One of the major limitations of brain organoids is the batch effect. Such inconsistent generation of brain organoids may yield substantial phenotype variance, hindering our understanding of the accurate brain development process or disease underlying mechanisms. This is largely due to the lack of an in vivo like environment in which various factors, such as signaling molecules, regulation of gene expression, and extracellular interaction, work together to control brain development precisely. Indeed, the brain organoid generated through unguided differentiation, which largely depends on the self-patterning and self-organization of PSCs, yields marked variation in structure, cellular diversity, and transcriptomes (6, 13, 14). To reduce the heterogeneity in brain organoid formation, several culture methods and bioengineering approaches have been introduced.

Engineering size and geometry of the embryonic body: The formation of EBs, which have the potential to differentiate into all three germ layers, is mediated by the self-assembly of PSCs and is the first step to generate brain organoids. Previous studies have shown that the size of EBs, thus the initial number of cells to aggregate, matters when it comes to the ectoderm-specific differentiation. In fact, a decreased size of EBs yielded a relatively effective differentiation into the neuroectoderm (15), which may be largely due to a lower surface-area-to-volume ratio. Nowadays, many protocols involve the use of cell-non-adhesive U-/or V-bottom plates to assemble EBs in controlled and uniform manners (Fig. 3A). An alternative strategy may be a physical dissociation of brain organoids to reform them into smaller pieces using the narrow opening of a Pasteur pipette, resulting in a smaller size and consistent formation of a single rosette structure (16). Furthermore, it was shown that not only the size but also the geometry of EBs matters when it comes to brain organoid development (15). The elongated EBs assembled with poly(lactide-co-glycolide) copolymer (PLGA) fiber microfilaments as a scaffold showed an enhanced neuroectoderm lineage specification. Several bioengineering approaches have been introduced to modulate the size and the geometry of EBs, including microwells (17-19) and micropatterned extracellular matrix (20, 21), showing potential to be applied to brain organoid to better guide into the neural fate (Fig. 3A).

Guiding the differentiation of brain organoids: A series of protocols that make use of signaling factors to instruct the organoid differentiation into distinct brain regions have been developed, the so-called ‘guided differentiation.’ In these protocols, small molecules or growth factors, which were previously discovered in model organisms to direct the brain regionalization in vivo (22), are added to the culture media. Such patterning with certain factors delineates the brain organoid development while improving the stochastic and spontaneous differentiation of EBs. The dual SMAD inhibition, which blocks the SMAD pathway, is widely used for neuroectoderm lineage specification, and its prolonged exposure led organoids to have dorsal forebrain characteristics with fidelity (7, 23). Moreover, the additional treatment of SHH, a ventralizing factor determining the ventral to dorsal axis of the brain, produced the ventral forebrain organoid as well (24, 25). Until now, numerous region-specific brain organoid protocols have been introduced, resembling the midbrain (7, 26), striatum (27), hippocampus (8), choroid plexus (28), thalamus (29), hypothalamus (7), hindbrain (30), cerebellum (9), and spinal cord (31).

Guided differentiation demonstrates an increased reproducibility of generating organoids with respect to structures and cell types (32) and further diminishes the batch variation even across different cell lines (33). However, the amount of factors present in the media must be carefully determined because the intrinsic threshold may be programmed differently in individual cell lines (34, 35). The use of external factors is still artificial, and it may often lead to a distorted developmental scenery, potentially misleading our understanding of the intrinsic properties of brain development.

There is a trade-off between the unguided and guided differentiation of brain organoids; the former leads to the emergence of various regions interacting together for development and functionality but suffers from low reproducibility, while the latter produces a region-specific brain organoid with high fidelity but does not resemble the multi-regional brain structure in vivo. The brain is composed of interconnected circuits that span through the various brain regions, and many brain disorders involve malformation or malfunction of those circuits. Therefore, the investigation of the interaction and connectivity among various brain areas is important. In fact, a recent article reported the generation of brain organoids with primordial eye fields, consisting of conserved developmental properties for both tissues and light-responsive functional connectivity (35). Similarly, it is increasingly required to develop advanced culture techniques that could resemble multiple regional identities in a single brain organoid (Fig. 3B).

