Controlling stem cell fate using cold atmospheric plasma

The stem cell is the foundation of regenerative medicine and tissue engineering. Regulating specific stem cell fate, such as cell attachment, proliferation, differentiation, and even death, undergoes continuous development. Cold atmospheric plasma (CAP), the core technology of plasma medicine, is attracting tremendous attention due to its ability and versatility to manipulate various types of cells, including stem cells. Specifically, the direct and indirect applications of CAP in controlling cell fate are best exemplified by upfront irradiation of the stem cells and modification of the stem cell niche, respectively. This review will describe the recent advances in various CAP strategies, both direct and indirect, and their influence on the fate of healthy and cancer stem cells. Particular emphasis will be placed on the mechanism of connecting the physical and chemical cues carried by the plasma and biological changes presented by the cells, especially at the transcriptomic level. The ultimate goal is to exploit CAP’s potential in regenerative medicine.


Cold atmospheric plasma
In physics, plasma is the so-called fourth state of matter consisting of roughly equal numbers of positively and negatively charged particles. It could be produced typically at very high temperature or at low pressures and acquired either naturally or artificially. Cold atmospheric plasma (CAP) is a partially ionized gas generated at atmospheric pressure and operates under room temperature. This term is sometimes interchangeable with low-temperature plasma (LTP), non-thermal atmospheric plasma (NTAP), and non-equilibrium atmospheric plasma (NAP). Various technologies have been used to generate atmospheric plasma ( Fig. 1), including, but are not limited to, pulsed atmospheric arc (PAA) technology (Fig. 1a) and piezoelectric direct discharge (PDD) technology (Fig. 1b), each with distinct advantages and disadvantages. A detailed comparison between these two technologies and their medical applicability can be found in Table 1.
The key components of CAP include reactive oxygen and nitrogen species (RONS), ions and electrons, and UV photons [1]. The composition and concentration of these components can be tuned and programmed for various applications, especially biomedical ones. In order for CAP to directly influence living recipients, such as cells, the plasma-derived reactive species need to pass various non-biological and biological phases (Fig. 2). Once the atmospheric plasma exits the nozzle and forms a jet, it contains reactive species including H 2 O 2 , O 3 , OH, and NO x . Then, they react with the extracellular fluid to form further reactive species including H 3 O + , NO 2 − , NO 3 − , O 2 − , ONOO − , and OOH − . Neutral diffusion of these RONS finally triggers intracellular events.

Plasma medicine
Plasma medicine is an emerging interdisciplinary field incorporating physics, chemistry, life science, and medicine. It has infiltrated several medical specialties with promising clinical or preclinical potentials [2]. In dermatology, CAP can functionally promote wound healing and cosmetically achieve skin rejuvenation [3]. In microbiology, applications of CAP are exemplified by eradication of microbial biofilm and disinfection of contaminated tissue [4]. In oncology, CAP induces senescence, detachment, apoptosis, and necrosis of tumour cells, demonstrating not only cancer selectivity but also synergy with existing anti-cancer treatment [5].
In addition to these direct plasma treatments on the living tissue, indirect treatments of the biological environment or the niche around the tissues or cells also have attracted extensive research. One example is surface modification of an artificial cell niche, e.g. tissue engineered scaffold or surgical implants (Fig. 3). The other modern example is the plasma-activated medium (PAM) [6]. PAM is inspired by the scientific basis of plasmaliquid interactions in which the reactive chemistry of CAP is transferred and retained prior to a chain of biological events. It can potentially be injected to treat deep cancers or cancers that have spread over large areas. Whether used directly or indirectly, CAP is at the heart of advancing plasma medicine.

Stem cell niche and control of stem cell fate
Stem cells are revolutionizing modern medicine mainly because of their clinical potential to promote the relief, repair, and regrowth response of diseased or damaged tissue. Stem cells exert these regenerative functions through their dynamic interaction with the surrounding microenvironment or the niche in which they reside [7]. The resultant homeostasis determines the fate of stem cells, either survival or death (Fig. 4). Therefore, possible fate options of stem cells include, but are not limited to, attachment (anchoring to the niche), proliferation (selfrenewal), differentiation (lineage specification), and death (active, programmed, or passive, accidental) [8].
