The most long-lived bone cells, osteocytes are known as the master regulator of bone formation and resorption (Bonewald 2011). The mechanosensory role of osteocytes underlies well-balanced bone homeostasis, which is primarily influenced by matrix strain and fluid shear stress (Weinbaum et al., 1994; Han et al., 2004; Robling and Turner 2009; Wittkowske et al., 2016). Through mechanotransduction processes, osteocytes are able to transduce extracellular signals to elicit cellular responses by initiating different signaling pathways accordingly to bring functional responses. The dysregulation of osteocyte behavior can lead to reduced bone mass and bone fragility observed in osteoporotic patients. For this reason, osteocyte-induced mechanotransduction has been studied extensively, however, the exact mechanisms and signaling pathways are not fully understood. Here we highlight the crucial role of osteocytes in bone homeostasis, including regulation of the overall bone remodeling process, perilacunar/canalicular remodeling, and systemic regulatory roles on other tissues such as the kidney, parathyroid, and heart (Dallas et al., 2013; Creecy et al., 2021). Furthermore, we summarize the osteocyte mechanosensors and the current state of mechanoresponsive signaling pathways identified in osteocytes with therapeutic implications. To achieve this, we present both in vivo and in vitro approaches that have been employed to understand the complex regulatory processes that underly osteocytes’ quintessential mechanosensory role in bone.

Bone is a weight-bearing tissue, which supports locomotion, protects soft tissue, and is also known as a reservoir for calcium and phosphate (Bellido 2014; Florencio-Silva et al., 2015). Bones are composed of both organic matrix, comprising of largely type I collagen (90%), with the remaining protein component including osteocalcin, osteonectin, osteopontin, fibronectin, and thrombospondin-2 (Sroga and Vashishth 2012), as well as inorganic matrix minerals, mainly comprised of hydroxyapatite (Ca₅(PO₄)₃OH) but also including small amounts of potassium, magnesium, sodium, strontium, and calcium salts (Lin et al., 2020). The formation of the bone matrix is initiated by the collagen assembly followed by hydroxyapatite deposition and tuned by minerals and amino acids of non-collagenous proteins (Young 2003; Tavafoghi and Cerruti 2016). The balance of mineral content is important and directly relates to mechanical strength (Faibish et al., 2006). For example, bones become brittle when mineral content is too high and less load-bearing if the mineral content is too low. This mineralized tissue undergoes remodeling to maintain its integrity and is tightly regulated by a precise balance of bone formation and resorption under the control of local and systemic factors, such as cytokines, hormones, and mechanical stimulation (Florencio-Silva et al., 2015). This complex process is a cycle of localized bone resorption to remove old or damaged bone followed by a longer phase of bone formation, both in an equilibrium to maintain healthy bone. The imbalance of this regulation often leads to bone diseases such as osteoporosis and is caused by a variety of factors such as aging, menopause, drugs, and changes in physical activity (Feng and McDonald 2011). Imbalance can also stem from genetic mutations, leading to bone overgrowth disorders due to defective signaling pathways that change the equilibrium resulting in van Buchem disease and sclerosteosis (Balemans et al., 1999; Sebastian and Loots 2018).

Bone is a rigid and load-bearing tissue designed to sustain high mechanical loads during exercise (Benedetti et al., 2018). There are two types of bone tissue, the cortical and trabecular bone, which have the same cells and matrix but differ in structural-functional roles (Clarke 2008). Cortical bones are more calcified and hard, and carry out the role of providing mechanical stability and form a protective layer for the internal cavity (Boskey and Coleman 2010). In comparison, the trabecular bones only contain 1/3 of calcified bone compared to the cortical ones and are mainly involved in metabolic as well as biomechanical functions (Clarke 2008). The composition of the bone matrix is important for fracture resistance, which largely depends on the geometric (size and shape) and material properties (mineral content and composition) (Osterhoff et al., 2016). Bones constantly experience mechanical forces created by various stimuli including fluid flow shear stress, hydrostatic pressure, and direct cellular deformation induced by gravitational forces as a weight-bearing tissue and loading-induced stimuli such as compressive force. The calcified bone matrix may induce micro-deformation with a maximum of 3% strain changes (Hart et al., 2017). The matrix deformation during locomotion is between 0.04 and 0.3% but hardly exceeds 0.1%. Surprisingly in vitro studies need to apply more than 10 times this mechanical stimulation to observe osteocyte responses, otherwise, the strain amplification at the cellular level is too small to initiate mechanotransduction pathways (Rubin and Lanyon 1984; Fritton et al., 2000). These in vitro forces applied back at the tissue level would cause a fracture (Burr et al., 1996; You et al., 2000; Wang et al., 2015). This difference has to be taken into consideration to more accurately capture the differences between in vivo and in vitro systems and facilitate the accurate interpretation of a translational approach. The externally applied force is transduced by highly mechanosensitive osteocytes that coordinate the effector cells, bone-forming osteoblasts, and bone-resorbing osteoclasts demonstrating the skeletal adaptation response of mechanical cues into biochemical signals (Bonewald 2011; Schaffler and Kennedy 2012). The above highlights the need to understand the mechanisms underlying osteocyte’s important regulatory role in bone homeostasis.