Assembloid - assembly of organoids with different regional identities: One of these techniques is called the ‘assembloid,’ which means the fusion of organoids representing different brain regions. The assembloid has shown successful assembly of organoids to mimic the inter-regional phenotypes, which could be used in studies for cell migration pattern or functional neural circuitry between particular brain regions (24, 25, 29, 36). In the case of the cortico-striatal, the migration of interneurons from the dorsal to ventral forebrain has been observed with the integrated electrophysiological connectivity, similar to the case of in vivo development (24, 25, 27). Furthermore, other various regional interconnections, such as thalamo-cortical (29). and hypothalamic-pituitary (37), have been successfully modeled via assembloid technology as well. More interestingly, a three-compartment assembly, the so-called cortico-spinal-muscle assembloids (38), was made which showed the functional connection to modulate muscle activity. The significance of the assembloid is that it not only resembles the in vivo-like circuitry but also enhances the neuronal maturation compared to single-region organoids, suggesting that the co-existence of distinct brain regions may be a key to further accelerating the developmental aspects of brain organoids.

Incorporation of an engineered signaling center for regionalization: During brain development, the signaling center has a substantial role in the regionalization of the brain, which mediates the dynamic gradients of morphogens to modulate its subsequent activation of gene expression essential for acquiring distinct positional identities (39). Such signaling centers have been observed along the boundaries of areas with distinct regional signatures in the unguided brain organoid (5), implying that the reproduction of signaling dynamics is critical for determining regional identity within the brain organoid. Indeed, the brain organoid culture that involves establishing morphogen gradients in a developmental context-relevant manner has received increasing attention in recent years. An engineered signaling center incorporated into brain organoids may create the morphogen gradients rather than using signaling molecules that are equally bathed in the culture media. As a result, the brain organoids are able to be spatially structured in response to the signaling gradient, displaying positional information or several distinct brain regions within a single brain organoid.

The simplest technique to introduce an artificial signaling source is to use morphogen-soaked beads, which is a common strategy for manipulating signaling in classical developmental studies (40). The degree of signaling may differ based on the concentration of the signaling molecules absorbed in the beads or the distance from the beads, through which a signaling gradient is established with diffused morphogens. Indeed, a recent study utilized a WNT agonist- and BMP4-soaked beads to successfully direct dorsoventral and anteroposterior topography in brain organoids (41). The spatial topography was determined by the concentration and position of the beads, in which stronger exposure to WNT and BMP yields more anterior/rostral molecular signatures. Such straightforward technology to mimic the signaling center in human brain development showed potential to generate brain organoids with controllable regional specification.

A cell-based signaling center is another strategy, which involves a group of cells that releases signaling factors. In this method, the cells are modified to express the target signal molecules and inserted at one pole of the EBs to further specify the following differentiation. For instance, BMP4 treated aggregates were combined with the untreated larger aggregates while the former acts as the signaling center (42). The signaling induced the expression of the downstream pathway, Wnt and Nodal, at one side and resulted in symmetry breaking of the EB, generating embryonic-like structures with the specified axis. Another example utilized Chd3- and Wnt3A-expressing HEK cells, which enable the spontaneous formation of a cell cluster and induction of the Wnt/β-catenin pathway, respectively (43). The cell cluster was attached to the EB and guided the patterned mesoderm-specification at the attached site. Both studies showed that a cell-based signaling center is a promising technique to recapitulate the biochemical environment throughout development.

Inducible systems for manipulating signaling with high spatiotemporal resolution: The signaling dynamics during brain development are precisely confined in space and time. To mimic such signaling activities in a spatiotemporally-restricted manner, an inducible gene expression system is now utilized on top of a cell-based signaling center. A chemical-inducible system, in which the addition of chemicals such as doxycycline can regulate the expression of the target signaling molecules, has been shown to direct positional identities in brain organoids (44). For this, a cluster of cells with a chemically-indu-cible system for SHH was embedded at one side of the forebrain organoid; its expression was controlled with doxycycline to generate a gradient of SHH. Such asymmetric SHH signals led to the assembly of the dorsoventral forebrain axis in the brain organoid.

Besides chemicals, researchers also attempted to use a light-inducible system instead, which may provide a greater degree of freedom in stimulation with respect to space and time. In a study, the light activable Wnt system was used to drive mesoderm-specific differentiation of hPSCs along with the induction of subpopulation-wise self-organization of cells in a 3D culture (45). Similarly, optical control of curvature in neuroectodermal organoids was reported, indicating the possibility to modulate brain organoid morphogenesis using a light-activable system (46). A more recent study has utilized a light-inducible Cre/Lox recombination system to activate the expression of SHH only in the photo-stimulated area within the neural organoid, resulting in the establishment of the dorsoventral positional identity (47). Possibly, a light-inducible system with high flexibility and reversibility, such as a light-activable CRISPR/Cas9 system (48), may provide a more versatile platform for brain organoid manipulation.

