PDA (CMCHm-PDA). This material displayed better hemostatic performance than two wide use commercial hemostatic agents Yunnan Baiyao^® or /and Quickclean^® in three kinds of rat bleeding models (tail amputation model, liver injure model and femoral arterial/venous cutting model), especially for CMCHm-PDA, the bleeding time was only 45s in the femoral artery/vein cut model (Figure 2B and C).⁴⁴ For conventional hemostatic material, Cao et al design a multifunctional hemostatic sponge modified by PDA. Furthermore, in rat tail amputation models, the sponge demonstrated a superior hemostatic effect compared to conventional gauze. This enhancement can be attributed to the improved procoagulant activity and increased adhesion of red blood cells and platelets to the sponge.^55,56

PDA Carries a Comprehensive Range of Drugs That Promote Tissue Regeneration and Repair

PDA has a strong binding capacity for a variety of drugs that facilitate tissue repair, like various metal ions, antibiotics, proteins, exosomes, etc.^57–63

A Variety of Protein-Based Growth Factors Combine with PDA for Tissue Growth

For achieving more desirable tissue growth, the method commonly employed in tissue repair, particularly in osseointegration, is the local delivery of growth factor agents.⁶⁴ Due to the short half-life and rapid clearance of protein-based growth factors from the body, traditional methods involving covalent or weak electrostatic encapsulation of proteins into natural hydrogels might lead to reduced bioactivity or potentially trigger side effects in vivo.^65,66 The latest researches on PDA and protein-based growth factors have shown that these problems can be effectively addressed and perfectly combined PDA.

Bone morphogenetic protein-2 (BMP-2) is an essential factor known for promoting osteogenesis and has found widespread use in clinical applications for bone repair and regeneration.^67,68 The remarkable bone regenerative ability of BMP-2 has captivated numerous researchers to incorporate it into biomaterials. Studies have shown that BMP-2 can activate cellular pathways associated with osteogenesis and effectively enhance bone formation in animal experiments.^69,70 Wu et al designed a kind of biomimetic hydrogel may be used as a translational potential material to promote the construction and regeneration of mandibular bones. They combined PDA to scavenge reactive oxygen species (ROS) and heparin (PDAH) to prolong and control BMP-2 release (Figure 3A).⁷¹ Heparin, a naturally occurring glycosaminoglycan, possesses a high negative charge and exhibits a strong affinity for a class of positively charged growth factors.^72–75 DA can undergo a chemical reaction with heparin through the interaction between the carboxyl groups or sulfate groups of heparin and the amino groups of PDA polymers. Typical images indicated that with the further increase of heparin concentration, the mixtures tend to form NP aggregates with the smaller particle size. In details, the BMP-2 absorption efficiencies on the PDA and PDAH NPs were 68.2% and 90.03%, respectively. Therefore, heparin-functionalized PDA NPs can enhance the loading capacity of BMP-2. Additionally, due to the strong affinity interactions between BMP-2 and heparin, these NPs can sustain the release of BMP-2 over time.⁷⁶

Figure 3 (A) PDA/heparin nanoparticles were prepared to improve the encapsulation efficiency and control BMP-2 release behavior. Reproduced from Wu Y, Li X, Sun Y, et al. Multiscale design of stiffening and ROS scavenging hydrogels for the augmentation of mandibular bone regeneration. Bioact Mater. 2023;20:111–125.⁷¹ Copyright © 2022 KeAi, open access. (B) Fabrication of bone morphogenetic protein-2 (BMP2)-functionalized 3D-printed P34HB scaffold via polydopamine surface modification.⁷⁷ (C) The amount of attached BMP2 was observed to increase with the increasing initial concentration of BMP-2.⁷⁷ (D) Percentage of released BMP2 from BMP2-functionalized 3D-printed P34HB scaffolds during 30 days incubation in PBS buffer.⁷⁷ (B–D) Used with permission of Royal Society of Chemistry, from Zhang X, Li J, Chen J, et al. Enhanced bone regeneration via PHA scaffolds coated with polydopamine-captured BMP2. J Mater Chem B. 022;10(32):6214–6227.⁷⁷ ; permission conveyed through Copyright Clearance Center, Inc. (E) Schematic illustration showing the PDA coating of porous microspheres and the subsequent exosome adsorption via bioinspired dopamine chemistry. Gao YK, Yuan ZY, Yuan XJ, et al. Bioinspired porous microspheres for sustained hypoxic exosomes release and vascularized bone regeneration. Bioact Mater. 2022;14:377–388. doi:10.1016/j.bioactmat.2022.01.041.⁷⁸ Copyright © 2022 KeAi, open access.