Osteocytes are the most abundant (∼95%) bone cells, which reside in the hard bone matrix (Hellmich and Ulm 2002; Bonewald 2011). Osteocytes are a terminally differentiated post-mitotic cell type from the osteogenic lineage, derived from mesenchymal stem cell progenitors (Pittenger et al., 1999; Day et al., 2005; Gaur et al., 2005; Sudo et al., 2007). Mesenchymal stem cell differentiation leads to osteoblasts, and a subpopulation is known to terminally differentiate into osteocytes that are individually embedded within small chambers called lacunae (Palumbo et al., 1990; Candeliere et al., 2001). After the differentiation process, the most striking morphological change of mature osteocytes is the development of unique dendritic cell processes. These dendritic cell processes create an extensive cellular network in the hard bone matrix, which enables osteocytes to communicate with neighboring osteocytes, and the osteoblasts and osteoclasts on the bone surface by creating a neuron-like network (Palumbo et al., 1990). This highly complex communication network, is created through a space called canaliculi, which are narrow channels in the hydroxyapatite matrix. Osteocytes are separated from the mineralized bone matrix, by a pericellular space filled with proteoglycan-rich matrix (glycocalyx) and interstitial fluid (Termine et al., 1981; Sauren et al., 1992; Aarden et al., 1996). Based on the measurements and mathematical models for branching, these dendritic processes were estimated to form approximately 23 trillion connections and span a total length of over 175000 km within the human body (Buenzli and Sims 2015). In vivo, each cell has been shown to have a varying number of dendritic cell processes ranging from 18 to 106, which reduces with aging (Beno et al., 2006; Qin et al., 2020). Initial development of dendritic cell processes from the cell body leads to the formation of subsequent subbranches, which create sufficient surface area for efficient communication with other cells and also serving as a mechanosensory structures. The unique environment for osteocytes is called the lacunocanalicular network (LCN) and is a complicated network within bone tissue with a total surface area of approximately 215 m² (Sims 2016; Martin 2019) and is also thought to provide a route for the provision of nutrients, oxygen, and biochemical signals.

Since osteocytes reside in this unique LCN architecture of mineralized matrix, it has been a challenge to study osteocytes. In spite of this challenge, a variety of mechanical stimulations such as fluid flow shear stress, and substrate deformation are known to influence osteocytes functions (You et al., 2000; McGarry et a., 2005; Wittkowske et al., 2016; Qin et al., 2020). It is important to understand that loading-induced matrix deformation not only changes fluid flow velocity, but also the matrix strain, which is closely associated with the LCN architecture. A recent study demonstrated that the LCN architecture is a key determinant for bone adaption in response to mechanical stimulation (van Tol et al., 2020). The fluid flow-induced velocity was strongly dependent on the LCN architecture in a highly dense and connected network (Denisov-Nikol’skiĭ Iu and Doktorov, 1987; Johnson 1984). Another study observed that the fluid flow velocity was not directly correlated to the loading-induced strain deformation, but more associated with the LCN structure based on in vivo mice micro-computed tomography (microCT) evaluations (van Tol et al., 2020). The changes in the strain distributions of the LCN upon applying various static and cyclic loads highlighted the diversity of mechanosensors on these cells and complexity of the underlying mechanotransduction pathways (Wang et al., 2015). The dendritic morphology of osteocytes itself is also proposed to be synergistic with the highly-dense LCN network, resulting in an actin-rich cytoskeleton, which enables cell–cell communications between osteocytes allowing a cascade of intracellular events capable of generating a functional response (Burra et al., 2010; Hemmatian et al., 2017).

As osteocytes are embedded individually within the bone and separated from the effector bone cell types, they utilize secreted signaling molecules to communicate their “instructions” in addition to their broader systemic effects (Dallas et al., 2013; Prideaux et al., 2016). Osteocytes are involved in the secretion of signaling molecules, to regulate osteoblast and osteoclast activities, as well as establishing direct physical connections via gap junctions (Figure 1A). The quintessential molecule in bone regulation is the osteocyte-specific sclerostin, which is exclusively expressed by mature osteocytes. Sclerostin is an anti-bone formation (antagonist) regulator that directly inhibits the proliferation and differentiation of osteoblasts (Duan and Bonewald 2016). The osteoblast-induced bone formation is initiated by secreted Wnt ligand glycoproteins, which bind to low-density lipoprotein receptors (LRP) 4/5/6 for phosphorylation, leading to suppression of glycogen synthase kinase 3 (GSK3) (Karner and Long 2017). This stabilizes β-catenin, which then translocates into the nucleus, and acts as a transcriptional co-activator. Sclerostin, the protein product of the SOST gene expressed by mature osteocytes, binds to the LRP 4/5/6 to inhibit Wnt-binding for the Wnt/β-catenin signaling pathway in osteoblasts. Sclerostin expression is also known to be decreased by mechanical loading and increased in response to unloading conditions such as microgravity and reduced physical levels in bed-ridden patients (Pajevic et al., 2013; Bradbury et al., 2020).