In addition to the aforementioned technologies, the conversion of brain organoid cultures with other bioengineering technologies, such as a microfluidic device (49) or stimuli-responsive hydrogel (50), could further improve brain organoids with multi-regional identities.

The neural extracellular matrix (ECM) has essential roles throughout the stages of the developing brain. Composed primarily of hyaluronic acid (HA), reelin, chondroitin sulfate proteoglycans, link proteins, tenascins, and laminins and with low levels of fibrous proteins, the neural ECM serves as a matrix of biochemical and biophysical cues that regulate the proliferation, differentiation, and migration of cells within the brain (51-53). Therefore, the selection of an appropriate ECM is critical for brain organoid systems because it provides the mechanical and signal-rich context for organoids in vitro culture systems (Fig. 3C).

Naturally derived biomaterials such as Matrigel and laminin are the most widely-used ECM for currently established protocols of cerebral organoid generation (5, 7, 54, 55). In particular, Matrigel is a murine sarcoma-derived reconstituted basement membrane that consists of a complex cocktail of about 2,000 unique proteins (56). However, while it is commercially available and easy to use, it is undefined and inconsistent among different batches and lacks many neural ECM components such as glycoproteins (56-58). Furthermore, studies report that Matrigel may bias neural differentiation by affecting neuronal yield and neurite length compared to other ECM materials (59, 60). Therefore, other natural and synthetically engineered biomaterials have been developed that may better recapitulate the in vivo environment of the developing human brain and provide a defined physical scaffold to guide growth and differentiation.

As alternatives to Matrigel, other naturally-derived biomaterials and cocktails may provide an improved culture environment for brain organoids. In particular, decellularized ECM (dECM) extracted from brain tissue more robustly mimics the neural ECM (61). For example, culturing human neural stem cells in a mixture of decellularized porcine brain ECM and laminin-coated silk scaffolds supplemented with type I collagen not only produces functionally mature neurons and astrocytes but also reduces reactive astrogliogenesis (61). The use of HA or modified HA may also promote differentiation of human pluripotent cells towards neural fates (62-64). Notably, HA-based hydrogels (HA and chitosan in a dextran-sodium chloride solution) can be used to differentiate induced pluripotent stem cells (iPSCs) into NPCs in the absence of any neural induction components (64). Density gradients can also be created using 3D layered hydrogels of methacrylate-modi-fied HA to closely observe neuronal migration and accelerate neuronal maturation (62). Using this approach, a study differentiated human iPSC-derived NPCs within a density gradient and reported migration defects caused by mutations associated with a neurodevelopmental disorder (62). These efforts to incorporate natural biomaterials to guide neuronal culture may be applied to 3D cultures to enhance brain organoid polarization and cortical layer formation.

As opposed to natural biomaterials, the use of synthetic biomaterials as the ECM for brain organoid culture enables for customization and control. The fine-tunable properties of extracellular matrices include ligand concentration, stiffness, degradability, and composition of the neural ECM components such as laminin and fibronectin. For example, modulating concentrations of adhesive ligands such as RGF, YIGSR, and IKVAV in matrices can increase cell survival and improve neuronal morphology and marker expression (65). Furthermore, PEG hydrogels can be modified to optimal stiffness and combined with other ECM components to promote neural differentiation and control organoid size and polarity (66, 67). Efforts through screening experiments to optimize the various parameters of synthetic neural extracellular matrices have demonstrated the potential to customize and “design” matrices best suited for the particular purpose of the brain organoid culture.

In summary, while natural biomaterials may provide improved organoid growth and architecture, they may also have high variability within batches. In contrast, synthetic biomaterials such as PEG provide a reproducible, well-defined microenvironment with the ability to fine-tune various parameters for optimal brain organoid culture. However, they lack the complex network of biochemical cues essential for cell physiology present in the neural ECM and partially in naturally derived biomaterials. To achieve a highly reproducible and optimal growth environment for culturing brain organoids that accurately model neurogenesis, future work should focus on characterizing the individual and interactive contributions of the ECM components and the impacts of the cell-secreted ECM in the designed matrix.