The conservative chemical structures of biomaterials, coupled with the lack of simple and moderate modification methods and the instability of bioactive substances (particularly growth factors), result in poor osteoinductive signals. This ultimately hinders cell adhesion, growth, and differentiation, leading to hindered bone restoration and regeneration. Zhang et al built a scaffold coated with PDA, the PDA can capture BMP-2 in BMP-2 solution (Figure 3B).⁷⁷ The amount of attached BMP-2 was observed to increase with the increasing initial concentration of BMP-2 (Figure 3C). The release of BMP-2 from the scaffolds exhibited no burst effect, with only 4.72 ± 1.55% of BMP-2 released within the first 24 hours. Furthermore, the released BMP-2 percentage remained stable over the course of 30 days, leading to a cumulative release percentage of 86.64 ± 1.53% (Figure 3D). For repairing bone defects resulting from surgery, conventional implants like titanium-based alloys and emerging materials like polyetheretherketone (PEEK) have become the essential materials used in orthopedic and dental implants.⁷⁹ The highly adhesive PDA layer on the substrate not only imparts a hydrophilic surface to the substrate,^80,81 but also provides a secondary reaction platform for immobilizing growth factors like BMP-2. This is possible due to the abundant catechol and amine groups in PDA, which can react with amine- and thiol-containing substances through Michael addition or Schiff base reactions.^82–84 BMP-2 can be combined with other sustained-release drug carriers, such as polylactic acid-glycolic acid (PLGA), which offers flexible regulation through adjustments in the lactide/glycolide ratio and the polymer molecular weight.⁸⁵ Then the microsphere carriers bond to the PDA coating of the PEEK surface after plasma pretreatment. The strategy of combining BMP-2 and PDA to promote bone healing may also provide implications for other drugs combined with PDA to promote bone healing.

PDA and Exosomes Binding Promotes Tissue Repair

Exosomes are small extracellular vesicles (30–150 nm in diameter) secreted by cells, demonstrating promising therapeutic potential as alternatives to living cells. They possess equivalent or even superior efficacy while requiring no external maintenance.^86,87 In tissue regeneration, the therapeutic efficacy of exosomes is often limited by their low retention and instability.^88,89 Hydrogels have been utilized as exosome carriers, enabling the encapsulation of exosomes, thereby facilitating the delivery of exosomes to the target site and enhancing their local retention.^90,91 Indeed, exosomes encapsulated in hydrogels often face challenges with long-term preservation, as they cannot be effectively stored over extended periods. To preserve exosomes using the lyophilization method, the addition of cryoprotectants becomes necessary to maintain their stability.⁹² Surface adsorption via affinity coatings, which avoids the need for the lyophilization step, could be a more gentle and friendly approach for transporting delicate exosomes. This method offers a promising alternative for preserving and delivering exosomes without subjecting them to potentially damaging freeze-drying processes.⁹³

In their study, Gao et al conducted a comparison of the loading efficiency and release kinetics of different surface coating methods, which included PDA, polyethyleneimine, tannic acid (TA), and heparin coatings (Figure 3E).^94–96 The PDA and TA coatings demonstrated sustained release of exosomes for over one week, which was attributed to the adhesive properties of the catechol groups in these coatings. They utilized bioinspired injectable porous PDA-modified poly(lactic-co-glycolic acid) microspheres, which led to enhanced loading efficiency, an optimized release profile, and preserved bioactivity of the exosomes microspheres.⁷⁸

Combination of PDA and Bioactive Natural Molecules Drugs for Tissue Repair

Many natural drugs are being discovered in the field of wound repair, but their diverse mechanisms of action require a powerful drug carrier with controlled release capabilities to carry out their effects. There have been many studies showing that PDAs have this capability.

Luteolin (LUT, a quorum sensing inhibitor) is a natural polyphenol flavonoid that exhibits promising characteristics as a natural drug for inhibiting the colony effect of bacterial biofilms. It demonstrates excellent capabilities in inhibiting and dispersing biofilms.⁹⁷ Hu et al was loaded in PDA NPs to form PDA-LUT nanosystem.⁵⁷ In response to the weak acidic environment of biofilm infections, LUT undergoes controlled release and selectively targets bacterial biofilms and pathogenic bacteria. This targeted action hinders the communication of bacterial quorum sensing signals, rendering them in a sensitive state.

Curcumin, a polyphenolic compound primarily extracted from the rhizome of turmeric, has been reported to alleviate injury through its anti-inflammatory, anti-oxidation, and free radical scavenging properties.⁹⁸ In a study conducted by Chen et al, curcumin-loaded mesoporous PDA NPs were prepared and intratracheally administered to the lung for the prevention and treatment of radiation pneumonitis.⁹⁹ The mesoporous structure of PDA offered a large inner space and numerous surface pores, resulting in high drug loading efficiency for curcumin. Additionally, the amorphous state of curcumin in PDA improved its dissolution and release, facilitating quick prevention and treatment upon pulmonary delivery.

The absence of a scientific drug-release system led to unstable drug release, resulting in the wastage of valuable Chinese herbal medicines and causing various discomforts to the patients. PDA as a highly binding material could provide a platform for the orderly release of many of these natural drugs.