Conventional methods of controlling the fate of stem cells are mostly physical and chemical modulation of the  stem cell niche. Adjustable physical and mechanical stimuli include strain, shear stress, matrix rigidity, and topography [9] whereas the tuneable chemical cues include exogenous growth factors, cytokines, and various small molecules [10]. Recent advances in biomaterial research have attempted to partially or entirely replace the stem cell microenvironment with engineered synthetic materials [11]. This has evolved from simple twodimensional (2D) cultures to complex three-dimensional (3D) scaffolds. No matter the approach, as mentioned above, is applied, their effects are considered 'indirect' as they universally target the niche in which stem cells inhabit.
In comparison, CAP is a unique technology to regulate and direct stem cell fate due to its excellent versatility. Not only can CAP indirectly control cell fate by modifying the cell-resident niche, it can also directly influence cell fate by stimulating stem cells in close contact (Fig. 4). This mini-review presents an up-to-date view of the versatility of CAP in controlling stem cell fate, highlighting a novel strategy for regenerative medicine and other applications.   Chemical modification turns PS hydrophilic and supports optimal PSC attachment and long-term self-renewal [12] CAP also endows mechanical improvement of surface, which enhances the adhesion and spreading of MSCs [13] Nitrogen plasma is better than oxygen and air plasma in improving MSCs attachment on gelatin scaffolds [14] CAP modification of PU scaffolds results in differential increments of cell attachment for ESCs and NSCs [15] Nanoscale, rather than microscale, PCL scaffolds attract larger benefits from CAP treatment for MSC adhesion [16] CAP-modified cochlear implant electrode array surface enables colonization of NT-secreting ASCs [17] Promoting stem cell proliferation Either indirect stimulation of cell niche or direct exposure of stem cells Oxygen plasma is better than argon plasma in promoting USSCs proliferation on PS surface [18] CAP-treated gelatin films support better MSCs proliferation, with the optimal hydrophilicity at 27-32°[

19]
Better MSCs proliferation on HA surface is due to faster progression of cell cycle at a transcriptomic level [20] CAP increases ASCs' proliferation by 60% while maintaining cellular stemness, through NO upregulation [21] CAP increases MSCs' and HSCs' proliferation by twofold, and activates relevant gene expression [22] An epigenetic study in which CAP upregulates genes for cytokines, chemokines but downregulates apoptosis [23] Enhancing stem cell attachment using CAP The cell-niche adhesion is crucial for stem cell survival and is dynamically adapted. CAP has recently been proven capable of improving stem cell's attachment to the natural niche and artificial extracellular matrix (ECM). This enhancement is mostly indirect, as CAP modifies the cell-facing niche or ECM (Table 2). Due to its intrinsic mechanism, CAP is well known to introduce chemical changes to the cell culture surface. One of the essential parameters of surface chemistry is surface energy, which is commonly reflected by wettability. Ueda et al. discovered that human pluripotent stem cells (PSCs) adhered poorly to hydrophobic cell culture dishes [12]. However, after turning the surface hydrophilic using CAP treatment, the chemically modified polystyrene (PS) surface could support optimal PSC attachment and long-term self-renewal. Unlike the traditional understanding that CAP solely induces chemical modification, a new theory by Yang et al. suggesting that CAP also alters other surface properties has gained popularity [13]. In their work, CAP treatment of the polymeric substrate also changed the topography and elasticity at the nanoscale level. The predominant mechanical effect enhanced the adhesion and spreading of human mesenchymal stem cells (MSCs) through good focal adhesions.
In addition to the 2D surfaces (e.g. laboratory cell culture system), 3D interfaces (e.g. tissue engineering scaffold) are also conveniently processable using CAP. The extent of enhancement depends on several factors including, but are not limited to, plasma parameters, type of stem cells, and the scale of the scaffold. Firstly, the quantity of bone marrow-derived MSCs (BM-MSCs) attached to CAP-treated gelatin scaffolds was significantly increased compared to untreated specimens [14]. Also, among the three types of working gas used (nitrogen, oxygen, and air), nitrogen plasma provided the best MSC attachment, owing to the N-containing functional groups generated on the surface. Secondly, surface modification of polyurethane (PU) scaffold using CAP led to increased cell attachment [15]. However, the increments were substantially different for human embryonic stem cells (ESCs) and rat postnatal neural stem cells (NSCs). Finally, Sankar et al. subjected polycaprolactone (PCL) fibrous scaffolds with nano-, micro-, and multiscale to CAP treatment. They discovered that the nanofibers demonstrated most remarkable MSC adhesion, spreading, and elongation [16].
