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Review

Recent Advances in Metal-Organic Framework (MOF) Asymmetric Membranes/Composites for Biomedical Applications

by
Farrokhfar Valizadeh Harzand
1,
Seyyed Navid Mousavi Nejad
2,
Aziz Babapoor
1,
Seyyed Mojtaba Mousavi
3,*,
Seyyed Alireza Hashemi
4,
Ahmad Gholami
5,
Wei-Hung Chiang
3,*,
Maria Giovanna Buonomenna
6 and
Chin Wei Lai
7,*
1
Department of Chemical Engineering, University of Mohaghegh Ardabili, Ardabil 56199-11367, Iran
2
Department of Clinical Biochemistry, School of Medicine, Shahid Beheshti University of Medical Sciences, Tehran 15167-45811, Iran
3
Department of Chemical Engineering, National Taiwan University of Science and Technology, Taipei 106335, Taiwan
4
Nanomaterials and Polymer Nanocomposites Laboratory, School of Engineering, University of British Columbia, Kelowna, BC V1V 1V7, Canada
5
Biotechnology Research Centre, Shiraz University of Medical Sciences, Shiraz 71348-14336, Iran
6
Ordine dei Chimici e Fisici della Campania (OCF) and MIUR, 80134 Napoli, Italy
7
Nanotechnology & Catalysis Research Centre, University of Malaya, Kuala Lumpur 50603, Malaysia
*
Authors to whom correspondence should be addressed.
Symmetry 2023, 15(2), 403; https://doi.org/10.3390/sym15020403
Submission received: 25 December 2022 / Revised: 19 January 2023 / Accepted: 30 January 2023 / Published: 3 February 2023
(This article belongs to the Special Issue Asymmetric Membranes: Volume 2)

Abstract

:
Metal-organic frameworks (MOFs) are a new class of porous crystalline materials composed of metal and organic material. MOFs have fascinating properties, such as fine tunability, large specific surface area, and high porosity. MOFs are widely used for environmental protection, biosensors, regenerative medicine, medical engineering, cell therapy, catalysts, and drug delivery. Recent studies have reported various significant properties of MOFs for biomedical applications, such as drug detection and delivery. In contrast, MOFs have limitations such as low stability and low specificity in binding to the target. MOF-based membranes improve the stability and specificity of conventional MOFs by increasing the surface area and developing the possibility of MOF-ligand binding, while conjugated membranes dramatically increase the area of active functional groups. This special property makes them attractive for drug and biosensor fabrication, as both the spreading and solubility components of the porosity can be changed. Asymmetric membranes are a structure with high potential in the biomedical field, due to the different characteristics on its two surfaces, the possibility of adjusting various properties such as the size of porosity, transfer rate and selectivity, and surface properties such as hydrophilicity and hydrophobicity. MOF assisted asymmetric membranes can provide a platform with different properties and characteristics in the biomedical field. The latest version of MOF materials/membranes has several potential applications, especially in medical engineering, cell therapy, drug delivery, and regenerative medicine, which will be discussed in this review, along with their advantages, disadvantages, and challenges.

1. Introduction

All types of cancer and bacterial infections are serious threats to global health. According to reports until 2018, nearly 18 million people die annually due to cancer and bacterial infection [1]. The development of nanotechnology has experienced exponential growth in recent years and has led to entry into interdisciplinary branches of various sciences, such as biomedicine, bio-nano-technology, nanobiotechnology, and nanomedicine. Nanostructures are designed with acceptable biocompatibility and efficiency. This class of materials has attracted researchers and scientists to explore nanostructures as innovative and efficient nanoplatforms for anticancer drug/gene delivery and nanocarriers, as well as promising devices for various bioassay and diagnostic applications (especially for therapy/diagnosis of cancer) to be used [2,3,4]. Metal-organic frameworks (MOFs) are organic-inorganic hybrid materials that have been rapidly developed for various applications such as clean energy, storage of gases such as hydrogen and methane, catalytic processes, and drug delivery platforms [3,5]. MOFs are composed of organic ligands as bases and clusters of suitable metal ions as nodes. MOFs with different properties can be obtained by adjusting the almost infinite combination of metal nodes and organic ligands. The wide range in the choice of ingredients of MOFs makes it possible to adjust the different sizes of their pores from micropores to mesopores or macropores. Like other nanomaterials, one of the main characteristics of MOFs is their high surface area. In addition, by modifying the surface of MOFs, their performance increases. These properties make MOFs suitable candidates for biomedical applications such as drug delivery and magnetic resonance imaging (MRI) [6,7,8]. The high specific surface area and large pore size of MOFs facilitate the encapsulation of drugs with drug loads, and besides, the structural and functional flexibility of MOFs allows them to be adapted to shape size, and function [9,10]. Modifying the surface of MOFs with different chemical groups makes it possible to carry various drugs and can simultaneously act as MRI contrast agents. MOFs perform both diagnosis and treatment goals at the same time. According to the mentioned contents, MOFs offer new advantages in the field of biomedicine, including the fields of monitoring, diagnosis, and treatment [11,12]. The MOFs show greater than 90% porosity at physiological conditions, as well as a high degree of stability, whereas the MOFs have a high potential for biomolecular in situ functionalization with metals or organic molecules. Additionally, flexible membranes enable the design of bioactive substrates effectively. In addition, by using different metal groups and multiple organic molecules, structures with a tunable pore size (typically 0.4–6 nm) and specific surface area (500–4500 m2/g) of MOFs can be obtained [13,14,15]. ZIF-8 is one of the types of MOFs. In 2020 Ejeian, and colleagues [16,17], used polypropylene, polyurea, and ZIF-8 (PP/PDA/ZIF-8) as a selective thin film to support the essential activities of cells using dental pulp stem cells (DPSCs). The results of this study indicated that ZIF-8 nanostructures offer new opportunities for the surface functionalization of polypropylene membranes as nanomedicines with significant therapeutic benefits. The researchers tested the primary cell attachment, proliferation rate, and multilineage differentiation of cells on this platform. guided bone regeneration (GBR). In the continuation of this review, some applications of MOFs in the biomedical field and recent developments in this field have been discussed.

2. MOF Synthesis

In the still relatively young field of MOF synthesis, the chemistry of the solid state and zeolites have been recognized as forming the basis of this field [18]. As coordination polymers are formed by connecting metal ions with organic ligands as linkers, coordination chemistry has investigated compounds labeled as coordination polymers for years. Even though Prussian blue compounds and Hofmann clathrates showed reversible sorption properties, interest in porous coordination polymers emerged much later [19]. A layered co-trimester that demonstrated reversible sorption properties was first called MOF by Yaghi et al. around 1995 [20]. HKUST-1 and MOF-5, which were synthesized in 1999, became among the most studied MOFs in the following years [21,22].
Hydrothermal or solvothermal synthesis routines have traditionally been used to prepare MOFs on small scales through electrical heating, which can take several hours or days to complete. To prepare high-quality single crystals suitable for structural analysis in dilute liquid phase conditions, efforts were primarily focused on preparing high-quality single crystals. Later, microwave-assisted synthesis, sonochemical synthesis, electrochemical synthesis, and mechanochemical synthesis methods were used to shorten the synthesis time. Several studies were conducted on the scale-up of MOF synthesis conditions to obtain high yields of solid products for industrial applications; some of these studies also investigated the optimization of MOF synthesis conditions to achieve high yields [23,24].
A variety of elements, including zinc, copper, chromium, aluminum, and zirconium, are commonly used to form frameworks containing bivalent or trivalent aromatic carboxylic acids or aromatics that contain N [25].
According to Table 1, the MOF structures were synthesized using the following methods and the key findings of these studies are presented.

3. MOF Membranes

MOF membranes are widely employed in the food industry, gas separation, drug delivery, and cancer therapy. various protocols have been applied for the design of MOF membranes. Thereby produced various types of MOF membranes with unique properties such as amorphous and low-crystalline MOF membranes, stimuli-responsive MOF membranes, ultra-thin MOF membranes, oriented MOF membranes, and pilot scale-up of MOF membranes. MOFs are gaining attention since they have regular nanopores and are highly selective in gas separation membranes. MOFs can be integrated into membrane materials in two different ways. In one way, MOF particles can be blended with a polymer matrix to form mixed matrix membranes (MMMs), while in another, dense MOF films can be grown on porous substrates. It is important in both cases to ensure the compatibility of MOFs with polymer matrixes and substrates at the interface [36,37].

3.1. Asymmetric Membranes

Asymmetric membranes were first manufactured out of cellulose acetate in the late 1950s by Loeb and Sourirajan and were used in reverse osmosis [38,39]. Since then, asymmetric membranes have been used in various fields of separation processes such as ultrafiltration, microfiltration, dialysis, gas separation, and wastewater treatment.
In addition to the mentioned applications, asymmetric membranes have also been used as wound dressings to treat skin injuries [40]. The first efforts of scientists in the field of regenerative medicine began with the development of occlusive wound dressings. Failure to absorb exudate in occlusive wound dressings such as Opsite®, Omiderm®, or Spandre® results in delayed healing in resuscitation medicine. Despite their effectiveness, these dressings did not prevent the penetration of microorganisms and dehydration of wounds. Researchers later concluded that a combination of both systems (occlusive as well as macroporous) would be ideal, since the bacteria could not penetrate both structures and exudate could be absorbed and gas exchanged simultaneously [41].
The first wound dressings used in regenerative medicine were impermeable and prevented exudate from being absorbed through the wound, causing the healing process to be delayed. Eventually, microporous constructs (e.g., Coldex®, Surfasoft®) were developed that allowed wound exudate to be better drained. Although these dressings prevented microbial penetration and wound dehydration, they were incapable of preventing penetration of microorganisms. The researchers concluded that combining both systems (occlusive and macroporous structures) would be the best option since it would prevent bacteria from entering while allowing exudate to be absorbed and gaseous exchange to occur. In order to improve blood flow, dressings were developed with a macroporous sublayer or a hydrogel linked to a dense or hydrophobic microporous top layer. These types of dressings include Lyofoam®, Epigard®, and Duoderm®. Although they were effective, they also had some disadvantages. For example, they had limited drainage capacity, exudate accumulation, and frequent replacements, which meant more wound infections. In the 1990s, Hinrichs et al., following Loeb and Sourirajan’s work, developed for the first time an asymmetric polyurethane membrane (PU) [39]. Based on in vitro bacterial testing using P. aeruginosa, the asymmetric PU membrane exhibited an interconnected microporous top layer (pore size 0.7 m), which prevented wound dehydration and bacterial penetration. The sublayer also possesses a sponge-like structure that contains micropores (pore size: ten micrometers) and macropores (pore size: 50–100 μm) that enhance tissue regeneration and absorption capacities. Moreover, both layers acted as drug release reservoirs, allowing controlled gaseous exchange in a way that surpasses the limitations of Lyofoam®, Epigard®, and Duoderm® described in the previous paragraph. The use of chitosan (CS) membranes in asymmetrical forms has also been demonstrated. Due to its intrinsic properties, such as antimicrobial activity, biocompatibility, biodegradability and hemostatic properties, CS, a natural polymer derived from deacetylation of chitin, has been extensively used for wound dressing production. A platelet recognizes the CS surface and initiates coagulation in a matter of seconds by attracting the negatively charged residues on red blood cell membranes with its protonated amine groups, leading to a strong agglutination, thrombin production, and fibrin mesh synthesis within the microenvironment created by this polysaccharide [39,42]. Considering the various properties of MOFs, the use of these materials with asymmetric membranes have shown a high potential in separating different materials, especially gases, with the help of membranes [43]. However, the use of these two-dimensional materials and asymmetric membranes in the biomedical field, especially in the field of wound dressing, still has room for improvement.

3.2. Electrospinning

Normally, polymer melts or solutions are electrospun by either pressing them through a needle, coating them on a wire, rotating a cylinder, etc., or introducing them into a strong electric field. Generally, a strong electric field is used to melt or introduce the polymer solution [44,45]. Its higher production performance can be attributed to needleless technology, which can usually be scaled up from the laboratory to the industrial level. A biotechnology or medical application often uses nanofiber mats of this type [44,46]. Nanofiber mats are typically produced with incidentally oriented nanofibers using a static collector plate. Biotechnology and biomedicine often use these kinds of nanofiber mats. Nanofiber mats aligned in a particular direction are beneficial for cell growth [44,47,48]. A rapidly rotating collector and blades can be used to prepare them. A conductive substrate with grounding can be used in orienting nanofiber mats, including magnetic nanofibers, allowing fiber alignment. Dielectric coatings can also be applied to parts of the substrate to modify the electric field during electrospinning. In their study, Nguyen et al. study a cylinder collector shielded by two dielectric films that rotate at a high speed. A thin gap between these two cylinders amplifies the electronic field, which controls fiber alignment and position through diverting airflow due to cylinder rotation [49,50]. It is possible, as well, to create one or more layers with different mechanical properties by partially growing nanofiber layers on conductive structures and partly consolidating them. Different polymers and polymer blends can be used for electrospinning nanofiber mats. An electrospinning process can be carried out using aqueous solutions for some polymers. This method is simple and environmentally friendly. To use nanofiber mats in humid environments, a crosslinking step is required. The majority of water-resistant polymers must be electrospun using toxic or corrosive solvents, as opposed to electrospinning with low-toxic solvents such as dimethyl sulfoxide (DMSO). Electrospinning often uses polyacrylonitrile (PAN) due to its spinnability from DMSO. Another reason PAN is often electrospun is that it can be used as a precursor for carbon nanofibers. There is a wide range of materials that can be spun and co-spun into nanofiber mats, making them attractive for applications in many fields, including biotechnology and biomedicine. It is, however, for this discussion that we will be focusing on materials that are suitable for tissue engineering as well as other types of cell growth that apply to this discussion [51,52]. It is highly desirable for biomedical and biotechnological applications due to its low toxic nature and ability to be electrospun from dimethyl sulfoxide (DMSO). Its use for tissue engineering is less frequent, however than that of other polymers. Scientists found that electrospun nanofiber mats with low Fe-MOF levels were highly porous, had an appropriate fiber diameter, and were chemically stable [53,54]. Fe-MOF scaffolds showed better attachment, proliferation, and spreading of human umbilical vein endothelial cells (HUVEC) than pure PAN nanofiber mats, as shown in Figure 1. It was possible to exclude cytotoxic effects for Fe-MOF in low quantities; in vivo implantation did not result in any inflammatory response. The optimal concentration of Fe-MOF is the concentration that has a balance between scaffold degradation and an increase in cytotoxicity. A negative effect of Fe-MOF is that it negatively impacts cell activity, but it positively impacts pH values at the biointerface [54,55,56].