PDA Applications for Building Controlled Drug Release Materials

Thermosensitive and Intelligent Drugs Delivery System Control by PTT Temperature-Response of PDA

To ensure effective and safe treatment of a damaged wound, it is crucial to design a drug release modulation system that allows for controlled release of the required medication. The approach taken for drug release modulation should be tailored to the specific drug being used, as different drugs have varying mechanisms of action and optimal release profiles.¹⁰⁰ For instance, growth-promoting drugs may require a sustained release over an extended period, while antibiotics may need to be released fully and rapidly to achieve optimal efficacy. If the drug release is not properly controlled, there is a risk that the medication may be ineffective or even contribute to drug resistance. To achieve controlled drug release, researchers have developed various drug delivery systems that utilize pH, ultrasound, or near-infrared (NIR) laser stimuli. These systems enable a controllable release of bioactive components in response to specific triggers, enhancing the therapeutic efficacy and minimizing drug wastage.¹⁰¹ However, traditional drug delivery systems often lack sensitivity and have limited short-term release capabilities. Fortunately, PDA can offer several benefits in drug delivery. Not only can PDA increase the amount of drug adsorption, but its PTT properties also enable the controlled release and accumulation of drugs. Indeed, the incorporation of PDA in drug delivery systems can lead to localized temperature increases. This property can be utilized to increase the rate of drug diffusion or enable an on-off effect, which can be activated on demand by irradiating the sample with a specific stimulus, such as near-infrared (NIR) light. This controlled drug release mechanism holds great promise for targeted and efficient drug delivery applications.^102,103 NIR irradiation has been shown to enhance antibiotic delivery, possibly due to physical interactions between the drug and the PDA that are sensitive to temperature changes. In fact, studies have demonstrated that the release rate of antibiotics dissolved in hydrogel with PDA under NIR is faster than without NIR.¹⁰⁴ These findings suggest that PDA can play a critical role in the development of smart drug release control biomaterials.

Che et al designed a biomimetic and bioactive scaffold with intelligently pulsatile teriparatide delivery for local and systemic osteoporosis regeneration. They have utilized thermosensitive liposomes (TSLs) as temperature-reactive media.¹⁰⁵ These TSLs can be easily controlled by temperature, allowing for stable drug retention at lower temperatures and rapid drug release at higher temperatures. This temperature-sensitive behavior offers a versatile and precise drug delivery mechanism that can be tailored to specific therapeutic needs.¹⁰⁶ Moreover, when the temperature of the system rises above the transition temperature, the extravasation of TSLs is significantly enhanced, leading to an immediate and rapid release of payloads.¹⁰⁷ This makes TSLs a promising candidate for controlled drug delivery, as they offer the ability to trigger drug release at the desired location and time by manipulating temperature. Liposomes are structures that can quickly recover to a dense form and remain stable with little drug release once the temperature drops below the transition temperature. In order to manage the TSLs reaction, PDA can be used as a heater under NIR, which can penetrate deep tissues and provide acute temperature control.¹⁰⁸ Recent studies have shown that using this technique, drug release from TSLs can be pulsatile and closely aligned with the average release rate over a 14-day period, in contrast to groups without NIR control, which released 34.7% of drugs within the first two days. Another strategy for controlling drug release is to combine TSLs with materials that respond to the PTT temperature-stimulated response. Exactly, phase-change materials like lauric acid and stearic acid (PCM) can serve as thermal response “gatekeepers” in drug delivery systems. When these materials are combined with PDA and subjected to NIR irradiation, and the temperature rises above their melting point (39−40 °C), the PCM undergoes a gradual melting process. This temperature-triggered melting, in turn, sequentially triggers the release of antibiotic drugs that are concealed within the material, allowing for controlled and targeted drug delivery. This approach could offer new possibilities for developing targeted and effective drug delivery systems.³⁰

Metal ions, particularly silver (Ag), have been extensively studied and have been shown to possess broad-spectrum bacteriostatic properties. Ag has been demonstrated to penetrate bacterial cell membranes, disrupt internal proteins and genetic material, and ultimately lead to bacterial death.^109,110 Despite these advantages, the accumulation of metal ions and their cytotoxicity remains a significant concern as a potential side effect.¹¹¹ Recent studies show different strategies benefit from the PTT property. In 2013, Zhang et al synthesized hybrid materials consisting of Ag NPs, PDA, and graphene nanosheets as a novel antibacterial material.¹¹² Indeed, PDA exhibits excellent biocompatibility, which can help reduce the cytotoxicity of Ag⁺ and facilitate its combination with other materials.¹¹³ In a recent study by Yang et al, they developed a “Ag⁺ self-rechargeable” stubborn infected cutaneous nanofibrous membrane designed to recover released metal ions, which helps moderate their toxicity and replenish the antibacterial capacity of metal ion therapy. This innovative approach offers a sustainable and effective solution for combating bacterial infections while minimizing the harmful effects of metal ions on surrounding healthy tissues.¹¹⁴ They reach the metal ions self-rechargeable ability by combining PDA and photodynamic therapy (PDT, photosensitizers yield ROS under light irradiation with an accommodative wavelength) materials (Figure 4A–D). PDA’s redox-active catechol group undergoes spontaneous oxidation to quinone, which acts as a reducing agent to convert Ag⁺ ions to Ag⁰ NPs on the surface of PDA when exposed to moderate solution conditions (Figure 4C).^115,116 Under NIR irradiation, the Ag NPs on the surface of PDA are oxidized back into Ag⁺ ions and subsequently released into the wound again (Figure 4B). This process ensures that the synergistic therapy remains potent and effective, while maintaining a rechargeable function to sustain the antibacterial capacity over time. The ability to recycle and reuse the released metal ions enhances the overall therapeutic efficacy and makes the system more practical for long-term applications (Figure 4D).

