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Simulating traumatic brain injury in vitro: developing high throughput models to test biomaterial based therapies

Basit, Raja Haseeb1,2; Wiseman, Jessica2,4; Chowdhury, Farhana3,4; Chari, Divya Maitreyi4,*

Author Information
doi: 10.4103/1673-5374.346465
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Abstract

Introduction

The total global annual burden of traumatic brain injuries (TBIs) is an estimated US $400 billion (van Dijick et al., 2019). Such injuries can arise from blunt (closed) or penetrating trauma (open/pTBI). These are prevalent in civilian/military personnel in areas of a high incidence of terrorism/violence and are associated with the worst clinical outcome in head injury cases. An injury track created by a foreign body (e.g. fragments or gunshot rounds) causes cavitation, shearing, and compression of nerve fibers and blood vessels, with damage to neurons and glia including myelin damage (Oehmichen et al., 2001). There is focal and diffuse neuronal apoptosis/necrosis, during the primary and secondary injury phases, and cellular debris leads to a high concentration of damage-associated molecular patterns. Microglial infiltration of lesions and release of pro-inflammatory cytokines such as interferon-γ and tumor necrosis factor-α drive acute inflammation (Lively et al., 2018). Oligodendrocyte precursor cells and fibroblasts infiltrate the lesion and proliferate with early (within 24 hours) astrocyte activation. The latter extend palisading processes into the lesion sealing the lesion core which contains cellular debris and molecules inhibitory to neurite outgrowth (such as myelin-associated glycoprotein and oligodendrocyte myelin glycoprotein; Filbin et al., 2003). The subsequent failure of regeneration, chronic inflammation, and atrophy are suggested to underpin the poor clinical outcomes post-pTBI. Treatments have been refined over the years and include early debridement with or without craniotomy and supportive therapies such as anti-seizure medications, antibiotics, and intracranial pressure monitoring (Vakil et al., 2017). Such injuries have significant contamination (approximately 43% infection risk) so early broad-spectrum antibiotics use is key. Cerebrospinal fluid leaks are also encountered increasing contamination risk and requiring dural repair. Long-term management focuses on neurorehabilitation requiring multidisciplinary input including teams from neurosurgery, neurology, physiotherapy, speech, and language therapy, in addition to input from allied specialties depending on the systemic manifestation of clinical injury. Current clinical interventions are therefore supportive and truly regenerative/neuroprotective therapies post-injury do not exist, remaining a key goal for research in regenerative neurology.

In this context, the use of implantable biomaterials as therapeutic scaffolds to promote repair has been a major recent advance in regenerative medicine. Such matrices can be prepared from many different biomolecules, including numerous proteins/polysaccharides. These are highly versatile for neurological injuries, given their extracellular matrix-like structures, high porosity, and ease of fluid/nutrient movement, supporting the 3-D growth of cells including axon/blood vessel ingrowth from ‘host’ tissue into implants (Weightman et al., 2014). They offer benefits as drug/cell delivery devices enabling local, controlled release of a therapeutic and, significantly, the ability to modify the post-injury extracellular microenvironment. For example, there is evidence that biomaterials in situ reduce the expression of mRNA for inflammatory- and glial cell scarring-related genes in injury sites, limit immune cell infiltration, attenuate glial scarring, and reduce cystic cavitation post-injury (Krings et al., 2016; Basit et al., 2021). They have tissue-mimetic mechanical properties, relatively rapid biodegradability (within about 3 months allowing for gradual replacement with nascent tissue), and mouldability for surgical delivery (Chen et al., 2019). Using a pTBI model, Hou et al. (2005) found neurite outgrowth and angiogenesis into hyaluronic acid hydrogels modified with laminin, which had been implanted into the cortices of Sprague-Dawley rats, with decreased glial fibrillary acidic protein upregulation in areas of biomaterial contact. Similarly, Chen et al. (2019) demonstrated reduced infiltration of activated microglia in a collagen-glycosaminoglycan matrix hydrogel implanted into a surgical rat brain injury, with a modified inflammatory signaling environment (interleukin-6, tumor necrosis factor-α, and interleukin-10 expression).

Such research is encouraging and requires suitable preclinical experimental models to identify and test the most promising interventions for future medicine. Given the pathological complexity of pTBI, this does present a highly challenging goal. An appropriate model, in our view, should offer the following features: wide availability across experimental facilities; facile methods to facilitate researcher training, inexpensive, high throughput nature to test multiple experimental conditions simultaneously, patho-mimicry to accurately simulate in vivo pTBI; compatibility with a range of microscopic methods (including, light, fluorescence, time-lapse and electron microscopy); and applicability to a wide range of species including genetically modified animals. Importantly, any model should provide an ethically viable approach in line with the 3 R’s (Reduction, Replacement, and Refinement) of animal experimentation. Here, we review the literature on experimental models of pTBI and their utility for the study of biomaterial based therapeutics.

Search Strategy and Selection Criteria

All years were chosen in the search. These searches were performed between June and December 2021 using the PubMed and Web of Science databases. Broad search terms such as traumatic brain injury, penetrating traumatic brain injury, in vitro models, neurological injury, 3D models, biomaterials, organoids, organotypic, and neuronal culture were used in various combinations.