4. Biomedical Applications

In coordination chemistry, open framework materials such as zeolites have been crucial since their discovery. In a wide range of applications, including catalysis, ion exchange, and gas separation, porous solids have been developed with targeted topology, architecture, crystallinity, and porosity [6,57,58]. Crystallized MOFs are open framework materials composed of metal nodes and organic ligands. The large surface area and well-defined pore distribution of MOFs have made them a valuable material for a wide range of applications since they were discovered at the end of the 1990s [59]. As well as tuning their chemical functionality during synthesis, they are capable of modifying their physical properties [60,61]. There has however been considerable effort made to improve the resistance of MOFs to degradation under different/harsh chemical conditions because of their chemical, thermal, and mechanical stability [62,63].

4.1. Biosensors

Biosensors allow for molecular interactions to be detected and converted into an electrical signal that can be detected [64,65]. An electrochemical, optical, piezoelectric, acoustic, or calorimetric biosensor involves the combination of biological elements, such as enzymes, DNA, RNA, metabolites, cells, and oligonucleotides [66,67,68]. An important characteristic of biosensors is their ability to convert biochemical interactions into electric signals that can be measured and quantified. Further, it is imperative that the minute changes that occur during biological processes, such as the interaction of various biomolecules, are analyzed efficiently. Therefore, biosensors are being developed to diagnose diseases, ensure food quality, and monitor the environment. As far as medical applications are concerned, biosensors are designed to detect tumors, bacteria, toxins, and biomarkers early in the onset of various disorders. Several factors have contributed to the popularity of biological sensors, including their low manufacturing costs, rapid response time, portability, high specificity, and high sensitivity, along with their ability to determine minute changes in biological elements [64,69,70,71]. Detecting biomolecules intracellularly presents a challenging task since non-specific targets can bind to biosensors [70,72]. To overcome this defect, structured materials from the Institute Lavoisier (MIL) family of metal-organic frameworks (MOF) are being utilized. In particular, a combination of MILs and fluorescence was used to detect intracellular ATP molecules. An indicator of active metabolism is the concentration of ATPs within the cell, which is the cellular energy currency [70,73]. As ATP aptamers (Apt-F) labeled with carboxyfluorescein (FAM) were linked to MIL-100, and thus quenched by PET (photoinduced electron transfer), Apt-F is bound to the ATP molecules at this point, thereby restoring FAM fluorescence. Using a chemiluminescent sensor, microfluidics-based nanosensors have been developed for identifying CD4 cells in the presence of HIV. Based on previous research, CD4+ and CD8+ T-helper cells are thought to play a role in wound healing, and so immunosensors can be used to monitor wound healing [64,74,75]. Due to the difficulty of finding water-soluble photosensitizer molecules that can bind selectively to tumor tissues that have a wide range of characteristics and are water-soluble (for high cell uptake), nanoscale agents are generally used for delivering photosensitizer molecules (molecules that destruct tumors upon exposure to light) [64,71]. With their high porosity, large surface area, and high tunability, MOFs can be used as nanocarriers for the treatment of sick tissue. The size, stability, half-life, and biocompatibility of these nano-carriers must also be monitored to increase their specificity to tumor tissue [76,77].

4.2. Drug Delivery

It has been proven that drug delivery systems (DDSs) consist of a carrier and a drug. Conventional DDSs such as tablets, capsules, and granules have several limitations and disadvantages such as high doses needed, poor bioavailability issues, and side effects. Due to various limitations of conventional DDSs, new DDSs have been created and designed in the last decade. Recently, numerous DDSs have been developed to reduce side effects and increase therapeutic efficacy. Therefore, inorganic materials such as carbon nanotubes, graphene, magnetic nanoparticles (NPs) of iron oxide, and gold nanoparticles were used. MOF membranes are a fascinating and versatile class of NPs, assembled from metal ions/clusters and organic linkers. MOF membranes have various properties, such as high porosity and surface area and special chemical and thermal stability. They have been applied in diverse applications, such as gas storage, photochemistry, catalysis, separation processes, adsorption properties, diagnostic, and antimicrobial properties, and delivery of a large variety of active drugs, biological gases, and cosmetics. Due to these properties, MOF membranes have become a good candidate for therapeutic and medicinal targets. The properties, such as low side effects, stimulus-based delivery systems, and multiple drugs loaded properties, have popularized the use of MOFs in drug delivery in the last decade. MOF membranes have been synthesized by diverse methods such as solvothermal, sonochemical, mechanochemical, and electrochemical. Drug release is controlled by MOFs, which have a high loading capacity, and targeting capabilities thanks to their high specific surface area, adjustable structure, modifications, and biodegradability [78]. Their physicochemical properties change as a result of being absorbed by proteins and cellular components [79,80]. This makes it extremely problematic for nanomaterials to have low therapeutic efficacy, poor targeting, and adverse side effects, which are all the result of their nano size. It is still possible to modify biomaterials (PEG, polymers, liposomes, hyaluronic acid, proteins, peptides, etc.) with MOF surfaces to some extent, despite MOFs’ properties of biocompatibility, active/passive targeting, and long circulation. However, there are still some limitations, such as easy degradation, immune recognition, and low targeting efficiency [81,82,83,84,85]. Moreover, the immune system can easily recognize and eliminate synthetic composites as foreign materials. Hence, most synthetic MOF carriers have a short half-life, which makes it difficult for them to accumulate in diseased parts of the body [86,87].The ideal drug carrier should therefore be biocompatible, stable, and able to target drugs. Physiochemically and biologically, biomimetic nanomaterials are derived from cell membranes [88,89,90]. Thus, they can avoid detection and elimination by the immune system as well as perform functions such as long circulation, targeted delivery, and controlled release. To achieve bionic camouflage, cell membrane biomimetic technology entraps MOFs and transfers their natural properties to the surface of MOFs using cell membrane biomimetic technology. Multifunctional MOF carriers can be designed easily using this method [91,92]. Since cell membrane-cloaked MOFs have similar properties to membrane-extracted source cells, they are capable of long circulation and disease-related targeting. Nano-carriers are currently made from various plasma membranes and cancer cell membranes, including those from blood-circulating cells [93,94]. The MOF platform has already been used to modify red blood cells (RBCs), platelets, neutrophils, macrophages, dendritic cells, and various cancer cell membranes to achieve biological camouflage [95,96,97,98]. The combination of enhanced bio-functions with improved drug delivery properties can be exhibited in a biomimetic MOF carrier. Considering the mentioned advantages of MOFs, the synergy of these properties with the capabilities that membranes bring can be considered a promising option in the field of controlled drug delivery [99]. Researchers are investigating porous polymers for applications apart from commercial applications, such as in catalysis and photo energy conversion [46,100]. For porous polymeric membranes, the most commercial potential may be found in the area of biomedicine, particularly in drug delivery, tissue engineering, bio-separation, and hemodialysis. Biodegradability and easy dissolution in certain solvents make these materials ideal for biomedical applications [85,101,102]. Biological scaffolds fabricated in vivo from membranes require controlled biodegradability, for example, for tissue engineering [103,104]. The development of porous polymeric membranes with diverse designs was enabled by selective solubility in polymer fabrication techniques such as electrospinning or block copolymer self-assembly [105]. The second half of this review discusses the use of porous polymeric membranes in biomedical applications. Detailed discussions of membrane properties, and features, including pore diameter ranges, porosity, and mechanical strength, will guide drug delivery techniques, including tissue engineering, biosensing, and bio-separation [87,106].

4.2.1. Biomaterial Types

Tissue engineering uses synthetic biodegradable polymers and acellular tissue matrixes such as decellularized tissues and organs [107,108]. These include natural polymers (such as collagen and alginate), acellular tissue matrixes, and synthetic biodegradable polymers (such as poly (glycolic acid) (PGA), poly (lactic acid) (PLA), and their copolymers) [109,110]. A biochemical, biomechanical, and biological evaluation of these biomaterials has been conducted. There are several differences between natural polymers and synthetic polymers, including their mechanical strength, degradation rate, and reproducible microstructures [46,111]. By electrospinning, nanofibers with unique properties such as high porosity, high permeability, and large surface area can be produced from natural and synthetic polymers. According to previous studies, a composite made of polycaprolactone (PCL) and collagen combines the excellent mechanical properties of PCL with excellent biocompatibility of collagen, making the composite a tissue engineering substrate for nerves, skin, bones, vascular scaffolds, etc. As a result, the electrospinning of PCL/Collagen can serve as an effective tissue-engineered substrate [112,113]. Since 2D nanomaterials possess unique physical, electronic, and chemical characteristics, they tend to possess remarkable properties compared to 1D and 3D nanomaterials [114]. In addition to having outstanding physical and chemical properties, 2D nanomaterials are also very biocompatible and biodegradable, which means they can be used in tissue or organ construction by combining them with cell biology [115,116]. Furthermore, 2D nanomaterials have high aspect ratios (surface area to volume ratios), which makes them suitable for use in drug delivery systems, as they can encapsulate a large number of molecules and provide superior control over the release of those molecules [117]. A variety of methods can be used to prepare MOFs, including solvochemical, electrochemical, mechanochemical, and sonochemical methods [23,77,118]. MOFs have proved a promising platform for biomedical applications due to their unique structure, large surface area, tunable pore sizes, and biodegradability. Rather than bridging metal ions with organic ligands, MOFs consist of organic bonds [119,120]. A polymer fibrous mat can have increased porosity by adding MOFs as high-porosity compounds. There are many composites of these porous materials reported that consist of fibers or monoliths of MOFs embedded in a polymer matrix [121,122].

4.2.2. Osmotic and Diffusion-Controlled Membranes

Osmotic-Controlled Membranes

A porous polymeric membrane diffuses drug molecules through its pores. The properties of the membrane are adjusted to control the permeation and release of drug molecules. As far as membrane systems go, there are two main types: (1) membrane systems controlled by osmosis, and (2) membrane systems controlled by diffusion [123,124]. A polymer membrane reservoir is usually used for osmotic systems, which are capable of permeating water but not drugs. This approach involves pore-forming agents being added to the membranes to create pores in situ. Meanwhile, diffusion-controlled membranes transport drugs across the membrane via drug diffusion, swelling of polymers, and degradation of the polymers [125,126]. Porous polymeric membranes are critical for the delivery of drugs because they must remain chemically and mechanically stable till the drug cargo reaches the target point, they must be uniform in size to control drug permeability and they should be easily adjustable to fit the drug’s size. Block copolymer self-assembly methods have gained popularity for drug delivery applications due to their ability to control pore sizes in the nanometer range and low fabrication costs [126,127,128].

Diffusion-Controlled Membranes

Compared to intravenous and oral drug delivery methods, transdermal drug delivery generally offers several advantages. In contrast to intravenous and oral DDS that require the internalization of membranes, the membranes do not need to be internalized in the body, thereby removing many barriers, such as controlled drug release or discomfort from needles [129,130,131]. It can be achieved by either injecting the drugs directly into the stratum corneum (SC) or by injecting them directly into the hair follicles and sweat ducts. To prevent drugs from leaking out of the transdermal drug delivery membrane, a drug impermeable layer is placed on top of it. In the case of porous polymer matrixes, an adhesive layer is used to attach the polymer matrix to the skin, followed by a drug reservoir and porous membrane to control drug release [132,133]. It has been demonstrated that a wide range of polymers can be used to produce transdermal drug delivery membranes, including gelatin, semi-synthetic polymers like hydroxypropyl cellulose, nitrocellulose, or cellulose, as well as synthetic polymers such as polysiloxane, polyisoprene, polyester, polyurethane, polyethylene vinyl acetate, polyacrylamide, and PVA [134,135]. Using a low current, the charged drug molecules pass through the body safely without causing physiological damage. Iontophoresis is a commonly used technique for this system that has been widely studied. Artificial membranes made of biocompatible materials are the main component of almost all iontophoresis patches. A significant improvement in drug penetration is possible due to active transport because: (1) without releasing the drug into the bloodstream, the superficial distribution of the drugs can be controlled; and (2) rather than releasing drugs into the bloodstream, the superficial distribution of the drugs can be controlled. The versatility of MOFs, their porosity, their large surface areas, and their high drug uptake have made them popular as DDSs in recent years [134,136]. The bioactive molecules can be incorporated into MOF materials in different ways. A one-pot synthesis and loading method takes advantage of the coordinative properties of the bioactive molecule by soaking the MOF system in a saturated solution of the bioactive molecule. The limitations of these methods are related to poor solubility of the bioactive molecules, competition with solvent molecules, or the absence of coordinative properties of the molecules. Mechanochemical methods are an alternative strategy. An environmentally friendly method for synthesizing MOFs and immobilizing catalysts has been reported based on mechanochemical synthesis [137,138].