Figure 4 (A) Illustration of the manufacturing procedure of the “self-rechargeable” membranes.¹¹⁴ (B) Diagram of the photothermal and photodynamic mechanism of the “self-rechargeable” system.¹¹⁴ (C) Antimicrobial and “self-rechargeable” effects.¹¹⁴ (D) In the “recycle-release” process, the “self-rechargeable” ability will gradually diminish, but PDA can slow this down significantly.¹¹⁴ Reproduced from Yang Y, Zhou X, Chan YK, et al. Photo-Activated Nanofibrous Membrane with Self-Rechargeable Antibacterial Function for Stubborn Infected Cutaneous Regeneration. Small. Mar 2022;18(12):e2105988.¹¹⁴ © 2022 Wiley-VCH GmbH.

pH-Responsive Bacteria Reactive Biomaterials with PDA

Bacterial growth during wound infection can result in tissue hypoxia, leading to glycolysis and acidification of the surrounding environment. The pH of infected wounds can drop to approximately 5.5.^117,118 The pH changes in infected wounds can be designed with a number of pH-responsive biomaterials for monitoring bacterial changes in wounds with PDA. Correct, PDA exhibits high sensitivity to acidic pH, which enables it to act as a switch for controlling drug release. In acidic environments, such as those found in certain disease sites or endosomes, PDA undergoes changes in its structure or properties, triggering the release of drugs from the carrier system. This pH-responsive behavior makes PDA an attractive candidate for targeted drug delivery, allowing for the release of drugs precisely at the intended site of action.^119,120

When exposed to a weak alkaline environment at room temperature, DA can undergo spontaneous polymerization and form a PDA film. This PDA film can effectively encapsulate drugs, providing a versatile and simple method for drug delivery and controlled release applications.¹²¹ In the acidic microenvironment of biofilms with a pH below 6.0, the outer layer of PDA degrades. This degradation process exposes the inner drugs within the PDA film to bacteria present in the deeper layers of the biofilm (Figure 5A). The pH-responsive nature of this strategy allows for on-demand drug release in situ, precisely targeting the biofilm microenvironment, and facilitating biofilm dispersion. This pH-responsive approach holds great promise for combating bacterial infections associated with biofilms, as it enhances drug delivery efficiency and the therapeutic effect. This pH-responsive strategy is well-suited for on-demand drug release in situ and biofilm dispersion.⁶¹

Figure 5 (A) Illustration of the pH-responsive nanocomposites (PDA@Kana-AgNP) coated with PDA based on kanamycin in combination with AgNPs. Reprinted from Colloids and Surface B: Biointerfaces, Volume 208, Li X, Li B, Liu R, Dong Y, Zhao Y, Wu Y. Development of pH-responsive nanocomposites with remarkably synergistic antibiofilm activities based on ultrasmall silver nanoparticles in combination with aminoglycoside antibiotics. Pages 112112.⁶¹ Copyright © 2021, with permission from Elsevier. (B) Bacterial infection triggers TCPP release to restore red fluorescence emission under illumination at 410 nm, and hydrogels generate antibacterial PDT under illumination at 660 nm. Hydrogels with wrapped bacterial debris are removed under illumination at 808 nm and changed into fresh hydrogel dressings to promote wound healing. Reproduced with permission from Ran P, Zheng H, Cao WX, et al. On-Demand Changeable Theranostic Hydrogels and Visual Imaging-Guided Antibacterial Photodynamic Therapy to Promote Wound Healing. Acs Appl Mater Inter. 2022.¹²² Copyright © 2022 American Chemical Society. (C) PES-release behavior from MPDA@ZIF-8/PES NPs at different pH without NIR irradiation.¹²³ (D) PES-release behavior of MPDA@ZIF-8/PES NPs at different pH under NIR irradiation.¹²³ Used with permission of the Royal Society of Chemistry from Peng D, Liu G, He Y, et al. Fabrication of a pH-responsive core-shell nanosystem with a low-temperature photothermal therapy effect for treating bacterial biofilm infection. Biomater Sci. 2021;9(22):7483–7491. ¹²³ Copyright © 2021, permission conveyed through Copyright Clearance Center.

A kind of pH-responsive bacteria monitoring wound hydrogel was developed by Ran et al using Tetrakis(4-carboxyphenyl)porphyrin (TCPP) and PDA¹²² (Figure 5B). TCPP generates a strong red fluorescence, but under physiological conditions, the fluorescence of TCPP is quenched by PDA NPs. However, in the acidic microenvironment of bacterial infection, TCPP is released from PDA NPs, leading to the restoration of fluorescence emissions, which enables real-time diagnosis under 410 nm illumination.¹²⁴