Long-term maintenance of organoids that sufficiently mimic the physiological functions of the postnatal and adult brain is one of the major challenges of organoid technology. Previous studies have shown that the majority of brain organoids can only reach a transcriptomic “age limit” of a second-trimester fetal brain (12, 33, 67). A recent study reported that brain organoids grown for 250 to 300 days could exhibit developmental signatures similar to that of the postnatal brain (11). Regardless, the in vitro culture environment poses many issues regarding organoid maturation and function, such as increased cellular stress and impaired cell-type specification (11, 12). In particular, a lack of even diffusion of oxygen and nutrients is one of the main limiting factors of brain organoid maturation in long-term culture. This eventually causes a necrotic core to build up inside the organoids, thus limiting further size increases. Different approaches have been used to address these issues with diffusion and to enhance the uptake of oxygen and nutrients (Fig. 3D).

A simple technological improvement that can vastly improve nutrient and oxygen absorption is to use spinning bioreactors. 3D printing technology has enabled the design and production of more accessible and cost-efficient spinning bioreactors for use in brain organoid cultures (5, 7, 68). Utilizing miniaturized spinning bioreactors such as SpinΩ produces brain organoids with reduced heterogeneity and may more robustly recapitulate primate-specific features of early neurodevelopment such as the presence of the outer subventricular zone and outer radial glial-like cells (7, 68). Additionally, rotating wall bioreactors may also be used to improve organoid culture, as can be seen in previous studies with retinal organoids (69-71). Incorporating spinning bioreactors in organoid culture can accelerate and improve growth and differentiation by enabling the efficient uptake of oxygen and nutrients.

Slice organoid culture at the air-liquid interface may also substantially enhance the long-term culture and maturation of brain organoids. Most brain organoid models are sphere-like structures, and therefore the diffusion limit is unavoidable without integrating an active circulation system. In contrast, a slice organoid culture at the air-liquid interface involves sectioning the organoid into disks to improve surface diffusion into the interior of the organoid. This method of slice culture at the air-liquid interface reduces cell death within the organoids and enables the expansion of the cortical architecture (72-74). Improved maturation and long-term culture through slice cultures may be particularly useful in modeling late human neurodevelopment, a stage that is critically important to study adult-onset diseases such as ALS/FTD (73).

An alternative to the previous methods of overcoming the diffusion limit is to introduce a perfusion system to the brain organoids through engineering or biological techniques. 3D printing is the basis behind the majority of the engineering methods, whether it be through the printing of biomaterial-derived casts for creating vascular networks (75), or direct printing of vasculature and/or vascular scaffolds (76). It is also possible to directly introduce a perfusion system to brain organoids through biological techniques. In vitro approaches may consist of coculturing brain organoids with endothelial cells (77, 78), using genetic engineering to induce vasculature-like network formation during brain organoid growth (79), or incorporating of the external perfusable device (80-82). One study ectopically expressed human ETS variant 2 (ETV2) in hESCs to induce the formation of vascularized networks during a brain organoid culture (79). Another study combined a human brain tissue-derived dECM and microfluidic systems to recapitulate human brain microenvironment and to improve the nutrient and oxygen supply (80). In vivo approaches consist of grafting brain organoids into a host animal brain, making the host act as a bioreactor to provide a perfusion system (83). Brain organoids transplanted into a host such as a mouse brain not only develop functional vasculature and graft-to-host synaptic connections, but they also show increased cell survival, alleviation of stress pathways, and enhanced cell type specification compared to in vitro culture (12, 83). Regardless of which approach is used, future models of brain organoids may require the incorporation of vascular networks to better emulate the context of the human brain.

Besides the perfusion of oxygen and nutrients, another critical component in the successful maturation of brain organoids is the development of connections among the various cellular subtypes. Current protocols fail to fully capture the complex interactions within the human nervous system, such as the interaction between neuronal and non-neuronal cell subtypes. Various studies have addressed these issues by incorporating missing cell types through small molecule induction or coculture (Fig. 3E).

One important example is the incorporation of microglia, the main source of immune defense in the central nervous system (CNS) and also a regulator of neurodevelopment (84, 85). Because microglia are derived from the mesoderm lineage, most brain organoid protocols that direct differentiation towards neuroectodermal lineages prevent the formation of microglia (86). However, microglia develop innately in brain organoids that are grown in neural organoid media without dual-SMAD inhibitors to enable for mesoderm differentiation (86). Microglia can also be incorporated through coculture, as demonstrated in a recent study that developed a rigorous model enabling the control of the ratio of human microglia in brain organoid culture (87). Incorporating microglia in brain organoid cultures is crucial to produce fully mature brain organoid models to study human-specific aspects of microglia during neurodevelopment.