The osteocyte-secreted dickkopf-related protein 1 (DKK1) binds to LRP4/5/6 on osteoblasts and acts as a Wnt competitive inhibitor (Li et al., 2006). Osteocytes also secrete osteoprotegerin (OPG), a soluble decoy receptor for receptor activator of nuclear factor-κB ligand (RANKL), which is a cytokine that binds to osteoclasts, promoting bone resorption (Kearns, Khosla, and Kostenuik 2008). The ratio between OPG and RANKL is commonly used as an indicator of bone mass and decreased RANKL/OPG ratio was reported in response to mechanical stimulation, leading to reduced osteoclast activity (Goldring 2015). Interestingly, proinflammatory cytokines were also observed to be down-regulated by mechanical loading, except interleukin 6 (IL-6) (Pathak et al., 2015; Pathak et al., 2020). Mechanical stimulation modulates the release of other factors such as nitric oxide (NO), prostaglandin E2 (PGE₂), cyclooxygenase-2 (COX-2), and adenosine triphosphate (ATP) in osteocytes (Li et al., 2021). Especially, loading-induced calcium ions (Ca²⁺) oscillation releases signaling molecules such as NO, PGE₂, insulin-like growth factor-1 (IGF-1), and β-catenin, which are important for osteocyte viability and anabolic effect on bone (Morrell et al., 2018).

Osteocytes, embedded in the hard bone matrix are also known to regulate their local microenvironment through a process called perilacunar/canalicular remodeling (PLR) (Figure 1B) (Qing and Bonewald 2009; Lin et al., 2020). Earlier studies observed the enlarged lacunae during lactation to release calcium from a mineralized matrix for high calcium demand situations and also in pathological conditions such as Paget’s disease, a bone loss disorder, suggesting the removal of perilacunar matrix by osteocytic osteolysis (Zambonin Zallone et al., 1982; Teti and Zallone 2009; Tsourdi et al., 2018). However, this microenvironment remodeling is also known as a homeostatic mechanism to maintain the perilacunar/canalicular network under healthy conditions such as lactation (Dole et al., 2017). Interestingly, osteocytes are able to remove both minerals and collagen from their surrounding perilacunar matrix by upregulating the H⁺ proton pump, creating an acidic microenvironment (Qing et al., 2012; Creecy et al., 2021). The acidic environment can be induced by the parathyroid hormone (PTH) upregulation during lactation (Jähn et al., 2017). Osteocyte-derived matrix removal was observed in lactating mice showing the enlarged lacunar area with upregulation of tartrate-resistant acid phosphatase (TRAP) and cathepsin K (CatK, encoded by the Ctsk gene), which were previously thought to be osteoclast-specific (Nakano et al., 2004; Qing et al., 2012; Lotinun et al., 2019). TRAP is an enzyme that is responsible for the dephosphorylation of bone matrix phosphoproteins and CatK is a lysosomal cysteine protease that contains the catalytic mechanism necessary for bone matrix degradation leading to bone resorption (Dai et al., 2020). By increasing osteoclast-like markers, they create an acidic environment via carbonic anhydrase 2 (Car2) and proton-pumping vacuolar ATPases.

Recent research hinted that transforming growth factor beta (TGF-β) is possibly associated with the PLR process (Schurman et al., 2021). In vitro studies have demonstrated TGF-β treatment upregulated Ctsk and matrix metalloproteinase 14 gene expressions in both osteocytic cell lines, MLO-Y4 and Ocy454 (Dole et al., 2017; Kegelman et al., 2020). Furthermore, intracellular pH (pHi) has been shown to decrease after TGF-β treatment, resulting in cell acidification, inducing PLR resorption that was dependent on the TGF-β receptors on osteocytes (Dole et al., 2017). TGF-β intake by osteocytes was blocked by using type I TGF-β receptor (TβRI) inhibitor (SB-431542), and lead to increased pH levels, equivalent to untreated groups. In vivo studies using osteocyte-specific TGF-β receptor knockout mice showed decreased expression of Ctsk leading to decreased bone resorption contributing to increased bone mass in these animals. (Dole et al., 2017; Schurman et al., 2021). Furthermore, TGF-β treatment induced changes in gene expression levels of sclerostin in osteocytes. PLR was also induced in osteocytes after recombinant human sclerostin (rhSCL) treatment, which lowers the pHi showing upregulation of catalytic genes (e.g., Ctsk, Car2, TRAP) (Kogawa et al., 2013). This suggests that osteocyte-produced sclerostin promotes catalytic activity to release the minerals. Moreover, rhSCL treatment in human trabecular bone samples showed an increased lacunar area around osteocytes (Kogawa et al., 2018). The activity of sclerostin was also confirmed by Lrp4/5/6 receptors, known for sclerostin binding inhibited osteocyte-mediated catalytic activity for the removal of bone matrix in PLR. However, further investigation is required to understand the mechanisms of PLR, which is different from osteoclast-mediated bone resorption.