The relevant research priority has shifted in the last several years; the emerging applications use genetically modified stem cells. In the study performed by Schendzielorz et al., CAP-assisted hydrophilization of cochlear implant electrode array surfaces enabled firm colonization of human adipose-derived stem cells (ASCs) that are known to secrete neurotrophins [17]. This long-term delivery of neurotrophic factors has profound clinical potential for treating inner ear diseases and neurotology conditions.
In summary, CAP can enhance stem cell attachment to their adjacent environment, mostly by activating the support surfaces. The mechanism of enhanced cell attachment is most likely due to the improved physicochemical changes of the surface, which enhance the expression of adhesion molecules, thus leading to favourable cell attachment.

Promoting stem cell proliferation using CAP
The continued self-renewal and proliferation drives the functionality of stem cells in regenerative medicine. CAP can accelerate the growth of stem cells while maintaining their stemness. This improvement in cell proliferation is achieved through either indirect stimulation of cell-resident niche or direct exposure of stem cells ( Table 2).
On the one hand, CAP can speed up cell growth by activating the cell-niche interface, regardless of the interface material. These materials range from regular cell culture plastic, such as PS [18], bioceramic, such as hydroxyapatite (HA) [20], to ECM-based protein, such as gelatin [19]. However, CAP-induced optimization of the surface chemistry seems to be the central cause for the cellular benefit. Biazar and colleagues demonstrated better proliferation of unrestricted somatic stem cells (USSCs) on the PS surfaces treated with oxygen or argon CAP than on the untreated samples [18]. Also, oxygen plasma provided more significant advantage than argon plasma, not just because of higher ensuing hydrophilicity, but also partially due to topographical changes, i.e. larger surface nano-roughness. In Prasertsung's study, the proliferation of BM-MSCs was significantly higher on the CAP-treated gelatin films than on the unmodified ones [19]. This observation was confirmed by shorter population doubling time and a higher growth rate of cells. Furthermore, the optimal water contact angle, a marker for hydrophilicity and surface energy, was observed at 27 to 32 degrees. Tan et al. concurred with these results and further explored their cellular and genetic mechanism [20]. In order to ascertain the actual growth rate of human MSCs on the HA samples, flow cytometry was used to analyse the dynamic distribution of cell cycle phases. It was suggested that the favourable cell proliferation on plasma-activated surfaces was a result of faster progression of the cell cycle, likely mediated by preferential expression of focal adhesion kinase (FAK). This was one of the first studies revealing CAPregulated biological benefits at a large-scale transcriptomic level.
On the other hand, CAP can enhance cell proliferation by irradiating the stem cells in situ. This possibility was exemplified by a series of step-wise investigations conducted by Park and her team [21][22][23]. In 2016, they showed that helium-based CAP increased proliferation of ASCs by nearly 60% after 3 days of incubation, compared with untreated cells [21]. Plasma-exposed ASCs maintained cellular stemness and their ability to differentiate into adipocytes, without demonstrating cellular senescence. In addition, Akt, ERK1/2, and their downstream NF-κB were all activated in ASCs after plasma exposure. These results collectively showed that nitric oxide (NO) rather than reactive oxygen species (ROS) is responsible for the increased proliferation of ASCs following CAP exposure. In 2019, Park et al. extended their stem cell choice from ASCs to various mesodermderived human adult stem cells [22]. They discovered that CAP increased proliferation of BM-MSCs and haematopoietic stem cells (HSCs) by almost twofold. Furthermore, CAP treatment of these stem cells also activated expression of stem cell-specific surface markers, such as CD44 and CD105, and common pluripotent genes for stemness, such as Oct4, Sox2, and Nanog. This year, the South Korean research group took the relevant work one step further by exploring the epigenetic mechanism by which CAP activates the proliferation of stem cells [23]. After examining the entire genome expression profiles of ASCs, they found that CAP upregulated genes for cytokines, chemokines, and growth factors, but downregulated the genes of intrinsic apoptotic pathways. Once again, plasma-induced epigenetic modifications at both mRNA and protein levels mainly relied on the NO generated from CAP.
In brief summary, CAP can promote stem cell proliferation directly and indirectly. These are realized by either exposing the stem cells to plasma or activating the cellniche interface. The mechanism of accelerated cell proliferation is a result of multilevel events, including faster cell cycle at the cellular level, activated stem cell-specific markers at the protein level, and advantageous deregulation of genes at the transcriptomic level.