Peng et al developed a pH-responsive core-shell nanosystem designed to exhibit a low-temperature photothermal therapy (PTT) effect to treat bacterial biofilm-infection. This innovative nanosystem demonstrates effective potential in treating bacterial biofilm infections. The pH-responsive nature of the nanosystem allows for controlled drug release in acidic microenvironments, while the low-temperature PTT effect enhances its therapeutic efficacy against biofilm-associated infections.¹²³ Pifithrin-μ (PES) is a heat-shock protein inhibitor. In their research, Peng et al proposed integrating PES into the PTT system. They hypothesized that by doing so, the inclusion of PES could reduce the tolerance of bacteria to heat, consequently decreasing the temperature required for PTT to eliminate biofilms. This approach aims to enhance the treatment efficacy of bacterial infections by making the PTT system more effective in eradicating biofilms. They prepared zeolite-based imidazole framework (ZIF-8)-coated PDA core–shell NPs and then loaded PES. ZIF-8 is a type of pH-responsive metal–organic framework. It remains stable in physiological environments but degrades in an acidic environment. This degradation leads to the release of zinc ions, which can have various therapeutic effects and applications in drug delivery, tissue engineering, and other biomedical fields. The pH-responsive behavior of ZIF-8 makes it a promising candidate for targeted drug delivery and controlled release systems that can selectively release drugs in response to the acidic microenvironment of specific disease sites (Figure 5C and D). The outer shell ZIF-8 was used to load PES. The release of PES could be achieved by the degradation of the outer shell under the stimulation of the acidic environment caused by bacterial infection. Then, the released PES acted on the biofilm and reduced the heat tolerance of the bacteria in the biofilm. Therefore, through the combined action of PES and localized PTT stimulation, the biofilms were effectively ablated, and the bacteria were eliminated. This innovative approach allowed for low-temperature PTT, making it a promising strategy for the treatment of bacterial biofilm infections.

Multi-Layers Structure Tissue Regeneration Biomaterials with PDA

Tissue regeneration is a complex process that requires biomaterials to meet various demands, including moistness, cell adhesion, water absorption, and drug chelation. It is challenging for individual materials to possess all of these characteristics simultaneously. Therefore, the current approach is to combine different materials and optimize their interaction to achieve proper tissue regeneration. When modifying the surface of inert and non-bioactive tissue repair materials, a single biomaterial modification may not achieve the desired effect. Multiple modifications or the combination of different modification strategies may be necessary to achieve the desired properties.¹²⁵ To achieve the desired properties, layer-by-layer (LBL), core-shell, multi-layers, sandwich-like, and other techniques have been developed to layer different materials in an orderly fashion.^126–128 Among these techniques, the PDA coating has garnered more attention as a surface modification due to its essential roles in multilayer structures.^129–131

Layer-by-Layer Structure

LBL assembly, a highly promising technique, involves the fabrication of thin multilayer coatings through the electrostatic mutual attraction of oppositely charged polyelectrolytes. This approach allows for precise control over the coating thickness and composition, making it an attractive option for various applications, including drug delivery, tissue engineering, and surface modification.^132,133 Yin et al successfully modified the surface of high-density polyethylene (HDPE) using three different functional biomaterials through LBL modification.¹²⁵ They used PDA as an adhesive material to modify the surface of 3D-printed HDPE scaffold as the base layer, providing a platform for further LBL modification with bioactive factors. ε-Polylysine (EPL), a small antibacterial cationic peptide with a large positive charge, and fibrin, essential for vascular and endothelial tissue regeneration with a small negative charge, were used as the subsequent layers.^134–137 EPL was able to react with the amino groups of the PDA layer to form the EPL layer, and the EPL and fibrin LBL coating was successfully generated through the interaction resulting from the electrostatic absorption principle.¹³⁸ For LBL modification on titanium implants, Zhao et al found that using PDA as the base layer resulted in an interconnected network of type I collagen (COL1) on the surface, with a higher COL1 content and satisfactory layer stability compared to the group without the PDA basement.¹³⁹

Sandwich-Like Structure

Wu et al utilized a sandwich structure consisting of PDA and carboxymethyl chitosan (CCS) layers to achieve long-term stable delivery of bone morphogenetic protein BML-284 (BML).¹²⁶ The PDA layer serves as a platform for immobilizing BML via Schiff base formation and physical adsorption, as well as electrostatic and chemical interactions between the PDA and the –NH₂ of BML. The CCS layer contains carboxymethyl groups that are negatively charged and can interact electrostatically with positively charged drugs such as BML.¹⁴⁰ This allows the BML to be released from the hybrid films in a controlled manner, with its release further restricted within the scaffold for sustained delivery through the combined electrostatic and chemical interactions between BML and CCS. This approach has great potential for achieving long-term stable delivery of various bioactive factors in tissue regeneration applications.

Core-Shell Sturcture

Polypyrrole (PPy) is a typical conductive polymer. Recently, the incorporation of PPy-PDA NPs has been shown to enhance the PTT conversion capacity of scaffolds, leading to improved sterilization efficacy.¹⁴¹ Electrospun poly(l-lactide) (PLLA) nanofibers have been widely used in various tissues regeneration but limited by its poor hydrophilicity.^142–145 Therefore, Xiong et al made a core-shell structure to fix the PLLA shortcoming and add PPy functions.¹²⁸ PDA modification of PLLA fibers, when polymerized in situ, can act as an effective binder between PPy and PLLA, while also synergistically enhancing the hydrophilicity, biocompatibility, and endogenous conductivity of composite materials.