In vitro organoids also lack the distinct boundaries provided by the membranous layers surrounding the CNS in the human brain. Consisting of the dura, arachnoid, and pia mater, these meningeal layers provide a physical boundary that protects and nourishes brain tissue and acts as a signal-rich niche required for brain cell maturation (88). For example, dorsal forebrain meninges control the timing of neurogenesis by the secretion of retinoic acid (88). Dorsal forebrain meninges interact with radial glial endfeet to influence the cell cycle exit of neuron progenitors, neuron production, and neuroepithelium elongation (88). The physical boundary that the meninges present may also help create and maintain concentration gradients of factors secreted by cortical layer neurons. Reelin, an extracellular matrix glycoprotein secreted by cells of the marginal zone in the developing forebrain, is known to affect neuronal migration and layer formation(89-91). In contrast, the lack of a closed boundary in typical organoid culture conditions, where they are suspended in liquid media, may impede the formation of these concentration gradients. This explains how brain organoids exhibit less complex and spatially distinct cortical layers compared to in vivo brain tissue. Looking forward, a possible approach to mimic the meninges will be to develop biomaterials encasing organoids that provide an appropriate ECM context and closed boundary conditions. Alternatively, another approach will be to coculture meningeal cells derived from neural crest lineages with neural cells to incorporate meninges into brain organoid culture.

Choroid plexus (ChP) and cerebrospinal fluid (CSF) production is another aspect of the meninges-brain interacting environment that needs to be considered in brain organoid cultures. The choroid plexus is found within the pia mater, the innermost layer, where it secretes the nutrient and signaling molecule-rich CSF. It also forms the blood-CSF barrier (B-CSF-B), which, together with the blood-brain barrier (BBB), works as a protective barrier blocking the entry of toxic substances to the CNS. These two main functions of CSF production and blood-CSF barrier formation are vital for brain function, and recent studies have established protocols to model the ChP in vitro through ChP organoids (28, 92). ChP organoids develop the ChP epithelium, express known biomarkers, and produce a CSF-like fluid (28, 92). Importantly, one study showed that their ChP organoids can quantitatively predict the CNS permeability of known molecules (28, 92), demonstrating their potential to be used for drug screening. Furthermore, another study conducted transcriptome analysis on organoids generated by their ChP organoid protocol and found that their ChP organoids showed high transcriptome correlation levels to adult human choroid plexus tissue (28, 92). A notable finding from studies using the ChP organoid model is that SARS-CoV-2 productively infects the ChP compared to other brain regions in organoid models (28, 92, 93). The establishment of 3D ChP models is an exciting development that will provide effective platforms for drug testing and exploration of human-specific disease mechanisms related to CNS protective barriers.

Lastly, brain organoid models represent only a portion of the human central nervous system. However, the nervous system consists of both the peripheral and central nervous systems, and models that accurately represent the complex CNS-PNS interactions have yet to be developed. An exception is the development of neuromuscular organoids (NMO), which generate functional neuromuscular junctions and can contract (94). Further efforts are required to generate rigorous models of the interplay between the CNS and PNS, including the connections along the corticospinal tract. Accurate representation of all parts of the nervous system in brain organoid culture will enable advanced maturation of brain organoids in vitro and provide powerful tools to study the interactions between neuronal and non-neuronal regions during neurogenesis.

In the developing brain, neural stem cells produce diverse types of cells depending on the spatiotemporal context. Lineage is a developmental path connecting the founder cell to its descendant cells. If a single progenitor cell is genetically marked and the mark is transmitted to all the progenies that originated from the founder cell, lineage information about the number of progenies, their location, and their differentiation status could be traced. Construction of lineage trees throughout brain development is beneficial and informative in modeling differentiation processes in vitro, opening the possibility of manipulating cell fates in vivo or identifying the origin of developmental pathologies or cancer (95).