Inducing stem cell differentiation using CAP
One of the defining features of stem cells is their capability to differentiate into various types of more specialized cells. This process usually involves a switch from proliferation to specialization, as well as alterations in cellular morphology, function, and fate. CAP can induce and/or boost the lineage-specific differentiation of stem cells into hard tissues or soft tissues, through direct and/ or indirect non-thermal treatment (Fig. 4). Cell differentiation induced by CAP-assisted coating deposition and drug delivery has been discussed elsewhere and, therefore, will not be discussed here.
CAP can induce differentiation of stem cells into hard tissues, such as bone, cartilage, and teeth, mostly through modifying cell-resident, tissue-engineered scaffolds (Table 3). Wang et al. achieved the osteogenic differentiation of BM-MSCs in a series of studies [24][25][26]. Firstly, they surface-modified HA/chitosan scaffolds [24]. A careful investigation found more total and adhesion-mediated protein (e.g. fibronectin and vitronectin) adsorption on the scaffold surfaces, which likely contributed to the enhanced late-stage osteogenic differentiation. Secondly, they combined the micro-scale architecture offered by 3D printed poly(lactic acid) (PLA) scaffolds with the nanoscale roughness and chemical modification provided by CAP, significantly promoting in vitro bone regeneration [25]. Lastly, they studied the cellular infiltration and drug loading in plasma-treated core-shell nanofibers [26]. CAP modification not only increased the pore size of the scaffold resulting in more calcium deposition, but also contributed to significant variations in drug release profiles. Like BM-MSCs, ASCs can also adapt to plasma modification of the scaffolds. Waser-Althaus et al. discovered that the degrees of osteogenic differentiation of ASCs on CAPtreated polyetheretherketone (PEEK) surface depended on plasma power and process gas [27].
Moreover, Griffin et al. examined the role of CAP in guiding ASCs towards both osteogenic and chondrogenic differentiations [28,29]. On the one hand, ASCs could be differentiated preferentially towards osteogenic and chondrogenic lineages on amine (NH 2 ) and carboxyl (COOH) modified scaffolds using CAP, respectively [28]. This chemical group-dependent plasma polymerization method has significant potential for selective stem cell therapy in the regeneration of bone and cartilage. On the other hand, ASCs on the argon CAP-treated polyurethane (PU) scaffolds showed upregulated expression of bone makers (e.g. alkaline phosphatase, collagen I, and osteocalcin) and cartilage markers (e.g. aggrecan and collagen II) [29]. Upon implantation onto the chick chorioallantoic membrane, plasma-treated scaffolds supported higher expression of vascular endothelial growth factor (VEGF) and laminin. These satisfactory in vitro and in vivo results proved CAP to be a simple but efficient tool that can promote ASC skeletal differentiation. Last but not least, CAP can directly induce osteogenic differentiation of stem cells from an unusual source, such as human mesenchymal stem cells isolated from periodontal ligament (PDL-MSCs), expanding its potential for future dental applications [30].
CAP can also induce differentiation of stem cells into forming soft tissues, such as nerves, mostly through directly irradiating NSCs (Table 3). In a series of studies, Xiong et al. achieved neuronal differentiation using murine immortalized neural stem cell line (C17.2-NSCs) and primary rat NSCs in a series of studies [31][32][33]. Initially, they applied microplasma jets (MPJs), a unique form of CAP, to direct in vitro differentiation of NSCs into the neuronal lineage, with longer neurites and cell bodies constituting a mature neuronal network [31,32]. The neuronal differentiation rate was around 75% using this one-step approach, which was much higher compared to the standard chemical method. The differentiated NSCs matured and produced mostly cholinergic and motor neuronal progeny. Their preliminary investigation suggested NO to be the main factor in such fate choice. Then, they deepened the investigation of the mechanism of enhanced and directed differentiation of NSCs by CAP, especially the possible signalling pathways stimulated by NO [33]. The exogenous NO in the plasma and the increased synthesis of intracellular NO by inducible nitric oxide synthase (iNOS) after plasma stimulation could be the underlying contributors. Collectively, the extracellular and intracellular NO downregulated Notch1 and Id2 and upregulated Ngn2 and Ascl1, thereby activating downstream NeuroD expression. As a supplement to the above study, Jang et al. conducted additional upstream and downstream investigations [34]. Specifically, RONS from the plasma phase interacted with reactive species in the extracellular liquid phase to form NO. The extracellular NO reversibly inhibited mitochondrial complex IV, while cytosolic hydrogen peroxide acted as an intracellular messenger to initiate the Trk/Ras/EKR signalling pathway. Thus, this study elucidated the mechanism connecting physicochemical signals from the CAP cascade to the intracellular neuronal differentiation signalling pathway, offering insights into developing of a novel plasma-based treatment for neurological diseases.