Models of Penetrating Traumatic Brain Injury Vary in Complexity

A variety of pTBI models have been deployed in experimental neurology. Large animal models typically involve researchers introducing penetrating brain lesions through gunshot/stab wounds in anesthetized sheep or monkeys (Finnie et al., 1993), with the evaluation of gross pTBI pathology. However, the considerable ethical implications and rarity in procuring such animals within common research facilities have resulted in these models largely falling out of favor. Small animal rodent models deemed ‘less sentient’ have been developed (such as a penetrating ballistic-like brain injury -rifle pellet injury) (Plantman et al., 2015). These are relatively inexpensive (versus live animal models), widely available in research facilities and offer ease of handling and standardized neurological/behavioral tests to evaluate the regenerative benefits of any therapy. However, all live animal models of neurological injury require extensive training and monitoring, given that these are some of the most invasive models in experimental research. As such, there is a need for stringent regulation of such work, often requiring experimental licenses and specialist infrastructure and staff for the housing and care of animals. These models are inherently lower throughput, and technically challenging compared to in vitro alternatives. The significant ethical implications surrounding live animal use in medical research also continue to be a matter of extensive public and scientific debate.

In vitro organotypic (organ-like) brain slices provide a 3D alternative. These offer the controllable environment of in vitro preparations providing an ‘interface’ between high throughput screening and pre-clinical animal models. Neural cytoarchitecture, cell inter-relationships, a vascular network, and the extracellular matrix are maintained in such tissue, allowing for neural plasticity, cell migration, and axonal regeneration to be easily examined. Rodents, including transgenic models and higher species (rabbits, pigs, dogs, and humans) can be used as donor sources, and the application of advanced microscopy, electrophysiology, molecular and genomic methods to these models has greatly expanded their practical utility, including for the study of TBI. Our lab previously developed an in vitro spinal cord organotypic slice culture model with a penetrating (transecting) injury (Weightman et al., 2014). We showed that the model replicates stereotypical pathological responses seen after neurological injury in vivo, namely: (a) reactive gliosis with astrocytes forming a scar, a major barrier to nerve fiber regeneration; (b) gradual infiltration of lesions by microglia; and (c) decreasing nerve fiber outgrowth with increasing donor tissue age, in conjunction with glial scarring and reactive microgliosis in lesions. Whilst offering significant patho-mimicry, such models are moderate throughput at best, and can be technically challenging to establish and maintain.

The most basic in vitro models use immortalized cell lines, which are robust, inexpensive, and widely available but are often resistant to cell death and prone to cryptic contamination. These offer major advantages in terms of a more facile and controlled yet high throughput approach, for multiple experimental manipulations or measurements. Systems offering greater complexity have been developed from dissociated cortices which typically take the form of monolayer cultures. For example, an astrocyte scratch wound model (using primary cultures of astrocytes) has been used to simulate traumatic neural injury with glial fibrillary acidic protein upregulation, hypertrophy of reactive astrocytes, and injury triggered calcium waves observed in the injury foci (Gao et al., 2013). In general, such models are high-throughput, facile, inexpensive, and widely available and contribute significantly to the reduction and refinement of animal experimentation, with far less ethical implications than in vivo systems. However, the drive for reductionism has often meant these models are overly simplistic, not containing the major neural cell types (notably the immune cells) to simulate the complex pathological responses observed in neural pathology. Therefore advanced in vitro systems are still urgently needed. Table 1 shows a comparison of in vitro neural cell models potentially adaptable to injury mechanisms.

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Table 1:
Possible in vitro systems for modelling brain tissue, traumatic injury mechanisms and biomaterial interventions – advantages and disadvantages, arranged from highest complexity to least complexity

Developing a New Multicellular Model of Penetrating Traumatic Brain Injury In Vitro

We recently developed a reliable, technically simple, and high throughput pTBI model, using rodent cortices, to evaluate the effects of implantation of biomaterial scaffolds on neural cells (unpublished data). The model is a variant of a widely used mixed glial culture system and contains the two major immunocompetent neural cell types in the central nervous system- namely the astrocytes and microglia in addition to oligodendrocyte precursor cells (Basit et al., 2021). We found evidence of both microglial invasion of lesions and reactive astrogliosis in peri-lesional astrocytes (hypertrophic palisading astrocytes at the lesion edge) with glial scarring responses and glial fibrillary acidic protein upregulation at the lesion edge. Implantation of a surgical grade matrix Duragen Plus™ into the lesion resulted in microglial and astrocytic infiltration into the biomaterial. Therefore, the model broadly replicates in vivo features of TBI pathology. It also highlights the need for experimental models that can predict the responses of major neuroglial phenotypes to introduced biomaterials. This is of high importance given the critical role these cells play in determining the intra-central nervous system fate of therapeutic scaffold materials. Astrocytes, for example, can dramatically remodel biomaterials, and fibrillar contraction in these cells alters their biomechanical properties. Microglia- the intrinsic immune cells of the central nervous system, have roles in biomaterial clearance and digestion which impacts their biodegradability and potential toxicity of the materials. This in turn exerts a critical impact on the pro-regenerative properties of the implant. Accordingly, we consider the model can be used to investigate materials varying in their chemistry, stiffness, and porosity to identify those with the most promise prior to preclinical testing. A major limitation of the model is the lack of a neuronal component, meaning axonal outgrowth– a key aspect of neuroregeneration, cannot be assessed. To address this, we have recently developed an advanced version of the multi-glial model using a simple chemical switch to maintain the neural cells in vitro (unpublished data; Figure 1). Briefly, cortices from neonatal rodents were extracted and enzymatically dissociated, using a specialized chemical medium found to support the growth of both neurons and all major glial subpopulations, including the microglia. In terms of the cellular constitution, the culture consists of approximately 50% neurons with glial populations making up the remaining cells. 70% of the neurons were found to be gamma-aminobutyric acid (GABA) positive; the remaining neurons were not found to be glutamatergic, in our hands and their identity, remains to be established (Figure 2).