Imaging-based pre-genomic methods such as a tracer dye, cell transplantation, and in toto confocal microscopy have been used to visualize cell lineages (96, 97). However, the temporal and molecular resolution of imaging-based techniques is not sufficient to fully capture the details of complex lineage relationships. Alternatively, lineage information can be extracted from genetic changes such as naturally-occurring somatic mutations or artificially induced genetic mutations (98-101). In this genetic lineage tracing, lineages of individual cells are permanently recorded in the genome. Current strategies that induce and analyze genetic manipulation at a specific locus are classified as dynamic lineage tracing, which can be divided into three approaches: transposon integration, Cre-loxP recombination, and CRISPR-Cas9 editing (102). Transposon-based recording usually inserts a fluorescent reporter cassette whose 3’ UTR carries a short sequence working as a barcode (103-106). Cre-loxP recombination sites or CRISPR-Cas9 target sites can also function as a barcode, usually introduced by homologous recombination or lentiviral transduction (107). After barcode integration and recording, lineage barcodes must be recovered by DNA or mRNA sequencing to construct a lineage tree. When edited sequences are predictable, in situ imaging such as seqFISH (sequential single-molecule fluorescence in situ hybridization) can be used as a visual readout, rather reaching a much higher recovery (108).

Dynamic lineage tracing tools have been actively applied to zebrafish and mouse embryos to monitor cell fate specification during embryogenesis. For instance, CRISPR-based GESTALT (Genome Editing of Synthetic Target Arrays for Lineage Tracing) revealed that few embryonic progenitor cells give rise to each organ of the entire zebrafish by implementing a barcode array consisting of 9 to 12 Cas9 targets (109). Cre-based barcoding called Polylox implemented an artificial recombination locus with ten loxP sites in alternating orientations and demonstrated the multilineage priming of mouse hematopoietic stem cells (HSCs) (107). Such sophistication of the barcode composition was followed by combination with single-cell transcriptomics, for example scGESTALT, becoming capable of incorporating cell state information into differentiation trajectories (110). Single-cell lineage tracing has been assisted by vigorous development of barcode systems such as ScarTrace (111), LINNAEUS (112), MARC1 (113), CellTagging (106), LARRY (105), etc. (For more detail of these technologies, refer to this review (114).

Recently, CHYRON (Cell History Recording by Ordered Insertion) emerged as a cutting-edge lineage recorder based on the CRISPR-Cas9 system (Fig. 4A) (115). Unlike existing methods relying on indel mutations of the barcode, Loveless et al. (2021) minimized deletion and facilitated insertion mutations at the barcode by combining Cas9, a homing guide RNA (hgRNA), and the template-independent DNA polymerase terminal deoxynucleotidyl transferase (TdT). Cas9 targets a specific sequence in the genome under the guard of guide RNA and generates a double-strand break. TdT can insert random nucleotides without the template DNA in repairing this double-strand break. Homing guide RNA, a self-targeting guide RNA, keeps taking Cas9 to the hgRNA-encoding locus so that insertion occurs in the same locus repeatedly. Thus, ordered insertions could be successfully recorded in the barcode and then safely reconstructed as cell population lineages through barcode-sequencing. By engineering Cas9 and TdT to be expressed only under the stimuli-of-interest (e.g., hypoxia), CHYRON could also capture the extent and timing of exposure to the biological stimuli. This technology will provide rich information about brain organoids, investigating lineage relationships between various cell types or cell populations that experienced particular stimuli to what extent.

Yet, the only lineage tracing tool applied to the brain organoid study has been iTracer (Fig. 4B) (116). Previous approaches were based on computational analyses, using the Monocle package, to construct pseudo-time trajectories from single-cell RNA-seq data in brain organoids (33, 117-120). iTracer is based on the sleeping beauty transposon system, integrating the 3’-barcoded GFP and the barcode-targeting guide RNA into multiple genomic loci. Cerebral organoids were generated with iTracer iPSCs containing an inducible Cas9 cassette. Cas9 expression is induced by introducing doxycycline at different developmental time points, resulting in genetic scars at the barcode. Editing may mirror versatile biological responses by modulating scar-inducing signals. Cells expressing lineage barcodes were subjected to lineage-coupled single-cell and spatial transcriptomics, which were both the first use in the brain organoid field. Transcriptome analyses revealed differentiation and regionalization trajectories of the iPSC clones by connecting different time points and distinct regions. Still, there are some technological limitations left to be solved, including transgene silencing, single-cell dropout, and sampling depth, for the sake of comprehensive lineage reconstruction from the iTracer system.

He et al. (2020) emphasized how powerful it will be to use the iTracer system together with 4D light-sheet microscopy, which is one of the breakthrough technologies that can secure temporal resolution of imaging-based lineage tracing. They demonstrated long-term live imaging of developing cerebral organoids by tracking individual fluorescently-tagged nuclei and observed local amplification of the initial clones. This concept is in line with ‘cell tracking,’ which follows each developing cell in real-time and draws complete lineage trees to monitor spatiotemporal developmental dynamics (Fig. 4C) (121).