Transplantation of pancreatic islet-forming stem cells is a promising therapeutic method for treating diabetes mellitus. However, finding a readily available stem cell source and cell carrier is technically challenging. An interesting work by Nadri et al. combined conjunctivaderived mesenchymal stem cells (CJMSCs) and PCL scaffold [35]. CAP-treated scaffold supported enhanced differentiation of CJMSCs into insulin-producing cells, with significantly higher insulin release in vitro.
In summary, CAP can induce and/or enhance differentiation of stem cells into various tissues, such as bone, cartilage, and nerve. Again, these could be achieved by either direct exposure or indirect modification. The underlying mechanism of CAP-induced cell differentiation is likely far more complicated than those of CAPassisted cell attachment and proliferation. But it should be traced back to the complex recipe of RONS generated using highly tunable but sophisticated plasma Table 3 Inducing and enhancing tissue-specific differentiation from stem cells using CAP. (ASCs adipose-derived stem cells, BM-MSCs bone marrow-derived mesenchymal stem cells, CJMSCs conjunctiva-derived mesenchymal stem cells, MPJs micro-plasma jets, NO nitric oxide, NSCs neural stem cells, PCL polycaprolactone, PDL-MSCs periodontal ligament-isolated mesenchymal stem cells, PEEK polyetheretherketone, PLA poly(lactic acid), PU polyurethane, RONS reactive oxygen and nitrogen species)

Target tissue Stem cells Novelty Ref
Hard tissue Bone BM-MSCs CAP provides surface modification of HA/chitosan scaffolds, leading to favourable protein adsorption, and enhanced osteogenic differentiation [24] CAP proves a quick and inexpensive way to modify nanoscale roughness and chemical composition of 3D printed PLA scaffolds with microscale architecture [25] CAP-modified core-shell nanofibers not only has higher surface pore size and osteoinductivity, but also improved drug release kinetics [26] ASCs Degrees of osteogenic differentiation from ASCs on CAP-treated PEEK surface depend on plasma power and working gas [27] Bone, cartilage ASCs can be differentiated towards osteogenic and chondrogenic lineages on amine-and carboxyl-modified scaffolds using plasma polymerization, respectively [28] Argon plasma-treated PU scaffolds support not only in vitro osteogenesis and chondrogenesis, but also in vivo tissue ingrowth and angiogenesis [29] Teeth PDL-MSCS CAP promotes osteogenic differentiation from PDL-MSCs, although inhibiting cell migration and attenuating cell proliferation [30] Soft tissue Nerve C17.2-NSCs, primary rat NSCs MPJs effectively direct in vitro differentiation of NSCs predominantly into neuronal lineage; higher differentiation efficiency than conventional method [31] A detailed experimental protocol with video demonstration of using CAP to accelerate neuronal differentiation rate in a one-step fashion [32] C17.2-NSCs A gene-level study investigating the mechanism of enhanced and directed differentiation of NSCs by CAP; both extra-and intracellular NO contribute [33] N2a cells CAP induces neural differentiation through crosstalk between specific RONS cascade and Trk/ Ras/ERK signalling pathway [34] Pancreatic islets CJMSCs CAP enhances stem cell differentiation into insulin-producing cells on 3D tissue engineering PCL scaffold; new source for diabetes therapy [35] parameters. Since stem cell attachment, proliferation, and differentiation are a dynamic and seamless chain of events, CAP has the potential to be used as a one-step streamlining tool to facilitate stem cell survival during their fate choices.
Stimulating cancer stem cell death using CAP In contrast to cell survival, controlled cell death could also be desired when determining stem cell fate, especially for cancer stem cells. Cancer stem cells (CSCs) are a small subpopulation of cells within tumours, likely initiating cancer recurrence and metastasis. They are capable of self-renewal, differentiation, and tumourigenicity when transplanted into a live host [36]. CSCs are resistant to conventional treatments, such as chemotherapy and radiotherapy. Therefore, efforts are increasing to develop novel anti-cancer treatment modalities targeting the CSCs. CAP proves a promising candidate for such a clinical purpose. The exertion of anti-CSCs using CAP is genuinely versatile, including direct irradiation of cells with or without adjuvant agent [37], plasma-stimulated macrophages [38], and plasma-activated medium (PAM) [39,40] (Fig. 4).