It is well known that the increased lacunar area returns to normal after the weaning process suggesting osteocytes play a role in local matrix restoration. It was proposed, that the local PLR remodeling process was independent of mechanical stimulation and was presumed to be hormonally regulated (Qing et al., 2012; Bach-Gansmo et al., 2016). However, a recent study of mice under microgravity conditions, which removes mechanical loading on bones, observed enlarged lacunae size and deformed bone microstructure in these animals (Gerbaix et al., 2017). For osteocytes to perform PLR, both collagen production and mineralization are essential for the matrix restoration process. Previous studies support the osteocyte-driven collagen production using novel GFP-collagen transgenic mice (Baylink and Wergedal 1971; Zambonin Zallone et al., 1982; Kamel-ElSayed et al., 2015). They observed bright collagen production around some osteocytes suggesting heterogeneity in the osteocyte population has a capability of collagen production for PLR restoration. The fact that the collagenous matrix aligned with the axis of the lacunae, suggests collagen orientation and alignment are also coordinated by osteocytes. During this process, the levels of bone matrix proteins such as dentin matrix protein 1 (DMP1) and matrix extracellular phosphoglycoprotein (MEPE) in osteocytes were highly up-regulated to support the mineralization process (Gluhak-Heinrich et al., 2007; Harris et al., 2007; Teti and Zallone 2009; Qing et al., 2012).

PLR contributes to bone quality by altering the mineral to matrix ratio (M/M ratio), which is often used to predict the biomechanical properties of bone (Takata et al., 2011). The M/M ratio often increases with elevated bone mineral density contributing to better bone quality and is significantly increased with exercise (Kohn et al., 2009; Gardinier et al., 2016). In vivo studies of mice undertaking treadmill running, showed an increased M/M ratio around the matrix close to osteocytes compared to the bone matrix further away, suggesting localized osteocyte-induced PLR (Gardinier et al., 2016). This finding suggests that PLR regulation takes place predominantly in the mineralized bone matrix such as cortical bone. A better understanding of the mechanism of PLR regulation will aid in developing potential therapeutic applications that could improve cortical bone integrity, which is known to have a lower recovery rate after fracture compared to trabecular fractures (Chen and Sambrook 2011; Rivadeneira and Mäkitie 2016).

Osteocytes are known to secrete signaling factors into the circulatory system to modulate behavior of distant target organs such as parathyroid, kidney, and heart (Martin 2019; Pathak et al., 2020; Florencio-Silva et al., 2015). Particularly, osteocyte-secreted factor, fibroblast growth factor 23 (FGF23) that plays a role in endocrine signaling (Figure 1C). FGF23 contributes to kidney functions, maintaining serum phosphate levels by modulating the expression level of sodium/phosphate co-transporters in the kidney (Bonewald and Wacker 2013; Dallas et al., 2013; Dussold et al., 2019). Through this mechanism, FGF23 suppresses the vitamin D hormone (1,25-dihydroxyvitamin D) production in the kidneys by inhibiting the conversion of 25-hydroxyvitamin D to the active form, 1,25-dihydroxyvitamin D by 1-α-hydroxylase (Martin, David, and Quarles 2012; Dallas et al., 2013). The high FGF23 levels inhibit the vitamin D conversion process leading to decreased phosphate absorption in the intestine. This signaling process is tightly regulated by a feedback system between the active form of vitamin D and the level of FGF23 in circulation, where osteocytes play a key role. The elevated levels of circulating FGF23 are known as a risk factor for heart disease such as left ventricular hypertrophy, but further investigation is required to understand the underlying mechanism of FGF23 in this tissue (Mirza et al., 2009; Desjardins et al., 2012). The high prevalence of heart failure is often seen in chronic kidney disease (CKD) patients, which is also associated with elevated levels of FGF23 (Scialla et al., 2014). Furthermore, the parathyroid gland is another target for FGF23, which decreases PTH secretion. Where increased FGF23 levels modulate the downregulation of PTH mRNA expression and secretion in vitro (Krajisnik et al., 2007). The important and well-characterized role of PTH is in maintaining systemic calcium levels, where the parathyroid gland-secreted PTH is known to respond to low serum calcium (Bellido et al., 2013). If there is a high calcium demand in the intestine, the PTH levels increase causing mineral release from bones, which is often seen in pathological conditions such as chronic kidney disease. Osteocytes closely coordinate this process by increasing mineral degradation through PLR. Osteocyte-secreted CatK also contributes to the regulation of PTH levels by increasing parathyroid hormone-related peptide (PTHrP) during lactation (Lotinun et al., 2019).