4.3. MOFs for Cardio-Vascular Implants

The prevalence of coronary artery disease (CAD) in industrialized societies is approximately 4%. The traditional treatment for artery occlusions is the administration of anti-thrombotic medications and small molecular weight nitric oxide donors [139]. The artery may also be blocked permanently by implanting a drug-eluting stent. The use of copper-based MOFs in antithrombotic coatings for cardio-vascular implants has recently become more prevalent. Using Cu-BTC as a catalyst, it has been established that blood-borne s-nitroso-cysteine can be converted into cysteine and nitric oxide in vitro [140,141]. S-Ntirosoglutathione can also be catalyzed by more complex Cu-MOFs. MOF/polymer composite materials show promise as lead materials for novel implants due to their nitric oxide release properties. In addition to these preliminary studies, Cu-BTC was directly grown on stent surfaces and demonstrated acceptable hemocompatibility in vitro. The MIL-101 (Fe) polycaprolactone composite, which was evaluated as an effective non-copper-based MOF for cardiovascular implants, used the MOF as mechanical reinforcement, a sustained drug release vehicle, as well as an MRI contrast agent. The interactions between MOFs and cardiomyocytes are also poorly studied [140,142]. A coating of Cu-BTC combined with polydopamine demonstrated effective surface modification of cardiovascular stents in vivo. The reduction of protein absorption, thrombus formation, platelet adhesion, and increased vasodilation, especially with nitric oxide donors that require catalytic degradation, resulted in a significant reduction in protein absorption, thrombus formation, and platelet adhesion (Figure 2). Other studies have reported that 3-(1H-tetrazole-5-yl) isophthalic acid-based MOFs reduced sympathetic excitability and prevented arrhythmia. In the future, MOFs will need to be compared to clinically used materials to determine their effectiveness and safety [120,140,143].

4.3.1. Tissue Engineering

Despite donor availability, the need for organ and tissue transplantation is still considered one of the biggest challenges in the medical field [144,145]. Tissue engineering scaffolds are materials that, by mimicking the extracellular matrix environment (ECM), enable connection to the cells of living tissues and can be implanted in the tissues of living organisms [146,147]. Tissue engineering scaffolds must have characteristics such as biocompatibility and high mechanical properties. On the other hand, the scaffold should have a suitable biodegradability speed for optimal tissue regeneration and match the new tissue regeneration speed [148,149,150,151]. The goal of regenerative medicine is to restore and maintain the normal function of injured or diseased tissues through the use of biological substitutes that mimic native tissues’ anatomical and functional characteristics. Engineering, cell biology, and materials science principles are used in this approach [152,153]. Today, tissue engineering is largely based on cell-based approaches and scaffold-based approaches [154,155]. Traditionally, tissues are engineered using natural and synthetic scaffold materials. For proper direction and orientation of new tissue in growth, scaffold-based tissue engineering relies more on the body’s natural ability to regenerate [53,156,157]. By mechanically and chemically removing cellular components from tissues, collagen-based tissue matrices can be prepared by constructing artificial microenvironments from natural or synthetic materials [158,159]. During cell ingrowth, extracellular matrix proteins replace scaffold materials that slowly degrade following implantation [160,161]. The field of tissue engineering, despite its challenges and versatility, has established itself as a very important discipline that combines alternative materials as replacements for damaged tissue and stimulates natural regeneration [155]. Modern science has made tissue engineering a dominant technique for overcoming transplantation limitations, graft rejections, and complexities in restoring function [162,163]. In addition to nanotechnology and biosensors, tissue engineering has expanded into the design of organs on chips, clinical trials on chips, microfluidics, genetic manipulation, and more. Deciphering etiologies and repairing damaged tissues is possible using this technique [164,165]. With the growing clinical need to repair critical-sized bony defects, guided bone biomaterials have been developed for bone tissue engineering [54]. A range of treatment approaches can be used to achieve bone regeneration, including guided bone regeneration (GBR), especially in the maxillofacial region [166,167]. An osseous injury cannot be penetrated by rapidly growing fibroblasts because of a barrier between gingival connective tissue and alveolar bone tissue. Osteoblasts can selectively repopulate bone defects during healing by maintaining a secluded space during this process [16,168]. There are two main types of GBR membranes: non-resorbable and resorbable materials [16,169]. Collagen (Col) membranes are advantageous for biomedical applications since they are biocompatible and biodegradable, eliminating the need for a second surgery. Col membranes, however, exhibit unsatisfactory mechanical properties and rapidly degrade, making them unsuitable for medical applications [170,171]. A MOF has the potential to make a promising biomedical platform because of its unusual pore structure, large surface area, and ability to be functionalized in a variety of ways [172,173,174]. The solution to designing bioactive substrates is to immobilize enzyme MOFs onto porous and flexible membranes. A MOF is also suitable for combining short peptides, antibodies, and nucleic acids. MOF layers have therefore been successfully used to support cellular behavior in vitro as well as in vivo [140,173]. Multifunctional MOF-based biomaterials are being designed and synthesized at an accelerated pace. Due to its excellent chemical and thermal stability, pH sensitivity, and negligible cytotoxicity, zeolitic imidazolate framework-8 (ZIF-8) is an ideal candidate for use in bone regeneration processes [172] (Figure 3).

4.3.2. Bone Adhesives

Bone adhesives with properties such as biocompatibility and prevention of shape changes in drugs used in the reconstruction of bone defects play an important role in bone graft repair surgery [175]. A multifunctional hydrogel containing catechol and chitosan modified with ZIF-8 nanoparticles (CA-CS/Z) was produced by Y. Liu et al. to stabilize graft environment, accelerate bone regeneration, promote osteogenic differentiation, and expand blood supply [176]. By chemically converting catechol and ZIF-8, they developed hydrogels with excellent wet adhesion. An analyses of the characterization data demonstrated that CA-CS/Z hydrogels were synthesized successfully, displaying reliable mechanical strength, excellent rheological properties, and excellent adhesion for clinical application. In rat bone marrow mesenchymal stem cells (rBMSCs), their superior biocompatibility allows them to provide blood supply through paracrine production of vascular endothelial growth factor (VEGF). Furthermore, ZIF-8 nanoparticles released from the hydrogels could enhance osteogenic differentiation of rBMSCs by up-regulating the secretion and production of collagen 1, osteocalcin, and alkaline phosphatase. Additionally, CA-CS/Z had antibacterial properties. CA-CS/Z also demonstrated an important effect on vascularized osteogenesis by stabilizing bone graft materials and thereby accelerating bone regeneration when applied to wound areas [175,176].

4.4. Cancer Therapy

Different synthetic methods have been used to prepare MOFs for a variety of uses, including catalysis, separations, sensing, drug delivery, optics, and many biomedical applications. Annually, millions of people die from cancer, one of the most serious threats to human health [177,178]. The most common method of treatment is chemotherapy. In addition to undesirable side effects, poor pharmacokinetics, and poor biodistribution, therapeutic drugs cannot be administered directly to patients. To decrease side effects and enhance therapeutic efficacy, research efforts have focused on controllable drug delivery vehicles [179]. Over the past few decades, various nanocarriers have been developed, including organic micelles, liposomes, and dendrimers, as well as inorganic mesoporous silica and quantum dots. These carriers, however, do have limitations in bio application, such as a low loading capability of liposomes, micelles, or dendrimers, and undesirable toxicity and degradation properties of inorganic materials. The following basic requirements must be met in a drug-loading system: a large loading capacity is important for intravenous drug administration; carriers must be nanoscale to allow intravenous drug administration; carriers must also be biocompatible, i.e., not toxic, and easily degraded by the body [179,180]. It is also possible to control the release of drugs from a vehicle loaded with drugs. Therefore, controlled drug release systems have been extensively investigated in cancer chemotherapy. A multimodal treatment system is also being developed to meet the ever-growing demand for effective therapeutic interventions [181]. Janus nanocomposites made of Au nanorods (NRs) and ZIF-8 were developed by Han and colleagues for CT imaging and synergistic chemo-photothermal treatment of BALB/c mice bearing the H22 gene (see Figure 4) [182,183]. MOFs have the following obvious advantages over traditional drug carriers, as discussed above: with a variety of morphologies, compositions, sizes, and chemical properties, MOFs have a variety of multi-functionalities and stimuli-responsive drug release mechanisms. In addition, MOF-based materials retain their desirable physicochemical characteristics after modification without significantly altering their controlled size, shape, or uniformity. The properties described above make MOFs beneficial as delivery systems for drugs, clinical tumor therapies, and other diseases [184]. Table 2 summarizes a few of the most important applications of MOF composites in biomedical fields.

5. Challenges

During the past decade, membrane surface engineering has become increasingly popular due to the use of mussel-inspired surface chemistry. The use of membranes in different processes and different membrane preparations have been extensively investigated and applied, but there are still several key challenges to be overcome in this field, which represent interesting future research opportunities. A common property of such coatings should be considered more closely. In membrane fabrication, mussel-inspired coatings may play a more diverse role due to their hydrophilicity. Multilayer composite membranes made from thin film composite membranes have shown excellent interfacial compatibility when they contain mussel-inspired interlayers. In this review, the latest applications of MOFs and membranes based on them in the biomedical field have been discussed. Because of their adaptability, excellent surface areas, high porosity, crystallinity, great loading capacities, improved thermal/chemical stability, and variable affinity, MOFs are most commonly used in biomedicine as multifunctional supports. Biomedical applications for MOF-based composites still face critical challenges despite significant advances in laboratory research. As a first step, toxicity issues regarding MOFs need to be addressed before or during clinical trials. The variety of MOF structures, species, sizes, and stabilities, along with the complex environment organisms live in, make MOFs toxic not only because of their composition, morphology, size, or stability, but also because of the environments they live in. As a result, a comprehensive assessment of MOF toxicity is necessary. To date, considerable research has been conducted on the toxicity of MOF scaffolds, with most experiments focusing on short-term in vivo or acute toxicity. However, the most important aspect of MOF scaffolds for biomedical applications is long-term toxicity, which has rarely been addressed. In vivo or acute toxicity studies of MOFs have been conducted in many excellent studies so far. Despite the critical aspect of long-term toxicity that must be considered if MOF scaffolds are to be outstanding biomedical candidates, few studies have been conducted to date. To evaluate MOFs’ toxicity comprehensively, extensive in vivo studies and long-term tissue accumulation monitoring is urgently needed. A ligand with strong biocompatibility and metal ion nodes with high biocompatibility can also be used to create functional MOFs while avoiding toxicity associated with MOFs. Considering the potential properties of MOFs, their use in the construction of MOF-based membranes has become a promising option in the biomedical field. Because the synergism of the properties of MOFs with the characteristics of membranes that can be produced from various materials such as polymers can facilitate the controlled and stable release of drugs. In addition, the use of membranes based on tissue engineering has paved the way for many treatments. In recent years, advances in nanotechnology and the understanding of biosensors have allowed tissue engineering to be applied to designing organs on chips, conducting clinical trials on chips, using microfluidics, manipulating genetics, and so on, for the puerto decodend repairing drepairssues. Considering the variety of materials that can be used with MOFs, the field of application of these materials in biomedical field is even wider, while among these materials, there are plenty of materials that solve problems such as the low biocompatibility of MOFs. However, due to the novelty of this aspect of 2D materials, there are many undiscovered applications that need to be investigated.

6. Perspective and Conclusions

In this review, the latest applications of MOFs and membranes based on them in the biomedical field have been discussed. Because of their adaptability, excellent surface areas, high porosity, crystallinity, great loading capacities, improved thermal/chemical stability, and variable affinity, MOFs are most commonly used in biomedicine as multifunctional supports. Biomedical applications for MOF-based composites still face critical challenges despite significant advances in laboratory research. As a first step, toxicity issues regarding MOFs need to be addressed before or during clinical trials. The variety of MOF structures, species, sizes, and stabilities, along with the complex environment organisms live in, make MOFs toxic not only because of their composition, morphology, size, or stability, but also because of the environments they live in. As a result, a comprehensive assessment of MOF toxicity is necessary. To date, considerable research has been conducted on the toxicity of MOF scaffolds, with most experiments focusing on short-term in vivo or acute toxicity. However, the most important aspect of MOF scaffolds for biomedical applications is long-term toxicity, which has rarely been addressed. In vivo or acute toxicity studies of MOFs have been conducted in many excellent studies so far. Despite the critical aspect of long-term toxicity that must be considered if MOF scaffolds are to be outstanding biomedical candidates, few studies have been conducted to date. To evaluate MOFs’ toxicity comprehensively, extensive in vivo studies and long-term tissue accumulation monitoring is urgently needed. A ligand with strong biocompatibility and metal ion nodes with high biocompatibility can also be used to create functional MOFs while avoiding toxicity associated with MOFs. Considering the potential properties of MOFs, their use in the construction of MOF-based membranes has become a promising option in the biomedical field. Because the synergism of the properties of MOFs with the characteristics of membranes that can be produced from various materials such as polymers can facilitate the controlled and stable release of drugs. In addition, the use of membranes based on tissue engineering has paved the way for many treatments. In recent years, advances in nanotechnology and the understanding of biosensors have allowed tissue engineering to be applied to designing organs on chips, conducting clinical trials on chips, using microfluidics, manipulating genetics, and so on, for the purpose of decoding etiology and repairing damaged tissues. Considering the variety of materials that can be used with MOFs, the field of application of these materials in biomedical field is even wider, while among these materials, there are plenty of materials that solve problems such as the low biocompatibility of MOFs. However, due to the novelty of this aspect of 2D materials, there are many undiscovered applications that need to be investigated.