Although plasma alone can eliminate cancer cells in many preclinical studies using various malignancy models, it has also demonstrated synergy with conventional chemotherapy medications [41]. Adhikari et al. combined CAP with nanotechnology, i.e. silymarin nanoemulsion (SN), for treating melanoma [37]. Cotreatment by SN and CAP increased the cellular toxicity for both melanoma cells and CSCs in a time-dependent manner in vitro and also decreased tumour weight and size in vivo. The p53-mediated apoptosis in these cells was likely activated through inhibition of the HGF/c-MET downstream pathway. Thus, CAP oncotherapy supplemented by SN serves as a new treatment approach for melanoma.
Like direct irradiation of CSCs, indirect CAP treatments, such as co-culture of cancer cells with plasmaactivated macrophages, also provide an equivalent anticancer function. Kaushik et al. demonstrated a tumoursuppressive role for CAP-stimulated macrophages in solid metastatic cancers that are mediated by epithelialmesenchymal transition (EMT) [38]. EMT contributes to many malignant behaviours of cancer cells and CSCs, including anti-apoptotic, motile, invasive, and stem-like features. CAP could induce M1/M2 macrophage polarization, with M1 to a greater extent. These M1polarized macrophages delayed the EMT process in glioma cells, attenuating CSCs maintenance. Therefore, CAP acted as an immune-modulating oncotherapy upregulating pro-inflammatory anti-tumourigenic M1 macrophages.
One of the recent advances of CAP oncotherapy is the usage of PAM, a plasma-treated solution in which the reactive chemistry of gaseous CAP is transferred and retained. Ikeda et al. discovered that PAM selectively induces apoptotic death of cancer cells but not healthy cells. Also, PAM killed both CSCs and non-CSC endometrioid carcinoma and gastric cancer cells [39]. When tested in a mouse xenograft model, PAM also had an anti-cancer effect on CSCs. Therefore, these in vitro and in vivo results supported PAM as a new modality of oncotherapy, targeting various cancer cells, including CSCs. Similar to CSCs, residual undifferentiated human induced PSCs, intended for regenerative medicine and cell transplantation therapy, might also demonstrate tumourigenic potential. Thus, selective elimination of undifferentiated stem cells from a population of differentiated cells before their transplantation is clinically important. Matsumoto et al. achieved this by inducing external oxidative stress using CAP [40]. Undifferentiated PSCs were more sensitive to PAM than PSCderived differentiated cells. Gene expression and protein assay suggested that hydrogen peroxide and various RONS in PAM was one of the mechanisms underlying PAM-induced selective cell death.
In summary, CAP is a multimodal treatment to suppress or eliminate cancer stem cells and stem cells with tumourigenic potential. Due to the versatility of CAP, the mechanism of plasma-induced CSCs elimination is strategy-dependent.

Concluding remarks and future directions
How to control stem cell fate is the key question while maximizing its clinical potential in regenerative medicine and cell transplantation therapy. It is difficult for a single technology to regulate all fate options of stem cells, considering the temporal and spatial complexity of cellular events, such as cell attachment, proliferation, differentiation, and death. Cold atmospheric plasma is a promising strategy due to its excellent versatility. Its direct applications, such as irradiating stem cells in close contact, and its indirect applications, such as modifying stem cell niche, have already gained preclinical interests. However, several challenges remain unsolved before this unique tool can be used widely in clinical applications.
Firstly, extensive research is required to elucidate the mechanism of how physicochemical changes induced by plasma are translated into biological benefits. Secondly, although CAP can regulate individual stages of stem cell fate, controlling the transition from one stage to another and balancing the extent of each stage demands further testing. Lastly, CAP-assisted enhancement in stem cell survival and CAP-induced death in cancer stem cells will need to be cell-specific and tissue-specific, thereby providing a customizable therapy based on the exact clinical requirement.
In summary, the innovative applications of CAP in regulating stem cell fate establishes a new frontier in plasma medicine, likely helping to form a nextgeneration therapy in regenerative medicine.