Osteocytes are known to be one of the most mechanosensitive cells (Jacobs et al., 2010). These cells can be stimulated by various mechanical forces in bone created by gravitational forces and daily activities leading to changes of interstitial fluid flow and matrix deformation at the cellular level in bone. The osteocyte cellular response to mechanical stimulation is crucial in terms of viability, and also for a regulatory role in balanced bone homeostasis (Qin et al., 2020; Wittkowske et al., 2016). The earlier studies primarily focused on fluid flow-induced osteocyte mechanotransduction compared to direct interaction with extracellular matrix (ECM) deformation (Cheng et al., 2001a; Cherian et al., 2005; Kulkarni et al., 2010; Li et al., 2012; Spatz et al., 2015; Qin et al., 2020). The fluid flow rate used in previous in vitro studies was between 0.5 and 2 dynes/cm² (0.5 and 2 Pa) with some studies using up to 16 dynes/cm² (Table 1). These studies were demonstrated using both osteocyte cell lines (Cheng et al., 2001b; Cherian et al., 2005; Kulkarni et al., 2010; Litzenberger et al., 2010; Li et al., 2012; Xu et al., 2012; Spatz et al., 2015; Sato et al., 2020) and primary osteocytes (Ajubi et al., 1996; Klein-Nulend et al., 1997; Sterck et al., 1998; Ajubi et al., 1999; Joldersma et al., 2000). However, the exact physiological flow rate remains unclear. Estimates of the physiological matrix strain that is generated at the cellular level is also lacking. The strain level surrounding osteocytes is heterogeneous, amplifying the strain between the local cellular level and tissue level (Weinbaum et al., 1994; Nicolella et al., 2001; You et al., 2001; Bonivtch et al., 2007; Verbruggen et al., 2012; Hart et al., 2017). Several studies have demonstrated that variations in the size and shape of the LCN geometries are closely associated with non-uniform strain distributions (Canè et al., 1982; Metz et al., 2003). A parametric finite element model used to predict the microstructural response in lacuna showed increased strain with a decreased perilacunar tissue modulus (Bonivtch et al., 2007). The canaliculi diameter was increased by 0.8–1% in response to the applied strain and this deformation directly contributed to the enclosed dendritic process via the tethering elements (e.g., CD44, laminin, and integrins) to the canalicular wall (You et al., 2004). It is postulated that the strain difference between lacunar and canlicular structures may induce significantly different cellular responses in osteocytes (McCreadie and Hollister 1997; Nicolella et al., 2006; Verbruggen et al., 2015). In vivo studies revealed that the strain around perilacunar was an order of magnitude greater than the macroscopically applied strains, suggesting that local tissue strain can be magnified by inhomogeneous microstructural features (Nicolella et al., 2006).

There is a wide variety of potential mechanosensors present on osteocytes, which will be discussed in more detail in the following section, that transduce extracellular signals into cellular responses, including pericellular matrix, connexins/pannexin channels, mechanically-sensitive ion channels, integrins, primary cilium, and caveolae (Figure 2) (Bonewald 2011; Qin et al., 2020). There is an ongoing debate around, whether the osteocyte’s cell body or the dendritic cell processes are the primary mechanosensitive features of osteocytes. The unique dendritic morphology enables osteocytes to create a massively interconnected network in the human body creating a surface area that increases exposure to the surrounding microenvironment (Buenzli and Sims 2015; Hemmatian et al., 2017). A previous study has shown that the dendritic cell processes are more responsive to fluid shear stress than the cell body, using a transwell filter system to separate the dendritic cell processes from the cell body (Burra et al., 2010). Subsequent studies have also concluded that the more sensitive mechanotransduction occurs through dendritic cell processes, which induces calcium influx and regulate gene transcription of key secreted signaling molecules such as sclerostin (Wu et al., 2011; Thi et al., 2013).

Although mechanically-induced osteocyte responses have been studied extensively, the precise signaling pathways underlying these responses are still unclear. Understanding the signaling pathways is critical due to the implications of the functional outcomes for both bone health and diseases, as well as more broadly for the other systemic role of osteocytes through their endocrine functions (Dallas et al., 2013). For the past decades, several signaling pathways have been identified, as potential therapeutic targets to improve bone health (Table 2).