Author Contributions

S.N.M.N., A.B. and S.M.M. developed the idea and structure of the review article; S.A.H. and F.V.H. wrote the manuscript and collected the materials from databases; A.G. and M.G.B. revised and improved the manuscript; S.M.M., C.W.L. and W.-H.C. supervised the manuscript. All authors have read and agreed to the published version of the manuscript.

Funding

This research work was financially supported by Fundamental Research Grant Scheme FRGS/1/2020/TK0/UM/02/8 (NO.FP023-2020), and Global Collaborative Programme—SATU Joint Research Scheme (No. ST004-2021).

Institutional Review Board Statement

Not applicable.

Informed Consent Statement

Not applicable.

Data Availability Statement

All data generated or analyzed during this study are included in this published article.

Conflicts of Interest

The authors declare no conflict of interest.

References

  1. Liao, Y.; Zhang, Y.; Blum, N.T.; Lin, J.; Huang, P. Biomimetic hybrid membrane-based nanoplatforms: Synthesis, properties and biomedical applications. Nanoscale Horiz. 2020, 5, 1293–1302. [Google Scholar] [CrossRef]
  2. Huang, Z.; Cui, X.; Li, S.; Wei, J.; Li, P.; Wang, Y.; Lee, C.-S. Two-dimensional MXene-based materials for photothermal therapy. Nanophotonics 2020, 9, 2233–2249. [Google Scholar] [CrossRef]
  3. Cheng, L.; Wang, X.; Gong, F.; Liu, T.; Liu, Z. 2D nanomaterials for cancer theranostic applications. Adv. Mater. 2020, 32, 1902333. [Google Scholar] [CrossRef] [PubMed]
  4. Mousavi, S.M.; Hashemi, S.A.; Gholami, A.; Omidifar, N.; Zarei, M.; Bahrani, S.; Yousefi, K.; Chiang, W.-H.; Babapoor, A. Bioinorganic synthesis of polyrhodanine stabilized Fe3O4/Graphene oxide in microbial supernatant media for anticancer and antibacterial applications. Bioinorg. Chem. Appl. 2021, 2021, 9972664. [Google Scholar] [CrossRef]
  5. Bahrani, S.; Hashemi, S.A.; Mousavi, S.M.; Azhdari, R. Zinc-based metal–organic frameworks as nontoxic and biodegradable platforms for biomedical applications: Review study. Drug Metab. Rev. 2019, 51, 356–377. [Google Scholar] [CrossRef] [PubMed]
  6. Luo, Z.; Fan, S.; Gu, C.; Liu, W.; Chen, J.; Li, B.; Liu, J. Metal–organic framework (MOF)-based nanomaterials for biomedical applications. Curr. Med. Chem. 2019, 26, 3341–3369. [Google Scholar] [CrossRef]
  7. Chowdhury, M.A. M etal-organic-frameworks for biomedical applications in drug delivery, and as MRI contrast agents. J. Biomed. Mater. Res. Part A 2017, 105, 1184–1194. [Google Scholar] [CrossRef]
  8. Mousavi, S.M.; Hashemi, S.A.; Iman Moezzi, S.M.; Ravan, N.; Gholami, A.; Lai, C.W.; Chiang, W.-H.; Omidifar, N.; Yousefi, K.; Behbudi, G. Recent advances in enzymes for the bioremediation of pollutants. Biochem. Res. Int. 2021, 2021, 5599204. [Google Scholar] [CrossRef]
  9. Zhong, Y.; Liu, W.; Rao, C.; Li, B.; Wang, X.; Liu, D.; Pan, Y.; Liu, J. Recent Advances in Fe-MOF Compositions for Biomedical Applications. Curr. Med. Chem. 2021, 28, 6179–6198. [Google Scholar] [CrossRef]
  10. Fallahinezhad, F.; Afsa, M.; Ghahramani, Y. Graphene Quantum Dots and their applications in regenerative medicine: A mini-review. Adv. Appl. NanoBio-Technol. 2021, 4, 59–72. [Google Scholar]
  11. Yang, J.; Yang, Y.W. Metal–organic frameworks for biomedical applications. Small 2020, 16, 1906846. [Google Scholar] [CrossRef]
  12. Gholami, R.M.; Borghei, S.; Mousavi, S. Heavy metals recovery from spent catalyst using Acidithiobacillus ferrooxidans and Acidithiobacillus thiooxidans. In Proceedings of the 2010 International Conference on Chemistry and Chemical Engineering, Kyoto, Japan, 1–3 August 2010; pp. 331–335. [Google Scholar]
  13. Liu, G.; Xu, Z.; Jin, W. Recent Progress on Asymmetric Membranes Developed for Natural Gas Purification. Membr. Technol. CO2 Sequestration Sep. 2019, 53, 74–94. [Google Scholar]
  14. Ahmadi, M.; Ayyoubzadeh, S.M.; Ghorbani-Bidkorbeh, F.; Shahhosseini, S.; Dadashzadeh, S.; Asadian, E.; Mosayebnia, M.; Siavashy, S. An investigation of affecting factors on MOF characteristics for biomedical applications: A systematic review. Heliyon 2021, 7, e06914. [Google Scholar] [CrossRef]
  15. Hashemi, M.; Shojaosadati, S.A.; Razavi, S.H.; Mousavi, S.M. Evaluation of Ca-independent α-amylase production by Bacillus sp. KR-8104 in submerged and solid state fermentation systems. Iran. J. Biotechnol. 2011, 9, 188–196. [Google Scholar]
  16. Ejeian, F.; Razmjou, A.; Nasr-Esfahani, M.H.; Mohammad, M.; Karamali, F.; Warkiani, M.E.; Asadnia, M.; Chen, V. ZIF-8 modified polypropylene membrane: A biomimetic cell culture platform with a view to the improvement of guided bone regeneration. Int. J. Nanomed. 2020, 15, 10029. [Google Scholar] [CrossRef]
  17. Mousavi, S.M.; Hashemi, S.A.; Kalashgrani, M.Y.; Gholami, A.; Omidifar, N.; Babapoor, A.; Vijayakameswara Rao, N.; Chiang, W.-H. Recent Advances in Plasma-Engineered Polymers for Biomarker-Based Viral Detection and Highly Multiplexed Analysis. Biosensors 2022, 12, 286. [Google Scholar] [CrossRef]
  18. Rubio-Martinez, M.; Avci-Camur, C.; Thornton, A.W.; Imaz, I.; Maspoch, D.; Hill, M.R. New synthetic routes towards MOF production at scale. Chem. Soc. Rev. 2017, 46, 3453–3480. [Google Scholar] [CrossRef]
  19. Yap, M.H.; Fow, K.L.; Chen, G.Z. Synthesis and applications of MOF-derived porous nanostructures. Green Energy Environ. 2017, 2, 218–245. [Google Scholar] [CrossRef]
  20. Yaghi, O.; Li, H. Chromatography in a Single Metal− Organic Framework (MOF) Crystal. J. Am. Chem. Soc 1995, 117, 10401–10402. [Google Scholar] [CrossRef]
  21. Shimomura, S. Studies on Syntheses and Properties of TCNQ based Porous. Chem. Rev 1999, 183, 117–138. [Google Scholar]
  22. Bosch, M.; Yuan, S.; Rutledge, W.; Zhou, H.-C. Stepwise synthesis of metal–organic frameworks. Acc. Chem. Res. 2017, 50, 857–865. [Google Scholar] [CrossRef]
  23. Stock, N.; Biswas, S. Synthesis of metal-organic frameworks (MOFs): Routes to various MOF topologies, morphologies, and composites. Chem. Rev. 2012, 112, 933–969. [Google Scholar] [CrossRef]
  24. Bai, Y.; Dou, Y.; Xie, L.-H.; Rutledge, W.; Li, J.-R.; Zhou, H.-C. Zr-based metal–organic frameworks: Design, synthesis, structure, and applications. Chem. Soc. Rev. 2016, 45, 2327–2367. [Google Scholar] [CrossRef]
  25. Masoomi, M.Y.; Morsali, A.; Dhakshinamoorthy, A.; Garcia, H. Mixed-metal MOFs: Unique opportunities in metal–organic framework (MOF) functionality and design. Angew. Chem. 2019, 131, 15330–15347. [Google Scholar] [CrossRef]
  26. Park, J.-H.; Park, S.-H.; Jhung, S.-H. Microwave-syntheses of zeolitic imidazolate framework material, ZIF-8. J. Korean Chem. Soc. 2009, 53, 553–559. [Google Scholar]
  27. Ni, Z.; Masel, R.I. Rapid production of metal− organic frameworks via microwave-assisted solvothermal synthesis. J. Am. Chem. Soc. 2006, 128, 12394–12395. [Google Scholar] [CrossRef]
  28. Abid, H.R.; Tian, H.; Ang, H.-M.; Tade, M.O.; Buckley, C.E.; Wang, S. Nanosize Zr-metal organic framework (UiO-66) for hydrogen and carbon dioxide storage. Chem. Eng. J. 2012, 187, 415–420. [Google Scholar] [CrossRef]
  29. Horcajada, P.; Surblé, S.; Serre, C.; Hong, D.-Y.; Seo, Y.-K.; Chang, J.-S.; Grenèche, J.-M.; Margiolaki, I.; Férey, G. Synthesis and catalytic properties of MIL-100 (Fe), an iron (III) carboxylate with large pores. Chem. Commun. 2007, 27, 2820–2822. [Google Scholar] [CrossRef]
  30. Eddaoudi, M.; Kim, J.; Rosi, N.; Vodak, D.; Wachter, J.; O’Keeffe, M.; Yaghi, O.M. Systematic design of pore size and functionality in isoreticular MOFs and their application in methane storage. Science 2002, 295, 469–472. [Google Scholar] [CrossRef]
  31. Choi, J.-S.; Son, W.-J.; Kim, J.; Ahn, W.-S. Metal–organic framework MOF-5 prepared by microwave heating: Factors to be considered. Microporous Mesoporous Mater. 2008, 116, 727–731. [Google Scholar] [CrossRef]
  32. Beldon, P.J.; Fábián, L.; Stein, R.S.; Thirumurugan, A.; Cheetham, A.K.; Friščić, T. Rapid room-temperature synthesis of zeolitic imidazolate frameworks by using mechanochemistry. Angew. Chem. 2010, 122, 9834–9837. [Google Scholar] [CrossRef]
  33. Joaristi, A.M.; Juan-Alca niz, J.; Serra-Crespo, P.; Kapteijn, F.; Gascon, J. Electrochemical synthesis of some archetypical Zn 2 þ, Cu 2 þ, and Al 3þ metal organic frameworks. Cryst. Growth Des. 2012, 12, 3489–3498. [Google Scholar] [CrossRef]
  34. Yang, D.-A.; Cho, H.-Y.; Kim, J.; Yang, S.-T.; Ahn, W.-S. CO 2 capture and conversion using Mg-MOF-74 prepared by a sonochemical method. Energy Environ. Sci. 2012, 5, 6465–6473. [Google Scholar] [CrossRef]
  35. Jhung, S.H.; Lee, J.H.; Yoon, J.W.; Serre, C.; Férey, G.; Chang, J.S. Microwave synthesis of chromium terephthalate MIL-101 and its benzene sorption ability. Adv. Mater. 2007, 19, 121–124. [Google Scholar] [CrossRef]
  36. Adatoz, E.; Avci, A.K.; Keskin, S. Opportunities and challenges of MOF-based membranes in gas separations. Sep. Purif. Technol. 2015, 152, 207–237. [Google Scholar] [CrossRef]
  37. Hashemi, S.A.; Bahrani, S.; Mousavi, S.M.; Mojoudi, F.; Omidifar, N.; Lankarani, K.B.; Arjmand, M.; Ramakrishna, S. Development of sulfurized Polythiophene-Silver Iodide-Diethyldithiocarbamate nanoflakes toward Record-High and selective absorption and detection of mercury derivatives in aquatic substrates. Chem. Eng. J. 2022, 440, 135896. [Google Scholar] [CrossRef]
  38. Loeb, S.; Sourirajan, S. Sea Water Demineralization by Means of An Osmotic Membrane; University of California, Department of Engineering: Berkeley, CA, USA, 1960. [Google Scholar]
  39. Morgado, P.I.; Aguiar-Ricardo, A.; Correia, I.J. Asymmetric membranes as ideal wound dressings: An overview on production methods, structure, properties and performance relationship. J. Membr. Sci. 2015, 490, 139–151. [Google Scholar] [CrossRef]
  40. Kamoun, E.A.; Kenawy, E.-R.S.; Chen, X. A review on polymeric hydrogel membranes for wound dressing applications: PVA-based hydrogel dressings. J. Adv. Res. 2017, 8, 217–233. [Google Scholar] [CrossRef]
  41. Hinrichs, W.; Lommen, E.; Wildevuur, C.R.; Feijen, J. Fabrication and characterization of an asymmetric polyurethane membrane for use as a wound dressing. J. Appl. Biomater. 1992, 3, 287–303. [Google Scholar] [CrossRef]
  42. Miguel, S.P.; Moreira, A.F.; Correia, I.J. Chitosan based-asymmetric membranes for wound healing: A review. Int. J. Biol. Macromol. 2019, 127, 460–475. [Google Scholar] [CrossRef]
  43. Basu, S.; Cano-Odena, A.; Vankelecom, I.F. MOF-containing mixed-matrix membranes for CO2/CH4 and CO2/N2 binary gas mixture separations. Sep. Purif. Technol. 2011, 81, 31–40. [Google Scholar] [CrossRef]
  44. Rahmati, M.; Mills, D.K.; Urbanska, A.M.; Saeb, M.R.; Venugopal, J.R.; Ramakrishna, S.; Mozafari, M. Electrospinning for tissue engineering applications. Prog. Mater. Sci. 2021, 117, 100721. [Google Scholar] [CrossRef]
  45. Mousavi, S.M.; Hashemi, S.A.; Kalashgrani, M.Y.; Omidifar, N.; Bahrani, S.; Vijayakameswara Rao, N.; Babapoor, A.; Gholami, A.; Chiang, W.-H. Bioactive Graphene Quantum Dots Based Polymer Composite for Biomedical Applications. Polymers 2022, 14, 617. [Google Scholar] [CrossRef]
  46. Hashemi, S.A.; Mousavi, S.M.; Faghihi, R.; Arjmand, M.; Rahsepar, M.; Bahrani, S.; Ramakrishna, S.; Lai, C.W. Superior X-ray radiation shielding effectiveness of biocompatible polyaniline reinforced with hybrid graphene oxide-iron tungsten nitride flakes. Polymers 2020, 12, 1407. [Google Scholar] [CrossRef]
  47. Luraghi, A.; Peri, F.; Moroni, L. Electrospinning for drug delivery applications: A review. J. Control. Release 2021, 334, 463–484. [Google Scholar] [CrossRef]
  48. Hashemi, S.A.; Bahrani, S.; Mousavi, S.M.; Omidifar, N.; Arjmand, M.; Behbahan, N.G.G.; Ramakrishna, S.; Lankarani, K.B.; Moghadami, M.; Firoozsani, M. Ultrasensitive Biomolecule-Less Nanosensor Based on β-Cyclodextrin/Quinoline Decorated Graphene Oxide toward Prompt and Differentiable Detection of Corona and Influenza Viruses. Adv. Mater. Technol. 2021, 6, 2100341. [Google Scholar] [CrossRef]
  49. Phan, D.-N.; Khan, M.Q.; Nguyen, N.-T.; Phan, T.-T.; Ullah, A.; Khatri, M.; Kien, N.N.; Kim, I.-S. A review on the fabrication of several carbohydrate polymers into nanofibrous structures using electrospinning for removal of metal ions and dyes. Carbohydr. Polym. 2021, 252, 117175. [Google Scholar] [CrossRef]
  50. Mousavi, S.M.; Hashemi, S.A.; Mazraedoost, S.; Yousefi, K.; Gholami, A.; Behbudi, G.; Ramakrishna, S.; Omidifar, N.; Alizadeh, A.; Chiang, W.-H. Multifunctional gold nanorod for therapeutic applications and pharmaceutical delivery considering cellular metabolic responses, oxidative stress and cellular longevity. Nanomaterials 2021, 11, 1868. [Google Scholar] [CrossRef]
  51. Yang, L.-Y.; Cao, J.-H.; Cai, B.-R.; Liang, T.; Wu, D.-Y. Electrospun MOF/PAN composite separator with superior electrochemical performances for high energy density lithium batteries. Electrochim. Acta 2021, 382, 138346. [Google Scholar] [CrossRef]