By identifying single stem cell lineages during cell fate specification, we can decipher complicated developmental processes such as discovering unique and transient cell types. Brain organoids came about as a potent in vitro model that can provide direct evidence in the investigation of the differentiation dynamics in human brain development. Lineage-coupled single-cell and spatial transcriptomics along with long-term time-lapse live imaging of barcoded organoids provide an unprecedented opportunity to overcome doubts in transcriptomic and spatial resemblance to the real human brain. As in human colon and retinal organoids, analyzing lineage relationships of diverse cell populations will contribute to the understanding of developmental effects of mutations and the modeling of cancer progression (122-125).

As we discussed, brain organoids have the potential to fill the gap between human monolayer cell culture models and animal models such as rodents. Although effective and accurate electrophysiological approaches have been developed for two-dimensional cultures, functional analysis of electrical activities of brain organoids is limited (126). Classical patch-clamp electrophysiology enables the recording of a single cell with a high temporal resolution but has difficulties grasping the complex activity of a group of cells due to its invasive and laborious nature. Thus, recent advances in the past several years to overcome limitations posed by the three-dimensional structure of brain organoids will be discussed here.

The classical methods for measuring electrophysiological activities, such as patch-clamp, offer high temporal resolution yet suffer from low spatial resolution to record whole-organoid activity (23). The imaging-based methods, such as calcium imaging, may provide larger-scale recording but lack of high temporal resolution (5). Lastly, microelectrode arrays (MEAs) (72) can provide both network-scale and relatively high temporal resolution but currently do not support the recording in three-dimension, which is in increasing need to accurately analyze electrophysiology in brain organoid.

Calcium imaging has been used to monitor neuronal activities at the single-cell level and their synchronization but suffered from its limited temporal resolution (25, 130). The problematic penetration depth is expected to be improved by the development of two-photon and light-sheet microscopy, expanding the region-of-interest from the organoid surfaces to deeper layers (127-129). In comparison, whole-cell patch-clamp recording can measure the detailed properties of one neuron at a time in millisecond temporal resolution while lacking network connectivity (23). Thus, these two techniques can be used together comple-mentarily. For example, Xiang et al. (2017) confirmed the neuronal activity and connectivity in fused MGE (medial ganglionic eminence)-cortical organoids (25).

Similar to calcium imaging that uses genetically encoded calcium indicators (GECIs), voltage imaging that uses genetically encoded voltage indicators (GEVIs) was developed as another option. Originally, voltage-sensitive dyes have been used because of their good speed and sensitivity but it’s hard to restrict them to specific cell populations (131, 132). Hochbaum et al. (2014) solved this problem by applying spectrally orthogonal GEVI and an optogenetic actuator, which is called all-optical electrophysiology that can visualize membrane voltage changes upon optical stimulation (Fig. 4D) (133). Recently, a synthetic NIR voltage reporter was invented by Puppo et al. (2021) for easy and safe delivery without triggering any bias (134). However, the technologies mentioned so far are incompatible with long-term stable measurements. The accuracy and resolution of calcium and voltage imaging are disrupted by the decaying dynamics of the indicators and increasing noise as the neuronal firing rate increases. Patch-clamp recording lacks long-term reliability due to difficulties in the maintenance of the subject, which is also confined to organoid edges or sliced cultures (101). This is where bioelectronics can have a big part, enabling noninvasive access to electrophysiological information whenever we want (Fig. 4E).

One of the most frequently used devices in electrophysiological measurements of brain organoids is a microelectrode array (MEA), which is a neural interface in which interconnected microelectrodes record electric signals from neighboring cells. 2D MEAs have been widely applied to the analysis of brain organoids, due to their good temporal and network resolution and larger data scale. For instance, Giandomenico et al. (2019) confirmed the functionality of long-range neural circuits and the connection between several regions within the organoid (72). Trujillo et al. (2019) conducted a comparison study that examined the electrical activities of developing forebrain organoids by weekly MEA recordings for 10 months and EEG features of preterm infants, suggesting that the evolution of neural networks in the developing organoids resembles that of preterm infants to some extent (135). In combination with single-cell RNA-seq and immunohisto-chemistry data, Fair et al. (2020) elucidated the electrophysiological maturation of forebrain organoids correlated with transcriptomic and morphological features (136).