Abnormalities of bone strength and microstructure are common in bone diseases, where the bones become more fragile and are more likely to fracture (Feng and McDonald 2011). These disorders are often closely associated with the dysregulation of bone cells, especially osteocytes (Pathak et al., 2020). Specifically, the loss of osteocyte functional ability is linked to compromised bone homeostasis. Osteocyte apoptosis has been proposed as a major risk factor caused by aging, reduced physical activity, hormone deficiency and inflammation resulting in dramatic decrease of osteocyte density (Almeida 2012). As a result, aged or dying cells are no longer able to carry out functional roles, which have an impact on the bone matrix quality (Shah et al., 2018). The accumulation of apoptotic osteocytes with aging is linked to several bone diseases such as osteonecrosis and the onset of age-related osteoporosis leading to increased fracture risk. During apoptosis, osteocytes secrete signals to osteoclasts to be recruited to the site for bone resorption (Schaffler et al., 2014). When apoptosis takes place, osteocytes release damage-associated molecular patterns (DAMPs) for osteoclast recruitment (McCutcheon et al., 2020). When dead osteocytes are removed, the empty lacunae are hyper-mineralized with calcium phosphate, leading to a condition called micropetrosis, resulting in more brittle bones (Qiu et al., 2002; Bell et al., 2008). The accumulation of mineralization in lacunae also interrupts the osteocytic cell–cell communication, leading to depletion of signals and nutrition due to disturbance of canalicular fluid flow (Hemmatian et al., 2017). This cascading process then inevitably further affects other osteocytes resulting in even more extensive osteocyte apoptosis. With less active osteocytes, the bone is less likely to be protected against microdamage. Microdamage triggers dying osteocytes to send signals for osteoclast activation, and at the same time, osteocytes also send anti-apoptotic factor, BAX to neighboring cells to protect their viability (Verborgt et al., 2000; Bonewald 2017). By doing this, the number of apoptotic osteocytes can be minimized around the damaged area. However, if there is a decreased number of viable cells, this mechanism is disrupted, leading to a large area of microcracks (Ma et al., 2008). Therefore, osteocyte cell viability plays a crucial role in the maintenance of bone health, and also protects against microdamage, which is a normal physiological process. The apoptosis process is closely associated with increased oxidative stress, which was confirmed with oxidative stress markers such as p53 and p66^Shc in aged mice (Almeida et al., 2007). The oxidation process has been shown to be delayed by anti-oxidant N-acetyl Cysteine. Another noticeable change in aged osteocytes is the decreased level of autophagic activity, which is an important indicator for stress susceptibility (Ru and Wang 2020). For example, aged-osteocytes are less likely to produce autophagic proteins (e.g., Beclin-1) to suppress apoptotic proteins (e.g., cleaved-caspase-3). This mechanism is important especially for the anti-apoptotic activity of neighboring cells. However, prolonged stress will cause apoptosis eventually, which highlights the importance of the underlying mechanism between autophagy and apoptosis. Apart from aging, other factors such as estrogen deficiency and glucocorticoid treatment can also induce osteocyte apoptosis leading to osteoporosis (Jilka et al., 2013). Additionally, inflammatory cytokines such as interleukin 1 (IL-1) and tumor necrosis factor-alpha (TNF-α) increase osteocyte death (Marahleh et al., 2019; Wang et al., 2019). Some factors including parathyroid hormone, estrogen, bisphosphonates are known to protect osteocytes from apoptosis (Plotkin et al., 1999; Bellido and Plotkin 2011). Furthermore, as already mentioned above, unloading or decreased level of exercise often leads to decreased bone mass, which is well described in astronauts or bedridden patients (Bradbury et al., 2020; Stavnichuk et al., 2020). These findings are further illustrating, that osteocytes require mechanical stimulation, which can be introduced by mechanotherapy such as low-intensity pulsed ultrasound (LIPUS) treatments where this type of direct mechanical stimulation has been shown to improve bone healing (Thompson et al., 2016; Jiang et al., 2019). The vibration therapy studies demonstrated that high-frequency, low-magnitude vibration therapy (gravitational force = acceleration of 9.81 m/s², frequency >30 Hz) improved bone health (Thompson et al., 2014). These relative parameters were estimated based on the bone dynamics that experience low-frequency (1–3 Hz), high-frequency (10–50 Hz), and large-magnitude (2,000–3,000 microstrain) (Fritton et al., 2000). Whole-body vibration (WBV) has been recently introduced as a bone stimulation therapy (12.6 Hz for 30 s with 1-min rest for 4 times) with hypoxic stimuli (16.1% FiO₂) also showed improvement in bone mineral density (BMD) after 18 weeks (Camacho-Cardenosa et al., 2019).

Osteocyte cell death with age is one of the major factors for the onset of osteoporosis. Age-related osteoporosis is closely associated with a low level of autophagic activity, which was also shown in apoptotic osteocytes. There are several treatments for osteoporosis, reducing bone resorption, that are based on the administration of oral bisphosphonates (Fosamax, Boniva), intravenous bisphosphonates (Zoledronate, Pamidronate), Cathepsin K inhibitors (Odanacatib), and Anti-RANKL antibody therapy (denosumab) (Merlotti et al., 2007; Lewiecki 2010; Eriksen et al., 2014; Suen and Qin 2016; Tanaka et al., 2017; Lu et al., 2018; Galvano et al., 2019). Osteoblast-targeted hormone replacement therapy is also widely used, including estrogen receptor (Raloxifene) and parathyroid hormone peptide (teriparatide, abaloparatide), however, these therapies also affect osteocytes (Deal et al., 2005; Bonewald 2017; Leder 2017). In vivo studies have confirmed that sclerostin monoclonal antibody (Scl-Ab) treatment induced bone formation, mass, and strength (Yao et al., 2016). Scl-Ab products are commercially available including Romosozumab (AMG 785, CDP-785), Blosozumab, and BSP804 (McClung 2017; Morrell et al., 2021). These antibody-based treatments are widely used for reducing fracture risk arising from various health conditions, including osteoporosis as well as post-menopause (Ominsky et al., 2011; MacNabb et al., 2016). Furthermore, a bispecific antibody for sclerostin and DKK1 has been shown to have synergistic effects for bone formation compared with monotherapies (Florio et al., 2016). These approaches try to inhibit the secretory signaling molecules produced by osteocytes that antagonize the Wnt-signaling pathway in the osteoblast lineage, affecting the anabolic bone formation.