  52. Mousavi, S.M.; Hashemi, S.A.; Parvin, N.; Gholami, A.; Ramakrishna, S.; Omidifar, N.; Moghadami, M.; Chiang, W.-H.; Mazraedoost, S. Recent biotechnological approaches for treatment of novel COVID-19: From bench to clinical trial. Drug Metab. Rev. 2021, 53, 141–170. [Google Scholar] [CrossRef]
  53. Ramezani, M.R.; Ansari-Asl, Z.; Hoveizi, E.; Kiasat, A.R. Fabrication and characterization of Fe (III) metal-organic frameworks incorporating polycaprolactone nanofibers: Potential scaffolds for tissue engineering. Fibers Polym. 2020, 21, 1013–1022. [Google Scholar] [CrossRef]
  54. Tanzli, E.; Ehrmann, A. Electrospun nanofibrous membranes for tissue engineering and cell growth. Appl. Sci. 2021, 11, 6929. [Google Scholar] [CrossRef]
  55. Hashemi, S.A.; Bahrani, S.; Mousavi, S.M.; Omidifar, N.; Arjmand, M.; Lankarani, K.B.; Ramakrishna, S. Simultaneous electrochemical detection of Cd and Pb in aquatic samples via coupled graphene with brominated white polyaniline flakes. Eur. Polym. J. 2022, 162, 110926. [Google Scholar] [CrossRef]
  56. Mousavi, S.M.; Hashemi, S.A.; Ramakrishna, S.; Esmaeili, H.; Bahrani, S.; Koosha, M.; Babapoor, A. Green synthesis of supermagnetic Fe3O4–MgO nanoparticles via Nutmeg essential oil toward superior anti-bacterial and anti-fungal performance. J. Drug Deliv. Sci. Technol. 2019, 54, 101352. [Google Scholar] [CrossRef]
  57. Qian, Q.; Asinger, P.A.; Lee, M.J.; Han, G.; Mizrahi Rodriguez, K.; Lin, S.; Benedetti, F.M.; Wu, A.X.; Chi, W.S.; Smith, Z.P. MOF-based membranes for gas separations. Chem. Rev. 2020, 120, 8161–8266. [Google Scholar] [CrossRef]
  58. Shehzad, M.A.; Yasmin, A.; Ge, X.; Wu, L.; Xu, T. A Review of Nanostructured Ion-Exchange Membranes. Adv. Mater. Technol. 2021, 6, 2001171. [Google Scholar] [CrossRef]
  59. Kang, Z.; Fan, L.; Sun, D. Recent advances and challenges of metal–organic framework membranes for gas separation. J. Mater. Chem. A 2017, 5, 10073–10091. [Google Scholar] [CrossRef]
  60. Qiu, S.; Xue, M.; Zhu, G. Metal–organic framework membranes: From synthesis to separation application. Chem. Soc. Rev. 2014, 43, 6116–6140. [Google Scholar] [CrossRef]
  61. Mousavi, S.M.; Hashemi, S.A.; Salahi, S.; Hosseini, M.; Amani, A.M.; Babapoor, A. Development of Clay Nanoparticles Toward Bio and Medical Applications; IntechOpen: London, UK, 2018. [Google Scholar]
  62. Giliopoulos, D.; Zamboulis, A.; Giannakoudakis, D.; Bikiaris, D.; Triantafyllidis, K. Polymer/metal organic framework (MOF) nanocomposites for biomedical applications. Molecules 2020, 25, 185. [Google Scholar] [CrossRef] [PubMed]
  63. Hashemi, S.A.; Bahrani, S.; Mousavi, S.M.; Omidifar, N.; Behbahan, N.G.G.; Arjmand, M.; Ramakrishna, S.; Lankarani, K.B.; Moghadami, M.; Shokripour, M. Ultra-precise label-free nanosensor based on integrated graphene with Au nanostars toward direct detection of IgG antibodies of SARS-CoV-2 in blood. J. Electroanal. Chem. 2021, 894, 115341. [Google Scholar] [CrossRef]
  64. Solaimuthu, A.; Vijayan, A.N.; Murali, P.; Korrapati, P.S. Nano-biosensors and their relevance in tissue engineering. Curr. Opin. Biomed. Eng. 2020, 13, 84–93. [Google Scholar] [CrossRef]
  65. Mousavi, S.M.; Hashemi, S.A.; Zarei, M.; Amani, A.M.; Babapoor, A. Nanosensors for chemical and biological and medical applications. Med Chem (Los Angeles) 2018, 8, 2161–0444.1000515. [Google Scholar] [CrossRef]
  66. Bieniek, A.; Terzyk, A.P.; Wiśniewski, M.; Roszek, K.; Kowalczyk, P.; Sarkisov, L.; Keskin, S.; Kaneko, K. MOF materials as therapeutic agents, drug carriers, imaging agents and biosensors in cancer biomedicine: Recent advances and perspectives. Prog. Mater. Sci. 2021, 117, 100743. [Google Scholar] [CrossRef]
  67. Hashemi, S.A.; Karimipourfard, M.; Mousavi, S.M.; Sina, S.; Bahrani, S.; Omidifar, N.; Ramakrishna, S.; Arjmand, M. Transparent Sodium Polytungstate Polyoxometalate Aquatic Shields Toward Effective X-ray Radiation Protection: Alternative to Lead Glasses. Mater. Today Commun. 2022, 31, 103822. [Google Scholar] [CrossRef]
  68. Mousavi, S.M.; Hashemi, S.A.; Mazraedoost, S.; Chiang, W.-H.; Yousefi, K.; Arjmand, O.; Ghahramani, Y.; Gholami, A.; Omidifar, N.; Rumjit, N.P. Anticancer, Antimicrobial and Biomedical Features of Polyoxometalate as Advanced Materials: A Review Study. Inorg. Chem. Commun. 2022, 146, 110074. [Google Scholar] [CrossRef]
  69. Arun Kumar, S.; Balasubramaniam, B.; Bhunia, S.; Jaiswal, M.K.; Verma, K.; Khademhosseini, A.; Gupta, R.K.; Gaharwar, A.K. Two-dimensional metal organic frameworks for biomedical applications. Wiley Interdiscip. Rev. Nanomed. Nanobiotechnol. 2021, 13, e1674. [Google Scholar]
  70. Distler, T.; Boccaccini, A.R. 3D printing of electrically conductive hydrogels for tissue engineering and biosensors–A review. Acta Biomater. 2020, 101, 1–13. [Google Scholar] [CrossRef] [PubMed]
  71. Hashemi, S.A.; Mousavi, S.M.; Arjmand, M.; Yan, N.; Sundararaj, U. Electrified single-walled carbon nanotube/epoxy nanocomposite via vacuum shock technique: Effect of alignment on electrical conductivity and electromagnetic interference shielding. Polym. Compos. 2018, 39, E1139–E1148. [Google Scholar] [CrossRef]
  72. Mousavi, S.M.; Hashemi, S.A.; Zarei, M.; Bahrani, S.; Savardashtaki, A.; Esmaeili, H.; Lai, C.W.; Mazraedoost, S.; Abassi, M.; Ramavandi, B. Data on cytotoxic and antibacterial activity of synthesized Fe3O4 nanoparticles using Malva sylvestris. Data Brief 2020, 28, 104929. [Google Scholar] [CrossRef]
  73. Hasan, A.; Nurunnabi, M.; Morshed, M.; Paul, A.; Polini, A.; Kuila, T.; Al Hariri, M.; Lee, Y.-k.; Jaffa, A.A. Recent advances in application of biosensors in tissue engineering. BioMed Res. Int. 2014, 2014, 307519. [Google Scholar] [CrossRef]
  74. Neto, N.; Dmitriev, R.I.; Monaghan, M.G. Seeing is believing: Noninvasive microscopic imaging modalities for tissue engineering and regenerative medicine. Cell Eng. Regen. 2020, 599–638. [Google Scholar]
  75. Mousavi, S.M.; Hashemi, S.A.; Zarei, M.; Gholami, A.; Lai, C.W.; Chiang, W.H.; Omidifar, N.; Bahrani, S.; Mazraedoost, S. Recent progress in chemical composition, production, and pharmaceutical effects of kombucha beverage: A complementary and alternative medicine. Evid. Based Complement. Altern. Med. 2020, 2020, 4397543. [Google Scholar] [CrossRef]
  76. Mu, X.; Wang, Z.; Zhong, Y.; Jiang, T.; Cheang, U.K. Development of 2D MOF-Based Microrobots under Annealing Treatment and Their Biomedical Application. Ind. Eng. Chem. Res. 2021, 60, 9465–9474. [Google Scholar] [CrossRef]
  77. Hosseini, H.; Mousavi, S.M. Bacterial cellulose/polyaniline nanocomposite aerogels as novel bioadsorbents for removal of hexavalent chromium: Experimental and simulation study. J. Clean. Prod. 2021, 278, 123817. [Google Scholar] [CrossRef]
  78. Hasan, M.N.; Bera, A.; Maji, T.K.; Pal, S.K. Sensitization of nontoxic MOF for their potential drug delivery application against microbial infection. Inorg. Chim. Acta 2021, 523, 120381. [Google Scholar] [CrossRef]
  79. Cao, J.; Li, X.; Tian, H. Metal-organic framework (MOF)-based drug delivery. Curr. Med. Chem. 2020, 27, 5949–5969. [Google Scholar] [CrossRef]
  80. Hashemi, S.A.; Mousavi, S.M.; Bahrani, S.; Omidifar, N.; Arjmand, M.; Ramakrishna, S.; Hagfeldt, A.; Lankarani, K.B.; Chiang, W.-H. Decorated graphene oxide flakes with integrated complex of 8-hydroxyquinoline/NiO toward accurate detection of glucose at physiological conditions. J. Electroanal. Chem. 2021, 893, 115303. [Google Scholar] [CrossRef]
  81. Illes, B.; Hirschle, P.; Barnert, S.; Cauda, V.; Wuttke, S.; Engelke, H. Exosome-coated metal–organic framework nanoparticles: An efficient drug delivery platform. Chem. Mater. 2017, 29, 8042–8046. [Google Scholar] [CrossRef]
  82. Huang, G.; Huang, H. Hyaluronic acid-based biopharmaceutical delivery and tumor-targeted drug delivery system. J. Control. Release 2018, 278, 122–126. [Google Scholar] [CrossRef]
  83. Lawson, H.D.; Walton, S.P.; Chan, C. Metal–organic frameworks for drug delivery: A design perspective. ACS Appl. Mater. Interfaces 2021, 13, 7004–7020. [Google Scholar] [CrossRef]
  84. Mousavi, S.M.; Soroshnia, S.; Hashemi, S.A.; Babapoor, A.; Ghasemi, Y.; Savardashtaki, A.; Amani, A.M. Graphene nano-ribbon based high potential and efficiency for DNA, cancer therapy and drug delivery applications. Drug Metab. Rev. 2019, 51, 91–104. [Google Scholar] [CrossRef]
  85. Ahmadi, S.; Fazilati, M.; Nazem, H.; Mousavi, S.M. Green synthesis of magnetic nanoparticles using Satureja hortensis essential oil toward superior antibacterial/fungal and anticancer performance. BioMed Res. Int. 2021, 2021, 8822645. [Google Scholar] [CrossRef]
  86. Huang, R.; Cai, G.-Q.; Li, J.; Li, X.-S.; Liu, H.-T.; Shang, X.-L.; Zhou, J.-D.; Nie, X.-M.; Gui, R. Platelet membrane-camouflaged silver metal-organic framework drug system against infections caused by methicillin-resistant Staphylococcus aureus. J. Nanobiotechnol. 2021, 19, 1–19. [Google Scholar] [CrossRef]
  87. Mousavi, S.M.; Yousefi, K.; Hashemi, S.A.; Afsa, M.; BahranI, S.; Gholami, A.; Ghahramani, Y.; Alizadeh, A.; Chiang, W.-H. Renewable carbon nanomaterials: Novel resources for dental tissue engineering. Nanomaterials 2021, 11, 2800. [Google Scholar] [CrossRef]
  88. Liu, W.; Yan, Q.; Xia, C.; Wang, X.; Kumar, A.; Wang, Y.; Liu, Y.; Pan, Y.; Liu, J. Recent advances in cell membrane coated metal–organic frameworks (MOFs) for tumor therapy. J. Mater. Chem. B 2021, 9, 4459–4474. [Google Scholar] [CrossRef]
  89. Hashemi, S.A.; Mousavi, S.M.; Bahrani, S.; Ramakrishna, S. Integrated polyaniline with graphene oxide-iron tungsten nitride nanoflakes as ultrasensitive electrochemical sensor for precise detection of 4-nitrophenol within aquatic media. J. Electroanal. Chem. 2020, 873, 114406. [Google Scholar] [CrossRef]
  90. Ghahramani, Y.; Mokhberi, M.; Mousavi, S.M.; Hashemi, S.A.; Fallahi Nezhad, F.; Chiang, W.-H.; Gholami, A.; Lai, C.W. Synergistically Enhancing the Therapeutic Effect on Cancer, via Asymmetric Bioinspired Materials. Molecules 2022, 27, 8543. [Google Scholar] [CrossRef]
  91. Wang, D.; Zhao, C.; Gao, G.; Xu, L.; Wang, G.; Zhu, P. Multifunctional NaLnF4@ MOF-Ln nanocomposites with dual-mode luminescence for drug delivery and cell imaging. Nanomaterials 2019, 9, 1274. [Google Scholar] [CrossRef]
  92. Mousavi, S.M.; Zarei, M.; Hashemi, S.A.; Ramakrishna, S.; Chiang, W.-H.; Lai, C.W.; Gholami, A.; Omidifar, N.; Shokripour, M. Asymmetric membranes: A potential scaffold for wound healing applications. Symmetry 2020, 12, 1100. [Google Scholar] [CrossRef]
  93. Tan, G.; Zhong, Y.; Yang, L.; Jiang, Y.; Liu, J.; Ren, F. A multifunctional MOF-based nanohybrid as injectable implant platform for drug synergistic oral cancer therapy. Chem. Eng. J. 2020, 390, 124446. [Google Scholar] [CrossRef]
  94. Mousavi, S.M.; Zarei, M.; Hashemi, S.A.; Babapoor, A.; Amani, A.M. A conceptual review of rhodanine: Current applications of antiviral drugs, anticancer and antimicrobial activities. Artif. Cells Nanomed. Biotechnol. 2019, 47, 1132–1148. [Google Scholar] [CrossRef]
  95. Zhang, E.; Phan, P.; Algarni, H.A.; Zhao, Z. Red blood cell inspired strategies for drug delivery: Emerging concepts and new advances. Pharm. Res. 2022, 39, 1–26. [Google Scholar]
  96. Lee, N.-H.; You, S.; Taghizadeh, A.; Taghizadeh, M.; Kim, H.S. Cell Membrane-Cloaked Nanotherapeutics for Targeted Drug Delivery. Int. J. Mol. Sci. 2022, 23, 2223. [Google Scholar] [CrossRef]
  97. Liu, X.; Zhong, X.; Li, C. Challenges in cell membrane-camouflaged drug delivery systems: Development strategies and future prospects. Chin. Chem. Lett. 2021, 32, 2347–2358. [Google Scholar] [CrossRef]
  98. Hashemi, S.A.; Mousavi, S.M.; Bahrani, S.; Ramakrishna, S.; Hashemi, S.H. Picomolar-level detection of mercury within non-biological/biological aqueous media using ultra-sensitive polyaniline-Fe3O4-silver diethyldithiocarbamate nanostructure. Anal. Bioanal. Chem. 2020, 412, 5353–5365. [Google Scholar] [CrossRef]
  99. Falsafi, M.; Zahiri, M.; Saljooghi, A.S.; Abnous, K.; Taghdisi, S.M.; Sazgarnia, A.; Ramezani, M.; Alibolandi, M. Aptamer targeted red blood cell membrane-coated porphyrinic copper-based MOF for guided photochemotherapy against metastatic breast cancer. Microporous Mesoporous Mater. 2021, 325, 111337. [Google Scholar] [CrossRef]
  100. Esquivel-Castro, T.A.; Ibarra-Alonso, M.; Oliva, J.; Martínez-Luévanos, A. Porous aerogel and core/shell nanoparticles for controlled drug delivery: A review. Mater. Sci. Eng. C 2019, 96, 915–940. [Google Scholar] [CrossRef]
  101. Wang, Z.; Wang, S.; Wang, A.; Liu, X.; Chen, J.; Zeng, Q.; Zhang, L.; Liu, W.; Zhang, L. Covalently linked metal–organic framework (MOF)-polymer all-solid-state electrolyte membranes for room temperature high performance lithium batteries. J. Mater. Chem. A 2018, 6, 17227–17234. [Google Scholar] [CrossRef]