Self-Healing and Shape-Memory PDA Biomaterials

The self-repairing ability of hydrogels can help maintain the material’s integrity at the wound site, which is crucial in preventing foreign material from entering the wound and causing infection.¹⁴⁶ Moreover, self-healing hydrogels can adapt to the wound’s shape and provide a scaffold for new tissue growth.¹⁴⁷ The self-healing property of hydrogels is accomplished by reassociating catechol groups via dynamic Schiff bonds, π-π stacking, and hydrogen bonding interactions between polymer chains.¹⁴⁸ PDA is enriched with diverse functional groups, including benzene rings, catechol, and amine groups, enabling it to establish a wide range of interactions with the polymer matrix. These interactions comprise both covalent and noncovalent bonding, such as hydrogen bonds, coordination, and π–π stacking.¹⁴⁹ Certainly, the incorporation of PDA into hydrogels or polyurethane offers a valuable means of enhancing their mechanical properties. This is attributed to the intermolecular interactions facilitated by PDA, which aid in effective energy dissipation during tensile deformation. As a result, the materials exhibit improved toughness and resistance to mechanical stress. This property renders PDA a promising component for various engineering and biomedical applications, where superior mechanical performance is essential.^150,151

Rao et al successfully combined PDA and CCS to develop a self-healing wound hydrogel.¹⁴⁸ The presence of amino groups in CCS chains enables them to react with the aldehyde functional groups of other polymers, forming dynamic Schiff base bonds that contribute to the material’s self-healing ability.¹⁵² The self-healing ability of 0.4 wt% of DA-CCS hydrogels was achieved at room temperature within 2 hours, where the hydrogel was cut into two halves and rejoined automatically within this time frame.

In another study, Dai et al designed a novel shape memory polyurethane based on PDA and polycaprolactone (PCL) prepolymer, which was responsive to NIR light (Figure 6A and B).¹⁵³ PCL is a widely used synthetic polymer in biomedical applications due to its low melting temperature (around 50 °C) and excellent biocompatibility.¹⁵⁴ The phenolic hydroxyl groups in PDA NPs participated in the chain extension reaction with the isocyanate bonds of PCL to obtain higher dispersibility, which prevented any reduction in mechanical properties or conversion efficiency.¹⁵⁵ The PCL-PDA polyurethanes were softened at 46 °C and shaped into a specific form, which was then fixed in an ice water bath (Figure 6A). Upon exposure to a 46 °C water bath, the material was able to recover its original shape. This novel shape memory polyurethane could be controlled using NIR light to transfer heat and regulate temperature to control shape (Figure 6B).

Figure 6 (A) PCL–PDA 1 was wound on a round rod at 60 °C and then submerged in an ice water bath for 5 min to obtain a spiral shape. At last, the sample was placed in a 60 °C water bath, and it recovered its permanent shape.¹⁵³ (B) Digital photos of NIR light-triggered shape memory behavior of PCL–PDA 1 polyurethane in vitro and in vivo.¹⁵³ Reproduced with permission from Dai S, Yue S, Ning Z, Jiang N, Gan Z. Polydopamine Nanoparticle-Reinforced Near-Infrared Light-Triggered Shape Memory Polycaprolactone-Polydopamine Polyurethane for Biomedical Implant Applications. ACS Appl Mater Interfaces. 2022;14(12):14668–14676.¹⁵³ Copyright © 2022 American Chemical Society.

PDA Absorbs Some of the Inflammatory Factors at the Site of Injury

PDA as Cell Free DNA Scavenger in Rheumatoid Arthritis

Rheumatoid arthritis (RA) is an autoimmune disease that differs from other bone injuries such as bone fractures, bone defects, and bone tumors. Accumulating evidence suggests that cell-free DNA is a major factor in the development of RA,^156,157 making the scavenging of cell-free DNA a promising approach for treating this disease. However, the use of cationic nanoparticles for this purpose has been limited by their high cytotoxicity.¹⁵⁸ PDA has been shown to be an effective gene binding nanocarrier with low toxicity.¹⁵⁹ Chen et al have developed an injectable PDA-based nanoparticle system for scavenging cell-free DNA in joints (Figure 7A). The abundant catechol and imine groups of the NPs were first activated by 1,1’-carbonyldiimidazole and then modified with dimethylamino groups (DP-M or DP-B) with varying charge density, by reacting with amino groups of 3-dimethylamino-1-propylamine (M) or 3,3-iminobis(N,N-dimethylaminopropyl) (B), to bind negatively charged cell-free DNA. Cytotoxicity tests showed that the PDA NPs exhibited almost no cytotoxicity, and at concentrations below 100 μg/mL, they showed protective effects against LPS-induced cells by preventing inflammation. The concentration of cell-free DNA in the serum of healthy individuals was found to be only 9 μg/mL, whereas it increased sharply to 52 μg/mL in the RA model group. However, after treatment with PDA NPs, the concentration of cell-free DNA remained high (33 μg/mL), but it was almost close to normal levels in the RA+DP-B group (13 μg/mL).¹⁶⁰ This suggests that PDA-based NPs can scavenge cell-free DNA and thus have potential as a therapeutic modality for RA.