Although these treatments are widely used, the long-term safety and efficacy have to be taken into consideration. The most commonly used treatment for osteoporosis is based on bisphosphonates (Drake et al., 2008). These are effective and safe treatments with persistent benefit even after taking a break from the treatment, however, there are no clear guidelines for “drug holiday” (Diab and Watts 2013). The United States Food and Drug Administration (FDA) proposed a reevaluation of continuing bisphosphonate therapy after 3–5 years, showing a small decrease in BMD without higher fracture risk (Whitaker et al., 2012). In contrast to the prolonged half-lives of bisphosphonates, anti-RANKL (denosumab) shows reduced efficacy after treatment discontinuation (Bone et al., 2011). The anti-sclerostin treatment with romosozumab showed a decrease in BMD after discontinuation followed by 2-years treatment (McClung et al., 2018). Similarly, blosozumab treatment showed a decline in BMD in both the femoral neck and the lumbar spine after the discontinuation suggesting there is an increased risk of fracture (Recknor et al., 2015). The treatment options are summarized in Table 3.

Osteogenesis imperfect (OI) is a congenital disease that exhibits brittle bone (Basel and Steiner 2009). This disorder is caused by alterations in type I collagen that was previously known to be associated with osteoblast activities (Wenstrup et al., 1990). As the type I collagen is the predominant ECM protein, its dysregulation influences bone mineralization, leading to the impairment of local-acting growth factors such as TGF-β (Morello 2018). A recent study revealed that the osteocyte transcriptome was dysregulated in OI mice including Wnt/β-catenin and TGF-β signaling pathways (Zimmerman et al., 2019). TGF-β is a crucial factor to regulate bone formation and bone resorption for maintaining bone mass. However, excessive activation of the TGF-β signaling pathway found in OI increases high bone turnover and low bone mass (Lim et al., 2017). This continuous activation of TGF-β signaling may disrupt osteoblast functions while increasing osteocyte density. Increased TGF-β signaling can be diminished by TGF-β neutralizing antibody (ID11) treatment leading to improved bone mass by decreasing osteoblast and osteoclast numbers while normalizing the osteocyte density. The exact mechanism of impaired TGF-β signaling in OI is not fully understood, but possibly through impaired binding of small leucine-rich proteoglycans (e.g., decorin) to TGF-β in collagen fibrils. OI mouse model showed abnormalities of type I collagen expression showing abnormal osteocyte phenotype with impaired dendritic formation. Impaired osteocyte phenotype may contribute to their functional roles by interrupting the cell–matrix interaction. As a consequence, osteocytes may increase osteoblast activities towards bone formation after detecting a defective matrix, possibly for the restoration process. The osteocyte transcriptome sequencing of OI compared to wild-type control mouse models demonstrated the differential expression of dysregulated collagen fibril organization, but also impaired osteocyte dendritic formation, ECM compositions, and integrin-mediated signaling (Zimmerman et al., 2019). This observation supports the role of impaired cell–matrix interaction promoting dysregulated dendritic formation and leading to changes in functional roles. Interestingly, the Wnt signaling pathway in osteocytes was also affected in OI mice as gene levels for Wnt ligands were significantly increased, however, the exact mechanism of Wnt upregulation in OI remains unclear (Fahiminiya et al., 2013). In vivo studies with the conditional Wnt inactivation in osteocytes showed increased bone fragility and low bone mass as a result of altered Wnt1 production (Joeng et al., 2017). Like osteoporotic therapeutics, anti-resorptive (e.g., cathepsin K inhibitors and Anti-RANKLtherapies) and bone anabolic treatments (e.g., Sci-Ab and PTH) are commonly used for OI patients (Drake et al., 2008; Morello 2018).

Apart from bone-related diseases, there is more evidence emerging that osteocytes are also associated with other diseases, facilitated via secretion of the FGF23 hormone (Guo and Yuan 2015). It was reported that highly elevated circulating FGF23 is closely associated with kidney dysfunction, and this was also linked to heart failures such as left ventricular hypertrophy and vascular calcification (Faul et al., 2011; Desjardins et al., 2012). Furthermore, FGF23 was linked to chronic hypophosphatemia, caused by impaired mineralization of the bone matrix leading to bone fragility (Murali et al., 2016). Circulating FGF23 controls serum phosphate levels, by suppressing reabsorption in the kidney, and excess FGF23 causes hypophosphatemia diseases. Hypophosphatemia with high levels of FGF23, can be treated with a monoclonal FGF23 antibody (anti-FGF23), for example, burosumab, which was recently approved by the FDA to stabilize serum phosphate levels. The alternative medication for hypophosphatemia is a combination of active vitamin D and phosphate salts, however, this treatment often leads to kidney failure (Kinoshita and Fukumoto 2018; Barratt et al., 2021).