  102. Hashemi, S.A.; Mousavi, S.M.; Naderi, H.R.; Bahrani, S.; Arjmand, M.; Hagfeldt, A.; Chiang, W.-H.; Ramakrishna, S. Reinforced polypyrrole with 2D graphene flakes decorated with interconnected nickel-tungsten metal oxide complex toward superiorly stable supercapacitor. Chem. Eng. J. 2021, 418, 129396. [Google Scholar] [CrossRef]
  103. Anahidzade, N.; Abdolmaleki, A.; Dinari, M.; Tadavani, K.F.; Zhiani, M. Metal-organic framework anchored sulfonated poly (ether sulfone) as a high temperature proton exchange membrane for fuel cells. J. Membr. Sci. 2018, 565, 281–292. [Google Scholar] [CrossRef]
  104. Mousavi, S.M.; Zarei, M.; Hashemi, S.A.; Ramakrishna, S.; Chiang, W.-H.; Lai, C.W.; Gholami, A. Gold nanostars-diagnosis, bioimaging and biomedical applications. Drug Metab. Rev. 2020, 52, 299–318. [Google Scholar] [CrossRef]
  105. Qian, S.; Song, L.; Sun, L.; Zhang, X.; Xin, Z.; Yin, J.; Luan, S. Metal-organic framework/poly (ε-caprolactone) hybrid electrospun nanofibrous membranes with effective photodynamic antibacterial activities. J. Photochem. Photobiol. A Chem. 2020, 400, 112626. [Google Scholar] [CrossRef]
  106. Yang, R.; Zheng, Y.; Zhang, Y.; Li, G.; Xu, Y.; Zhang, Y.; Xu, Y.; Zhuang, C.; Yu, P.; Deng, L. Bipolar Metal Flexible Electrospun Fibrous Membrane Based on Metal–Organic Framework for Gradient Healing of Tendon-to-Bone Interface Regeneration. Adv. Healthc. Mater. 2022, 11, 2200072. [Google Scholar] [CrossRef]
  107. Wang, Y.; Xu, Y.; Zhou, G.; Liu, Y.; Cao, Y. Biological evaluation of acellular cartilaginous and dermal matrixes as tissue engineering scaffolds for cartilage regeneration. Front. Cell Dev. Biol. 2021, 8, 624337. [Google Scholar] [CrossRef]
  108. Hashemi, S.A.; Mousavi, S.M.; Ramakrishna, S. Effective removal of mercury, arsenic and lead from aqueous media using Polyaniline-Fe3O4-silver diethyldithiocarbamate nanostructures. J. Clean. Prod. 2019, 239, 118023. [Google Scholar] [CrossRef]
  109. Benatti, A.C.B.; Pattaro, A.F.; Rodrigues, A.A.; Xavier, M.V.; Kaasi, A.; Barbosa, M.I.R.; Jardini, A.L.; Maciel Filho, R.; Kharmandayan, P. Bioreabsorbable polymers for tissue engineering: PLA, PGA, and their copolymers. In Materials for Biomedical Engineering; Elsevier: Amsterdam, The Netherlands, 2019; pp. 83–116. [Google Scholar]
  110. Sahoo, D.R.; Biswal, T. Alginate and its application to tissue engineering. SN Appl. Sci. 2021, 3, 1–19. [Google Scholar] [CrossRef]
  111. Spicer, C.D. Hydrogel scaffolds for tissue engineering: The importance of polymer choice. Polym. Chem. 2020, 11, 184–219. [Google Scholar] [CrossRef]
  112. Wu, T.; Ding, M.; Shi, C.; Qiao, Y.; Wang, P.; Qiao, R.; Wang, X.; Zhong, J. Resorbable polymer electrospun nanofibers: History, shapes and application for tissue engineering. Chin. Chem. Lett. 2020, 31, 617–625. [Google Scholar] [CrossRef]
  113. Hosseini, H.; Mousavi, S.M. Density functional theory simulation for Cr (VI) removal from wastewater using bacterial cellulose/polyaniline. Int. J. Biol. Macromol. 2020, 165, 883–901. [Google Scholar] [CrossRef]
  114. Murali, A.; Lokhande, G.; Deo, K.A.; Brokesh, A.; Gaharwar, A.K. Emerging 2D nanomaterials for biomedical applications. Mater. Today 2021, 50, 276–302. [Google Scholar] [CrossRef]
  115. Wang, Z.; Colombi Ciacchi, L.; Wei, G. Recent advances in the synthesis of graphene-based nanomaterials for controlled drug delivery. Appl. Sci. 2017, 7, 1175. [Google Scholar] [CrossRef]
  116. Zheng, Y.; Hong, X.; Wang, J.; Feng, L.; Fan, T.; Guo, R.; Zhang, H. 2D nanomaterials for tissue engineering and regenerative nanomedicines: Recent advances and future challenges. Adv. Healthc. Mater. 2021, 10, 2001743. [Google Scholar] [CrossRef] [PubMed]
  117. Sun, R.; Chen, H.; Sutrisno, L.; Kawazoe, N.; Chen, G. Nanomaterials and their composite scaffolds for photothermal therapy and tissue engineering applications. Sci. Technol. Adv. Mater. 2021, 22, 404–428. [Google Scholar] [CrossRef]
  118. González, C.M.O.; Kharisov, B.I.; Kharissova, O.V.; Quezada, T.E.S. Synthesis and applications of MOF-derived nanohybrids: A review. Mater. Today Proc. 2021, 46, 3018–3029. [Google Scholar] [CrossRef]
  119. Cai, M.-H.; Chen, X.-Y.; Fu, L.-Q.; Du, W.-L.; Yang, X.; Mou, X.-Z.; Hu, P.-Y. Design and development of hybrid hydrogels for biomedical applications: Recent trends in anticancer drug delivery and tissue engineering. Front. Bioeng. Biotechnol. 2021, 9, 630943. [Google Scholar] [CrossRef]
  120. Ahmadi, S.; Fazilati, M.; Mousavi, S.M.; Nazem, H. Anti-bacterial/fungal and anti-cancer performance of green synthesized Ag nanoparticles using summer savory extract. J. Exp. Nanosci. 2020, 15, 363–380. [Google Scholar] [CrossRef]
  121. Kalaj, M.; Bentz, K.C.; Ayala Jr, S.; Palomba, J.M.; Barcus, K.S.; Katayama, Y.; Cohen, S.M. MOF-polymer hybrid materials: From simple composites to tailored architectures. Chem. Rev. 2020, 120, 8267–8302. [Google Scholar] [CrossRef]
  122. Hosseini, H.; Mousavi, S.M.; Wurm, F.R.; Goodarzi, V. Display of hidden properties of flexible aerogel based on bacterial cellulose/polyaniline nanocomposites with helping of multiscale modeling. Eur. Polym. J. 2021, 146, 110251. [Google Scholar] [CrossRef]
  123. Spiridonova, T.I.; Tverdokhlebov, S.I.; Anissimov, Y.G. Investigation of the size distribution for diffusion-controlled drug release from drug delivery systems of various geometries. J. Pharm. Sci. 2019, 108, 2690–2697. [Google Scholar] [CrossRef]
  124. Patil, P.; Uphade, K.; Saudagar, R. A Review: Osmotic Drug Delivery System. Pharma Sci. Monit. 2018, 9, 283–300. [Google Scholar]
  125. Khan, S.A.; Ali, H. Novel Drug Delivery Systems. In Essentials of Industrial Pharmacy; Springer: Berlin/Heidelberg, Germany, 2022; pp. 235–250. [Google Scholar]
  126. Jafari, A.; Zamankhan, P.; Mousavi, S.M.; Henttinen, K. Multiscale modeling of fluid turbulence and flocculation in fiber suspensions. J. Appl. Phys. 2006, 100, 034901. [Google Scholar] [CrossRef]
  127. Good, W.R.; Lee, P.I. Membrane–Controlled Reservoir Drug Delivery Systems. In Medical Applications of Controlled Release; CRC Press: Boca Raton, FL, USA, 2019; pp. 1–40. [Google Scholar]
  128. Zhang, W.J.; Hong, C.Y.; Pan, C.Y. Polymerization—Induced Self—Assembly of Functionalized Block Copolymer Nanoparticles and Their Application in Drug Delivery. Macromol. Rapid Commun. 2019, 40, 1800279. [Google Scholar] [CrossRef]
  129. Yao, S.; Chi, J.; Wang, Y.; Zhao, Y.; Luo, Y.; Wang, Y. Zn-MOF Encapsulated Antibacterial and Degradable Microneedles Array for Promoting Wound Healing. Adv. Healthc. Mater. 2021, 10, 2100056. [Google Scholar] [CrossRef]
  130. Sabbagh, F.; Kim, B.S. Recent advances in polymeric transdermal drug delivery systems. J. Control. Release 2022, 341, 132–146. [Google Scholar] [CrossRef]
  131. Kalashgarani, M.Y.; Babapoor, A. Application of nano-antibiotics in the diagnosis and treatment of infectious diseases. Adv. Appl. NanoBio-Technol. 2022, 3, 22–35. [Google Scholar]
  132. Kubovics, M.; Rojas, S.; Lopez, A.M.; Fraile, J.; Horcajada, P.; Domingo, C. Fully supercritical CO2 preparation of a nanostructured MOF composite with application in cutaneous drug delivery. J. Supercrit. Fluids 2021, 178, 105379. [Google Scholar] [CrossRef]
  133. Gao, Y.; Hao, Y.; Zhang, W.; Wei, Y.; Shu, Y.; Wang, J. Microwave-triggered ionic liquid-based hydrogel dressing with excellent hyperthermia and transdermal drug delivery performance. Chem. Eng. J. 2022, 429, 131590. [Google Scholar] [CrossRef]
  134. Yewale, C.; Tandel, H.; Patel, A.; Misra, A. Polymers in Transdermal Drug Delivery. In Applications of Polymers in Drug Delivery; Elsevier: Amsterdam, The Netherlands, 2021; pp. 131–158. [Google Scholar]
  135. Kalashgrani, M.Y.; Harzand, F.V.; Javanmardi, N.; Nejad, F.F.; Rahmanian, V. Recent Advances in Multifunctional magnetic nano platform for Biomedical Applications: A mini review. Adv. Appl. NanoBio-Technol. 2022, 3, 31–37. [Google Scholar]
  136. Rasouli, R.; Barhoum, A.; Bechelany, M.; Dufresne, A. Nanofibers for biomedical and healthcare applications. Macromol. Biosci. 2019, 19, 1800256. [Google Scholar] [CrossRef]
  137. Beamish-Cook, J.; Shankland, K.; Murray, C.A.; Vaqueiro, P. Insights into the Mechanochemical Synthesis of MOF-74. Cryst. Growth Des. 2021, 21, 3047–3055. [Google Scholar] [CrossRef]
  138. Kalashgrani, M.Y.; Javanmardi, N. Multifunctional Gold nanoparticle: As novel agents for cancer treatment. Adv. Appl. NanoBio-Technol. 2022, 3, 1–6. [Google Scholar]
  139. Sánchez-Fernández, J.; Cué-Sampedro, R.; Flores-Hernandez, D.R. Metal-Organic Frameworks-Polymer Composites for Practical Applications: Compatibility, Processability, and Biotribology Studies. In Biotribology; CRC Press: Boca Raton, FL, USA, 2021; pp. 123–145. [Google Scholar]
  140. Shyngys, M.; Ren, J.; Liang, X.; Miao, J.; Blocki, A.; Beyer, S. Metal-organic framework (MOF)-based biomaterials for tissue engineering and regenerative medicine. Front. Bioeng. Biotechnol. 2021, 9, 603608. [Google Scholar] [CrossRef]
  141. Kalashgrani, M.Y.; Nejad, F.F.; Rahmanian, V. Carbon Quantum Dots Platforms: As nano therapeutic for Biomedical Applications. Adv. Appl. NanoBio-Technol. 2022, 3, 38–42. [Google Scholar]
  142. Mousavi, S.; Arjmand, O.; Hashemi, S.; Banaei, N. Modification of the epoxy resin mechanical and thermal properties with silicon acrylate and montmorillonite nanoparticles. Polym. Renew. Resour. 2016, 7, 101–113. [Google Scholar] [CrossRef]
  143. Mousavi, S.; Arjmand, O.; Talaghat, M.; Azizi, M.; Shooli, H. Modifying the properties of polypropylene-wood composite by natural polymers and eggshell Nano-particles. Polym. Renew. Resour. 2015, 6, 157–173. [Google Scholar] [CrossRef]
  144. Koons, G.L.; Diba, M.; Mikos, A.G. Materials design for bone-tissue engineering. Nat. Rev. Mater. 2020, 5, 584–603. [Google Scholar] [CrossRef]
  145. Luo, G.; Jiang, Y.; Xie, C.; Lu, X. Metal—Organic framework—Based biomaterials for biomedical applications. Biosurf. Biotribol. 2021, 7, 99–112. [Google Scholar] [CrossRef]
  146. Unal, A.Z.; West, J.L. Synthetic ECM: Bioactive synthetic hydrogels for 3D tissue engineering. Bioconjugate Chem. 2020, 31, 2253–2271. [Google Scholar] [CrossRef]
  147. Heydarkhan-Hagvall, S.; Schenke-Layland, K.; Dhanasopon, A.P.; Rofail, F.; Smith, H.; Wu, B.M.; Shemin, R.; Beygui, R.E.; MacLellan, W.R. Three-dimensional electrospun ECM-based hybrid scaffolds for cardiovascular tissue engineering. Biomaterials 2008, 29, 2907–2914. [Google Scholar] [CrossRef]
  148. Zhu, G.; Zhang, T.; Chen, M.; Yao, K.; Huang, X.; Zhang, B.; Li, Y.; Liu, J.; Wang, Y.; Zhao, Z. Bone physiological microenvironment and healing mechanism: Basis for future bone-tissue engineering scaffolds. Bioact. Mater. 2021, 6, 4110–4140. [Google Scholar] [CrossRef]
  149. Madrid, A.P.M.; Vrech, S.M.; Sanchez, M.A.; Rodriguez, A.P. Advances in additive manufacturing for bone tissue engineering scaffolds. Mater. Sci. Eng. C 2019, 100, 631–644. [Google Scholar] [CrossRef]
  150. Jiao, Y.; Li, C.; Liu, L.; Wang, F.; Liu, X.; Mao, J.; Wang, L. Construction and application of textile-based tissue engineering scaffolds: A review. Biomater. Sci. 2020, 8, 3574–3600. [Google Scholar] [CrossRef]
  151. Mousavi, S.; Esmaeili, H.; Arjmand, O.; Karimi, S.; Hashemi, S. Biodegradation study of nanocomposites of phenol novolac epoxy/unsaturated polyester resin/egg shell nanoparticles using natural polymers. J. Mater. 2015, 2015, 1–6. [Google Scholar] [CrossRef] [Green Version]
  152. Abedi, A.; Hasanzadeh, M.; Tayebi, L. Conductive nanofibrous Chitosan/PEDOT: PSS tissue engineering scaffolds. Mater. Chem. Phys. 2019, 237, 121882. [Google Scholar] [CrossRef]
  153. Soundarya, S.P.; Menon, A.H.; Chandran, S.V.; Selvamurugan, N. Bone tissue engineering: Scaffold preparation using chitosan and other biomaterials with different design and fabrication techniques. Int. J. Biol. Macromol. 2018, 119, 1228–1239. [Google Scholar] [CrossRef]
  154. Iijima, K.; Otsuka, H. Cell scaffolds for bone tissue engineering. Bioengineering 2020, 7, 119. [Google Scholar] [CrossRef]
  155. Qu, H.; Fu, H.; Han, Z.; Sun, Y. Biomaterials for bone tissue engineering scaffolds: A review. RSC Adv. 2019, 9, 26252–26262. [Google Scholar] [CrossRef]
  156. Zhang, M.; Wang, G.; Zhang, X.; Zheng, Y.; Lee, S.; Wang, D.; Yang, Y. Polyvinyl Alcohol/Chitosan and Polyvinyl Alcohol/Ag@ MOF Bilayer Hydrogel for Tissue Engineering Applications. Polymers 2021, 13, 3151. [Google Scholar] [CrossRef]
  157. Mousavi, S.; Zarei, M.; Hashemi, S. Polydopamine for biomedical application and drug delivery system. Med. Chem. (Los Angeles) 2018, 8, 218–229. [Google Scholar] [CrossRef]
  158. Copes, F.; Pien, N.; Van Vlierberghe, S.; Boccafoschi, F.; Mantovani, D. Collagen-based tissue engineering strategies for vascular medicine. Front. Bioeng. Biotechnol. 2019, 7, 166. [Google Scholar] [CrossRef]
  159. Blackstone, B.N.; Gallentine, S.C.; Powell, H.M. Collagen-based electrospun materials for tissue engineering: A systematic review. Bioengineering 2021, 8, 39. [Google Scholar] [CrossRef] [PubMed]