Figure 7 (A) Schematic illustration of in vivo RA therapy effect of dimethylamino group (3- dimethylamino- 1- propylamine (M) or 3, 3- iminobis (N, N- dimethylaminopropyl) (B)) modified polydopamine (DPs). The DPs were intra articular (IA) injected into the knee joint of CIA rat and strongly bound with cfDNA to lower the expression of inflammatory factors: MMP-13, TNF-α, IL-6 and IL-1β for RA therapy. Reproduced from Chen Y, Wang Y, Jiang X, et al. Dimethylamino group modified polydopamine nanoparticles with positive charges to scavenge cell-free DNA for rheumatoid arthritis therapy. Bioact Mater. 2022;18:409–420. ¹⁶⁰ Copyright © 2022 KeAi, open access. (B) Schematic illustration of PDA@MF NPs treatment for ROS-related kidney diseases.¹⁶¹ (C) Bio-distribution of PDA NPs and PDA@MF NPs was examined via in vivo imaging instruments.¹⁶¹ (D) H&E analysis of kidneys in different groups.¹⁶¹ Adapted from Zheng B, Deng G, Zheng J, et al. Self-polymerized polydopamine-based nanoparticles for acute kidney injury treatment through inhibiting oxidative damages and inflammatory. Int J Biochem Cell Biol. 2022;143:106141. ¹⁶¹ Copyright © 2022, with permission from Elsevier.

PDA as ROS Scavenger

Uncontrolled inflammatory responses triggered by pathogens can lead to excessive production of ROS, which in turn can result in chronic or non-healing wounds. Thankfully, antioxidants can effectively inhibit alveolar bone resorption by attenuating the excessive production of ROS.^162,163 Traditional natural enzymes often function as ROS scavengers, but their poor stability and potential high-dose toxicity pose significant obstacles in preventing ROS-related diseases. As an alternative, PDA has emerged as a promising antioxidant for various therapeutic applications, such as periodontal disease, skin lesions, and ischemic stroke. Its use addresses the limitations associated with traditional enzymes, making it a potential solution for ROS-related conditions.^19,164,165

Li et al design a high efficiency ROS eliminate system.¹⁶⁶ The elimination of ROS is accomplished by the catechol groups present in PDA, which are converted to quinone groups. Additionally, PDA-reduced GO facilitates electron transfer to the quinone groups, leading to the reduction of quinone groups back to catechol groups. This process enables PDA to continuously remove ROS generated by wound tissue.

Pharmacological inhibitors or siRNA targeting mTOR have been demonstrated to effectively reduce ROS formation and mitigate proinflammatory processes.¹⁶⁷ Shi et al loaded rapamycin (Rapa) which is an inhibitor of mTOR and PDA into PDA to construct mPDA@Rapa for the treatment of Spinal cord injury (SCI).¹⁶⁸ Both the mPDA group and mPDA@Rapa group exhibited significantly reduced ROS levels, which can be attributed to the ROS scavenging ability of mPDA. Additionally, in the Rapa and mPDA@Rapa treated groups, the expression of mTOR protein decreased. Consequently, the ROS level in the Rapa group also showed a slight reduction due to the inhibition of mTOR by Rapa. Therefore, PDA not only possesses strong ROS scavenging ability by itself, but also can be combined with other drugs to obtain stronger anti-ROS effect.

PDA Related Biomaterial for Internal Organ Repairment

Acute kidney injury (AKI) is a sudden episode of kidney failure or kidney damage, which triggers a series of biological events including excessive production of ROS and hypoxia.¹⁶¹ To address this, Zheng et al developed PDA NPs for scavenging excessive ROS and producing oxygen in AKI (Figure 7B). They used biocompatible manganese ferrite (MF) NPs as treatment agents to continuously generate oxygen in the inflammatory area. Although it is challenging to apply biomaterials to internal organs, PDA-related biomaterials have shown great ROS scavenging properties in acute peritonitis and acute lung injury, suggesting their potential for use in other internal organs (Figure 7C). The MF NPs were verified to be 5 nm in size and were dispersed into DA hydrochloride solution to construct PDA-encapsulated MF nanocomposites (PDA@MF). The PDA@MF NPs were monodispersed and had an average diameter of 140 nm. The researchers evaluated the kidney function of an AKI mouse model after PDA@MF NPs treatment and found that both plasma creatinine and blood urea nitrogen levels were significantly decreased compared with the control group. The pathological situation was greatly alleviated with the addition of PDA@MF NPs, suggesting PDA@MF NPs contributed to the maintaining of renal tissue integrity (Figure 7D). Additionally, PDA@MF NPs were mainly accumulated in the lung, liver, and kidney but negligible in other organs (such as the heart and spleen), suggesting the potential of PDA in the treatment of lung and liver diseases as well.¹⁶¹ These results show that PDA also has the potential to play roles in lung and liver diseases.

Conclusion and Prospect

In conclusion, PDA is a versatile material with a wide range of functions and immense potential in wound and tissue regeneration. Its diverse properties and abilities offer promising avenues for designing more sophisticated and intelligent tissue repair materials.

Powerful Bonding and Adhesion Allow for a Wide Range of PDA Applications

In recent years, PDA has been frequently utilized as an auxiliary material to complement the properties of the primary materials in tissue repair designs. Its strong bonding capabilities enable seamless integration with various types of materials without compromising their individual performance. PDA’s exceptional binding and adhesion properties make it a versatile component, facilitating its combination with a diverse range of materials in various tissue repair applications. Despite the array of materials available for tissue repair, PDA stands out for its ability to modify these materials and fulfill its role by simply integrating with them.