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Figure 1:
The schematic depicts cellular responses of multiple neural cell types to a penetrating lesion in vitro, in the experimental model developed by our group.Here, microglia infiltrate the intralesional space, with axonal outgrowth and hypertrophic palisading astrocytic processes in the lesion core. Biomaterial scaffolds (and other materials) can be introduced into the lesion gap to evaluate their pro-regenerative properties. CNS: Central neural system.
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Figure 2:
Characterization of the multicellular cortical model.Representative fluorescent micrographs showing the cellular constitution of the new mixed cortical culture containing neurons (Tuj-1) and astrocytes (GFAP) (A); and neurons (Tuj-1) and oligodendrocytes (MBP) (B). Staining of constituent neurons with GABA is shown in (C). Nuclei shown stained with DAPI. Graphical representation of the relative cell proportions within the culture shown in (D). DAPI: 4’,6-Diamidino-2-phenylindole; GABA: gamma-aminobutyric acid; GFAP: glial fibrillary acidic protein; MBP: myelin basic protein. Unpublished data.

The model is pathomimetic, inexpensive, high throughput and contains all of the central nervous system cell types. Penetrating lesions can easily be induced within the culture system, and potential therapeutic interventions such as biomaterial implantation or nanoparticle delivery assessed. There are very few reports that focus on the response of all major neural cell types simultaneously and thereby overlook the multi-dimensional cellular response, despite the known importance of all glial and neuronal cell functions in neuroinflammation, therapeutic assessment, and regeneration. Our model offers significant benefits in this regard. All the cell types were homogeneously distributed throughout the cultures allowing sufficient evaluation of the multiple cell responses to injury. The potential to study the therapeutic impact on all major neural cell types simultaneously has significant benefits when considering a high throughput, facile brain tissue model. For example, Goshi et al. (2020) reported that astrocytes and neurons respond differently to neuroinflammatory stimulators and neurotrauma in the presence of microglia. This reinforces the importance of the immune component in mixed neural cultures, and in turn the significance of the micro-dynamics between all neural cell types. Accordingly, we consider our new model offers a versatile adaptable platform for the study of a range of TBI mechanisms, therapeutics, and drug testing within the neuro-regenerative field, using a simple but scalable system. This robust brain tissue-modeling platform would be adaptable to multiple injury mechanisms including weight drop contusions, glutamate-induced excitotoxicity, lipopolysaccharide stimulated neuroinflammation and hypoxia, to understand concurrently the response of all brain cell types.

Interestingly, we have found that the model can be adapted into a 3D format using cell seeding into a hydrogel matrix, thereby expanding its utility to study more complex pTBI, such as pellet simulating ballistic injuries or crush injuries through weight drop (unpublished data). Further refinements in the future could include the addition of endothelial cells to simulate the blood-brain barrier, and the inclusion of peripheral immune cells, to enhance the pathomimetic potential of the approach. A more detailed assessment of the lesion pathology is also needed, for example, the use of proteomic methods to study the spatial and temporal molecular expression profiles in the injuries (for comparison to in vivo data), or an assessment of the extent of myelination/demyelination in the injuries, including use of high-resolution electron microscopy. Whilst such pTBI models can never outright replace preclinical testing, we believe they are of high value for the developmental testing and identification of promising biomaterial scaffold-based therapeutic interventions. Their versatility also allows them to be deployed to test other promising neuro therapies such as novel nano-pharmaceuticals and glial scar attenuation/immunomodulatory treatments.

Acknowledgments:We thank the EPSRC and NHS bursaries whose generous support enabled this work.

Author contributions:RHB, JW, DMC conceived, wrote and edited the manuscript, and generated the Table and Figure 1. FC provided the experimental data (unpublished) shown in Figure 2.

Conflicts of interest:The authors declare no conflicts of interest.

C-Editors: Zhao M, Liu WJ, Wang Lu; T-Editor: Jia Y

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Additional file

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      Keywords:

      astroglial scar; biomaterial; cortical culture; in vitro model; microglial infiltration; multicellular model; penetrating injury; scaffold; traumatic brain injury

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