  160. Fazzotta, S.; Buscemi, S.; Palumbo, V.; Damiano, G.; Geraci, G.; Licciardi, M.; Palumbo, F.; Fiorica, C.; Cudia, B.; Genova, P. Nanofibrillar scaffold resists to bile and urine action: Experiences in pigs. Клиническая и экспериментальная хирургия 2020, 8, 29–34. [Google Scholar] [CrossRef]
  161. Mousavi, S.-M.; Nejad, Z.M.; Hashemi, S.A.; Salari, M.; Gholami, A.; Ramakrishna, S.; Chiang, W.-H.; Lai, C.W. Bioactive agent-loaded electrospun nanofiber membranes for accelerating healing process: A review. Membranes 2021, 11, 702. [Google Scholar] [CrossRef]
  162. Wubneh, A.; Tsekoura, E.K.; Ayranci, C.; Uludağ, H. Current state of fabrication technologies and materials for bone tissue engineering. Acta Biomater. 2018, 80, 1–30. [Google Scholar] [CrossRef] [PubMed]
  163. Mousavi, S.M.; Behbudi, G.; Gholami, A.; Hashemi, S.A.; Nejad, Z.M.; Bahrani, S.; Chiang, W.-H.; Wei, L.C.; Omidifar, N. Shape-controlled synthesis of zinc nanostructures mediating macromolecules for biomedical applications. Biomater. Res. 2022, 26, 1–20. [Google Scholar] [CrossRef] [PubMed]
  164. Kumar, R.; Aadil, K.R.; Ranjan, S.; Kumar, V.B. Advances in nanotechnology and nanomaterials based strategies for neural tissue engineering. J. Drug Deliv. Sci. Technol. 2020, 57, 101617. [Google Scholar] [CrossRef]
  165. Funda, G.; Taschieri, S.; Bruno, G.A.; Grecchi, E.; Paolo, S.; Girolamo, D.; Del Fabbro, M. Nanotechnology scaffolds for alveolar bone regeneration. Materials 2020, 13, 201. [Google Scholar] [CrossRef]
  166. Kwon, K.-J.; Seok, H. Silk protein-based membrane for guided bone regeneration. Appl. Sci. 2018, 8, 1214. [Google Scholar] [CrossRef]
  167. Mousavi, S.M.; Farsi, M.; Azizi, M. Enhancement of rheological and mechanical properties of bitumen using styrene acrylonitrile copolymer. J. Appl. Polym. Sci. 2015, 132, 17. [Google Scholar] [CrossRef]
  168. Zhang, K.-R.; Gao, H.-L.; Pan, X.-F.; Zhou, P.; Xing, X.; Xu, R.; Pan, Z.; Wang, S.; Zhu, Y.; Hu, B. Multifunctional bilayer nanocomposite guided bone regeneration membrane. Matter 2019, 1, 770–781. [Google Scholar] [CrossRef]
  169. Mousavi, S.M.; Hashemi, S.A.; Bahrani, S.; Sadrmousavi-Dizaj, A.; Arjmand, O.; Omidifar, N.; Lai, C.W.; Chiang, W.-H.; Gholami, A. Bioinorganic Synthesis of Sodium Polytungstate/Polyoxometalate in Microbial Kombucha Media for Precise Detection of Doxorubicin. Bioinorg. Chem. Appl. 2022, 2022, 2265108. [Google Scholar] [CrossRef]
  170. Sbricoli, L.; Guazzo, R.; Annunziata, M.; Gobbato, L.; Bressan, E.; Nastri, L. Selection of collagen membranes for bone regeneration: A literature review. Materials 2020, 13, 786. [Google Scholar] [CrossRef]
  171. Mousavi, S.M.; Hashemi, S.A.; Bahrani, S.; Yousefi, K.; Behbudi, G.; Babapoor, A.; Omidifar, N.; Lai, C.W.; Gholami, A.; Chiang, W.-H. Recent advancements in polythiophene-based materials and their biomedical, geno sensor and DNA detection. Int. J. Mol. Sci. 2021, 22, 6850. [Google Scholar] [CrossRef]
  172. Xue, Y.; Zhu, Z.; Zhang, X.; Chen, J.; Yang, X.; Gao, X.; Zhang, S.; Luo, F.; Wang, J.; Zhao, W. Accelerated bone regeneration by MOF modified multifunctional membranes through enhancement of osteogenic and angiogenic performance. Adv. Healthc. Mater. 2021, 10, 2001369. [Google Scholar] [CrossRef]
  173. Ramezani, M.R.; Ansari-Asl, Z.; Hoveizi, E.; Kiasat, A.R. Polyacrylonitrile/Fe (III) metal-organic framework fibrous nanocomposites designed for tissue engineering applications. Mater. Chem. Phys. 2019, 229, 242–250. [Google Scholar] [CrossRef]
  174. Mousavi, S.M.; Hashemi, S.A.; Ghahramani, Y.; Azhdari, R.; Yousefi, K.; Gholami, A.; Fallahi Nezhad, F.; Vijayakameswara Rao, N.; Omidifar, N.; Chiang, W.-H. Antiproliferative and Apoptotic Effects of Graphene Oxide@ AlFu MOF Based Saponin Natural Product on OSCC Line. Pharmaceuticals 2022, 15, 1137. [Google Scholar] [CrossRef]
  175. Hoseinpour, V.; Shariatinia, Z. Applications of zeolitic imidazolate framework-8 (ZIF-8) in bone tissue engineering: A review. Tissue Cell 2021, 72, 101588. [Google Scholar] [CrossRef]
  176. Liu, Y.; Zhu, Z.; Pei, X.; Zhang, X.; Cheng, X.; Hu, S.; Gao, X.; Wang, J.; Chen, J.; Wan, Q. ZIF-8-modified multifunctional bone-adhesive hydrogels promoting angiogenesis and osteogenesis for bone regeneration. ACS Appl. Mater. Interfaces 2020, 12, 36978–36995. [Google Scholar] [CrossRef]
  177. Zhang, L.; Wang, Z.; Zhang, Y.; Cao, F.; Dong, K.; Ren, J.; Qu, X. Erythrocyte membrane cloaked metal–organic framework nanoparticle as biomimetic nanoreactor for starvation-activated colon cancer therapy. ACS Nano 2018, 12, 10201–10211. [Google Scholar] [CrossRef]
  178. Mousavi, S.M.; Hashemi, S.A.; Ghasemi, Y.; Amani, A.M.; Babapoor, A.; Arjmand, O. Applications of graphene oxide in case of nanomedicines and nanocarriers for biomolecules: Review study. Drug Metab. Rev. 2019, 51, 12–41. [Google Scholar] [CrossRef]
  179. Xiao, Y.; Huang, W.; Zhu, D.; Wang, Q.; Chen, B.; Liu, Z.; Wang, Y.; Liu, Q. Cancer cell membrane-camouflaged MOF nanoparticles for a potent dihydroartemisinin-based hepatocellular carcinoma therapy. RSC Adv. 2020, 10, 7194–7205. [Google Scholar] [CrossRef]
  180. Xiang, X.; Pang, H.; Ma, T.; Du, F.; Li, L.; Huang, J.; Ma, L.; Qiu, L. Ultrasound targeted microbubble destruction combined with Fe-MOF based bio-/enzyme-mimics nanoparticles for treating of cancer. J. Nanobiotechnol. 2021, 19, 1–14. [Google Scholar] [CrossRef]
  181. Liu, J.; Huang, J.; Zhang, L.; Lei, J. Multifunctional metal–organic framework heterostructures for enhanced cancer therapy. Chem. Soc. Rev. 2021, 50, 1188–1218. [Google Scholar] [CrossRef]
  182. Yang, J.; Yang, Y.W. Metal—Organic framework-based cancer theranostic nanoplatforms. View 2020, 1, e20. [Google Scholar] [CrossRef]
  183. Mousavi, S.M.; Hashemi, S.A.; Gholami, A.; Kalashgrani, M.Y.; Vijayakameswara Rao, N.; Omidifar, N.; Hsiao, W.W.-W.; Lai, C.W.; Chiang, W.-H. Plasma-Enabled Smart Nanoexosome Platform as Emerging Immunopathogenesis for Clinical Viral Infection. Pharmaceutics 2022, 14, 1054. [Google Scholar] [CrossRef]
  184. Feng, L.; Song, C. Coated Metal-Organic Framework Composites for Anti-Cancer Drug Delivery: Preparation and Applications. Molecules 2022, 6, 155–164. [Google Scholar] [CrossRef]
  185. Alyami, M.Z.; Li, Y.; Patel, N.; Baslyman, W.; Alahmed, O.; Alsharif, N.A.; Sleiman, J.; Kosel, J.; Merzaban, J.S.; Khashab, N.M. Iron Nanowires Coated with Metal–Organic Frameworks for Cell-Type-Specific Multimodal Therapy. ACS Appl. Nano Mater. 2022, 5, 13903–13911. [Google Scholar] [CrossRef]
  186. Quirós, J.; Boltes, K.; Aguado, S.; de Villoria, R.G.; Vilatela, J.J.; Rosal, R. Antimicrobial metal–organic frameworks incorporated into electrospun fibers. Chem. Eng. J. 2015, 262, 189–197. [Google Scholar] [CrossRef]
  187. Zang, Y.; Roberts, T.R.; Batchinsky, A.I.; Reynolds, M.M. Metal–organic framework polymer coating inhibits Staphylococcus aureus attachment on medical circulation tubing under static and dynamic flow conditions. ACS Appl. Bio Mater. 2020, 3, 3535–3543. [Google Scholar] [CrossRef]
  188. Li, T.-T.; Zhang, H.; Gao, B.; Shiu, B.-C.; Ren, H.-T.; Peng, H.-K.; Lou, C.-W.; Lin, J.-H. Daylight-driven rechargeable, antibacterial, filtrating micro/nanofibrous composite membranes with bead-on-string structure for medical protection. Chem. Eng. J. 2021, 422, 130007. [Google Scholar] [CrossRef]
  189. Wang, H.; Chen, W.; Chen, Q.; Liu, N.; Cheng, H.; Li, T. Metal-organic framework (MOF)-Au@ Pt nanoflowers composite material for electrochemical sensing of H2O2 in living cells. J. Electroanal. Chem. 2021, 897, 115603. [Google Scholar] [CrossRef]
  190. López-R, M.; Barrios, Y.; Perez, L.D.; Soto, C.; Sierra, C. Metal-Organic Framework (MOFs) tethered to cotton fibers display antimicrobial activity against relevant nosocomial bacteria. Inorg. Chim. Acta 2022, 537, 120955. [Google Scholar] [CrossRef]
  191. Hu, Y.; Yang, H.; Wang, R.; Duan, M. Fabricating Ag@ MOF-5 nanoplates by the template of MOF-5 and evaluating its antibacterial activity. Colloids Surf. A Physicochem. Eng. Asp. 2021, 626, 127093. [Google Scholar] [CrossRef]
Figure 1. Various scaffolds after seeding HUVEC are shown in scanning electron micrographs. (a) Placing HUVEC on a PAN scaffold, (b) placing HUVEC on a PAN/5% FeMOF scaffold, (c) placing HUVEC on a PAN/10% FeMOF scaffold, and (d) placing HUVEC on a PAN/20% FeMOF scaffold. Reprinted from [54]. Copyright © 2021, MDPI.
Figure 1. Various scaffolds after seeding HUVEC are shown in scanning electron micrographs. (a) Placing HUVEC on a PAN scaffold, (b) placing HUVEC on a PAN/5% FeMOF scaffold, (c) placing HUVEC on a PAN/10% FeMOF scaffold, and (d) placing HUVEC on a PAN/20% FeMOF scaffold. Reprinted from [54]. Copyright © 2021, MDPI.
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Figure 2. By continuously releasing earth-alkaline ions from MOFs, bone implants are improved, increasing bone regeneration and biomineralization (A). By enhancing osteoinduction and integration of relevant genes in the presence of specific MOFs (B), and by improving tissue integration and antibacterial effects (C), MOFs facilitate osteoinduction and integration. Reprinted from [140]. Copyright © 2021, Frontiers.
Figure 2. By continuously releasing earth-alkaline ions from MOFs, bone implants are improved, increasing bone regeneration and biomineralization (A). By enhancing osteoinduction and integration of relevant genes in the presence of specific MOFs (B), and by improving tissue integration and antibacterial effects (C), MOFs facilitate osteoinduction and integration. Reprinted from [140]. Copyright © 2021, Frontiers.
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Figure 3. ZIF-8 base Polymeric bone regenerative platform. Reprinted from [172]. Copyright © 2021, Wiley.
Figure 3. ZIF-8 base Polymeric bone regenerative platform. Reprinted from [172]. Copyright © 2021, Wiley.
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Figure 4. LA-AuNR/ZIF-8 and its application for CT imaging-guided tumor treatment. Reprinted from [182]. Copyright © 2020, Wiley.
Figure 4. LA-AuNR/ZIF-8 and its application for CT imaging-guided tumor treatment. Reprinted from [182]. Copyright © 2020, Wiley.
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Table 1. Some of the MOFs and synthesis methods.
Table 1. Some of the MOFs and synthesis methods.
SampleLigandMetalSynthesis MethodRef
ZIF-82methyl imidazole Zn(NO3)2·6H2OMicrowave-assisted[26]
IRMOF-32-amino-1,4-benzene dicarboxylic acidZn(NO3)2·6H2OMicrowave-assisted[27]
UiO-661,4-benzenedicarboxylic acid ZrCl4Conventional solvothermal heating[28]
Fe-MIL-1001,3,5-benzenetricarboxylic acidMetallic iron (Fe0)Conventional solvothermal heating[29]
MOF-51,4-benzenedicarboxylic acidZn(NO3)2·4H2OConventional solvothermal heating[30]
MOF-51,4-benzenedicarboxylic acidZn(NO3)2·4H2OMicrowave-assisted[31]
ZIF-82methyl imidazoleZnOMechanochemical synthesis[32]
ZIF-4ImidazoleZnOMechanochemical synthesis[32]
Al-MIL-1001,3,5-benzenetricarboxylic acidAl(NO3)3·9H2OElectrochemical[33]
Mg-MOF-742,5- 4 dihydroxy-1,4-benzenedicarboxylic acidMg(NO3)·6H2OSonochemical[34]
Cr-MIL-1011,4-benzenedicarboxylic acidCr(NO2)3·9H2OMicrowave-assisted[35]
Table 2. MOF/Matrix applications in biomedical fields and preparation methods.
Table 2. MOF/Matrix applications in biomedical fields and preparation methods.
MOF-TypeMatrix/MOF-Based MaterialPreparation MethodApplicationRef
ZIF-11DimethylformamideElectrospinningIntegrated restoration of the tendon-to-bone interface.[106]
ZIF-8Alumina membranesElectrochemical depositionHomologous-targeted therapeutic applications.[185]
Cobalt-based MOFPLA/PVPElectrospinningAntibacterial applications.[186]
ZIF-8Double-layer PCL/Col membraneElectrospinningOsteogenesis and angiogenesis applications.
Bone regeneration, bone tissue engineering.
[172]
CuBTTriMedical tubingTubing Coating Method/chemical vapor deposition (CVD)Antibacterial coating for medical devices.[187]
ZIF-8PCL- PPCL- TAEG-PDAmelt-blown ElectrospinningDay ligDaylight recyclable antibacterial masks, medical protective clothing, and bactericidal air purification filter application.[188]
ZIF-67Au@PtOne-pot synthesis ultrasound-assisted methodElectrochemical sensing of H2O2 in living cells[189]
MOF-199,MOF-74,MOF-5, MIL-53CottonIn situ cotton-MOF synthesisAntimicrobial activity against nosocomial bacteria[190]
MOF-5AgGreen and mild methodAntibacterial activity[191]
Fe(III) metal-organic frameworksPANElectrospinningTissue engineering investigations[173]
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Valizadeh Harzand, F.; Mousavi Nejad, S.N.; Babapoor, A.; Mousavi, S.M.; Hashemi, S.A.; Gholami, A.; Chiang, W.-H.; Buonomenna, M.G.; Lai, C.W. Recent Advances in Metal-Organic Framework (MOF) Asymmetric Membranes/Composites for Biomedical Applications. Symmetry 2023, 15, 403. https://doi.org/10.3390/sym15020403