First and foremost, PDA can serve as a surface modifier for other non-biologically active materials, such as PEEK and metal. Through PDA modification, the surfaces of these materials can be improved, enhancing their surface properties.^169,170 Secondly, the incorporation of PDA also opens up opportunities to develop drug release systems. By utilizing PDA as a carrier or modifier, controlled drug release can be achieved, enhancing the therapeutic efficacy of wound repair materials. Thirdly, the versatility of PDA allows it to be combined with various materials, enabling the creation of multi-layered structures and the design of more intricate wound repair materials. Fourthly, materials combined with PDA demonstrate robust self-healing capabilities, making them better suited to withstand the challenges of complex wound environments. Incorporating PDA in the design of new materials holds the promise of harnessing its beneficial properties for tissue repair applications.

PDA Can Be Used for the Design of Drug-Controlled Release Systems

Silver ions are a powerful antimicrobial material, but they also have some cytotoxicity. Controlling their release is currently the key to balancing the antimicrobial activity and toxicity of silver-based materials. The combination of materials such as PDA and MXene can provide more design ideas for controlling silver ion release systems.¹⁷¹ The strategy of combining PDA and metal ion materials is also applied to the disinfection of water bodies.^172,173 The design ideas of materials in different fields may bring new inspiration to the design of wound antimicrobial materials.

The PTT capability of PDA enables the design of light-controlled drug release materials. By converting near-infrared (NIR) light energy into heat energy, PDA enhances drug release capacity and provides control over the drug release process. Moreover, PDA can be combined with temperature-responsive materials, like hot-melt materials, which melt at elevated temperatures, facilitating drug release concurrently. Additionally, PDA’s pH responsiveness enables it to control drug release in response to changes in pH levels. These versatile strategies offer promising avenues for designing intelligent and precise drug release systems for tissue repair applications.

PDA Can Be Used for in vivo Organ Repair

The application of drugs to open injuries in organs is relatively straightforward, but using repair materials on visceral tissues has posed challenges. PDA, with its potential for intravenous administration, can accumulate in organs such as the lung, liver, and kidney. Thus, PDA holds promise for addressing tissue damage in these organs. Additionally, local injection of PDA shows potential for treating neurological disorders like SCI. However, the safety of PDA for repairing visceral organ damage needs further validation. Questions regarding the degradation of PDA, potential embolism formation, and the possibility of new complications arising from its presence in the body remain to be addressed through comprehensive studies.

Prospect

It has been few decades that mussel-inspired materials come into scientists’ sight. While a few mussel-inspired materials, like mussel adhesive protein, have found their way into daily skin care and superficial clinical applications, their widespread adoption is hindered by production limitations and material complexity. Extracting MAP from natural sources or producing it through biological fermentation yields relatively low quantities, making it impractical for large-scale applications. Additionally, the intricate nature of mussel-inspired biomaterials for tissue repair and regeneration poses challenges for manufacturing and real-world clinical use. PDA, on the other hand, emerges as a promising alternative due to its ease of production and low cost. Its potential extends beyond that of natural mussel-inspired materials, making it a viable replacement in certain areas. Scientific research often explores the realm of possibilities, while medical products must prioritize practicality, production feasibility, and extensive clinical trials. With hundreds of published studies on PDA, there is ample reason to believe that with sufficient time and investment, PDA could revolutionize clinical treatments for a wide range of patients.

Abbreviations

PDA, Polydopamine; DOPA, 3,4-dihydroxy-l-phenylalanine; DA, Dopamine; NPs, Nanoparticles; PTT, Photothermal; HA, Hyaluronic acid; GO, Graphene oxide; CMCHm-PDA, Carboxymethyl chitin microspheres with PDA; BMP-2, Bone Morphogenetic Protein-2; ROS, Reactive oxygen species; PDAH, PDA with heparin; PEEK, Polyetheretherketone; TA, Tannic acid; LUT, Luteolin; NIR, Near infrared; TSLs, Thermosensitive liposomes; PCM, Phase-change material; Ag, Sliver; PDT, Photodynamic therapy; TCPP, Tetrakis(4-carboxyphenyl)porphyrin; PES, Pifithrin-μ; ZIF-8, Zeolite-based imidazole framework; LBL, Layer-by-layer; HDPE, High-density polyethylene; EPL, ε-Polylysine; COL1, Type I collagen; CCS, Carboxymethyl chitosan; BML, BML-284; PPy, Polypyrrole; PLLA, Poly(l-lactide); PCL, Polycaprolactone; RA, Rheumatoid arthritis; Rapa, Rapamycin; SCI, Spinal cord injury; AKI, Acute kidney injury; MF, Manganese ferrite.

Disclosure

The authors report no conflicts of interest in this work.

Acknowledgement

This work was supported by grants from National Natural Science Foundation of China (No. 82172206), Zhejiang Provincial Medical and Healthy Science Foundation of China (No. 2023RC183 and 2024KY110). We thank Xiaoli Hong and Chao Bi from the Core Facilities, Zhejiang University School of Medicine for their technical support.