Despite the progress that 2D MEAs have made, their planar structure cannot record the inner part of 3D brain organoids. Therefore, 3D MEAs were developed by folding the electrode array into a hinged form so that the vertically aligned part of the probes can monitor the inner part as well. Soscia et al. (2020) developed flexible MEA probes using polyimide layers that can be naturally positioned to the inner part of the organoid by seeding the cells (e.g., iPSC-derived neurons) embedded in conditioned ECM on the probes and then growing the cells to establish a 3D structure around the probes (137). There are a lot of improvements being made, such as implementing high-density MEAs that enable single-cell analysis and 3D multifunctional MEAs that can both monitor and modulate neural activities in real time (138-142). However, MEAs still have some problems including their limited contact with the organoids and the inconvenience arising from organoid culture protocols that require frequent media exchange. Shim et al. (2020) recently fabricated a 3D dual-MEA to overcome these problems by sandwiching brain organoids between two stretchable polyimide layers, in which high stretchability was engineered with serpentine interconnects (143).

Another approach in bioelectronics has been proposed to outperform MEA technologies. By enhancing the flexibility of polyimide arrays to softly envelop the entire brain organoids, Park et al. (2021) designed a 3D flexible neural interface precisely matching the shape of cortical spheroids; therefore, gold microelectrodes are positioned proximal to the surface of the organoids (144). They named this 3D multifunctional mesoscale framework (3D MMF), where additional functional elements such as an optical device, thermal actuator, or electrochemical oxygen sensor enable simultaneous stimulation and measurement. Likewise, many different materials and electrode designs have been engineered to improve biocompatibility, such as printing MEAs on soft substrates mechanically similar to brain tissue and manufacturing electrodes using titanium nitride or ruthenium oxide (145-147). Furthermore, mesh nanoelectronics expedites the electrical characterization of organoids throughout the entire developmental time course. Li et al. (2019) first demonstrated ‘cyborg organoids,’ by integrating a stretchable layer containing electrodes in a mesh structure to a cardiomyocyte monolayer prepared for a cardiac organoid generation (148). During the organoid genesis, electrodes could be evenly spaced across the entire organoid, and electrophysiological measurements could be conducted all the time in single-cell resolution. Cyborg brain organoids were implemented into the brain organoid system to enable long-term non-invasive recording of neuronal activities (149). These approaches are part of bioinspired flexible electronics, enabling the safe establishment of neural interfaces and chronic recording from the entire organoid (150). This also includes the engineering of nanoelectronic scaffold (nanoES), invented by Tian et al. (2012), which provides structural and bioactive support for better mimicry of tissue organization and simultaneous monitoring of electrical activity (151). Moreover, neuron-like electronics (NeuE) can be applied to brain organoids (152), incorporating neural probes that resemble neurons in size, shape, and mechanical properties into neural tissues for high-resolution electrophysiological recording.

Long-term stable recording of brain organoid electrophysiology became a reality thanks to the development of various bioelectronic interfaces. However, some issues still remain in common. First, spatial mapping of electrophysiological activity is yet blurred. Recently, Miccoli et al. (2019) visualized the spatial distribution of electrical activity in neuronal monolayer culture with a 2D multimodal complementary metal-oxide-semiconductor (CMOS)-based MEA (153). This high-resolution MEA measured the impedance of each unit during the electrical recording. Impedance variation was calculated and used as an indicator of electrical activity, later constructed as an electrical map, demonstrating label-free, real-time and non-invasive visualization of the electrical activity in a neuronal network. Similar approaches in the 3D MEAs may clarify this map in the brain organoids. Second, cell-type specificity is lost in bioelectronic platforms. Li et al. (2021) recently succeeded to integrate single-cell electrophysiology with in situ sequencing, proposing in situ electro-seq (154). Utilizing the cyborg organoid platform, they labeled each electrode in the flexible mesh electronics with a unique fluorescent electronic barcode (E-barcode) by photolithography to represent the location of the electrode across the organoid. Whole organoid-electronics hybrid was fixed after electrical recording and cleared for in situ sequencing, leading to the explication of spatially-resolved RNA expression at the single-cell level. Optogenetics may enrich the knowledge in this field by manipulating the electrical activity of specific neurons (155, 156). Chemo-genetics, represented by DREADDs (designer receptor exclusively activated by designer drugs), may also enable the functional segregation of neuronal subtypes in brain organoids (157, 158). Taken together, thorough and systemic electrical characterization of brain organoids will contribute to our understanding of the process of neural circuitry formation in human brain development and brain disorders.