AMA Style

Valizadeh Harzand F, Mousavi Nejad SN, Babapoor A, Mousavi SM, Hashemi SA, Gholami A, Chiang W-H, Buonomenna MG, Lai CW. Recent Advances in Metal-Organic Framework (MOF) Asymmetric Membranes/Composites for Biomedical Applications. Symmetry. 2023; 15(2):403. https://doi.org/10.3390/sym15020403

Chicago/Turabian Style

Valizadeh Harzand, Farrokhfar, Seyyed Navid Mousavi Nejad, Aziz Babapoor, Seyyed Mojtaba Mousavi, Seyyed Alireza Hashemi, Ahmad Gholami, Wei-Hung Chiang, Maria Giovanna Buonomenna, and Chin Wei Lai. 2023. "Recent Advances in Metal-Organic Framework (MOF) Asymmetric Membranes/Composites for Biomedical Applications" Symmetry 15, no. 2: 403. https://doi.org/10.3390/sym15020403

APA Style

Valizadeh Harzand, F., Mousavi Nejad, S. N., Babapoor, A., Mousavi, S. M., Hashemi, S. A., Gholami, A., Chiang, W. -H., Buonomenna, M. G., & Lai, C. W. (2023). Recent Advances in Metal-Organic Framework (MOF) Asymmetric Membranes/Composites for Biomedical Applications. Symmetry, 15(2), 403. https://doi.org/10.3390/sym15020403

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