Once considered inactive cells, the osteocytes are now attributed to have crucial roles in the overall bone remodeling process, local microenvironment regulation and systemic interactions with other organs. The tightly regulated bone homeostasis becomes dysregulated as we age and with reduced mechanical stimulation, shifting the balance towards more bone resorption, leading to bone loss diseases such as osteopenia and osteoporosis, which increases fracture risk. As we move towards a more aging society, both intrinsic and extrinsic factors accelerate pathological signaling pathways causing disorders. Intrinsic factors (e.g., genetics, hormones, vasculature) and extrinsic factors (e.g., nutrition, physical activity, medications) are associated with the mechanisms that maintain healthy bone (Demontiero et al., 2012).

When the mechanosensitivity of osteocytes was first demonstrated, understanding the underlying modes of detection, the osteocyte-induced mechanotransduction pathways, and the functional outcomes for bone metabolism became significant research focuses in the field (Iolascon et al., 2013). The long life span of osteocytes (up to 25 years) and their important role in regulating the continuous coordinated cycle of bone formation and resorption and in the repair of bone damage makes them an ideal target for therapeutics. However, bone homeostasis is a complicated system involving multiple cell types that are signaling and coordinating each other. Until now, most studies on bone cells have focused on the more accessible effector cells, osteoblasts, and osteoclasts as compared to osteocytes (Liedert et al., 2005). The inaccessible location of osteocytes buried within the hydroxyapatite matrix, makes their visualization challenging, so studies have largely focused on in vitro cellular models to understand the mechanistic pathways that respond to mechanical stimuli.

Although in vivo studies provide more physiologically relevant outcomes, the various biological effects within more complex tissue responses are challenging to dissect and to attribute specific cellular roles given the complex microstructural organization of bone is hard to mimic. Targeting simplified approaches, focused on osteocyte-elicited mechanotransduction on 2D plastic or 2.5D using collagen coating, the in vivo three-dimensionality has been largely neglected in this field. Only recently, commercially available natural (e.g., collagen and fibrin), synthetic (e.g., polyethylene glycol hydrogels), and both animal and plant-derived (e.g., matrigel, gelatin, and alginate) matrices were used to construct 3D in vitro models (Langhans 2018; Zhang et al., 2019c; Aziz et al., 2020). The inorganic component, hydroxyapatite, is available as a ceramic composite with tricalcium/biphasic calcium phosphate (Boukhechba et al., 2009). Hydroxyapatite is widely used for coatings on metallic implants, bone fillings, and injectable bone substitutes (Ramesh et al., 2018). Alternative synthetic material, polystyrene is also available, and is tunable for various parameters such as pore sizes and thickness (Spatz et al., 2015). Direct cell-free bone tissue also becomes an option that represents the natural milieu, but again the mechanical properties are difficult to tune (Lyons et al., 2010; Li et al., 2019b).

Despite their inherent advantages, none of the cell models recapitulates the 3D dendritic morphology observed in vivo, indicating more ideal matrices need to be developed. This is especially important for osteocyte mechanotransduction studies, as the dendritic morphology is now considered an important mechanotransducer. Without providing an ideal microenvironment, this is not only limiting the morphology but also cellular responses, where better understanding of osteocyte mechanotransduction will provide significant opportunities for developing novel therapeutics for bone-related diseases.

The currently available treatments for bone disorders either target osteoclastic activity or osteoblastic activity (Rochefort 2014). Despite osteocytes abundance and their instrumental role in regulating bone metabolism, osteocyte-targeted treatments are not readily available. There are, however, some indirectly targeting antibody-based treatments to osteocyte-secreted molecules such as the recently FDA-approved sclerostin monoclonal antibody treatment for osteoporosis, promoting bone formation (Shakeri and Adanty 2020). Maintaining osteocyte viability is now considered one of the most important factors to maintain healthy bone (Bonewald 2017; Ru and Wang 2020). Aging, in particular, accelerates osteocyte apoptosis, resulting in fewer secretory factors, less bone matrix remodeling, and lower responsiveness to mechanical stimulation leading to impaired osteocyte functional roles in bone. Therefore, the development of novel osteocyte-specific therapeutics would be ideal to target osteocyte functions and signaling pathways including mechanisms to prevent apoptosis. Many of these pathways are still lacking a detailed understanding of, while others are more generic signaling pathways, such as the Wnt/β-catenin and TGF-β1 signaling, which are expressed in other cell types making therapies more challenging and less targeted (Janssens et al., 2005; Rys et al., 2016). In addition, the extra-skeletal roles of osteocytes in regulating distant organs, such as kidneys, heart, and parathyroid through secreted signaling molecules provides opportunities to target the associated dysfunctions in these organs through osteocyte manipulation.

The focus of this review was to highlight the fundamental role of osteocytes, the most mechanosensitive cells of the bone, by revealing how these cells detect mechanical stimuli through various mechanosensors and the proposed mechanotransduction pathways driving the functional responses that fundamentally affect bone metabolism. However, much detail around these mechanoresponsive pathways in osteocytes is still lacking. Therefore a greater understanding of these mechanisms will help us to identify more effective treatments for both chronic bone loss diseases such as osteoporosis as well as other genetic diseases affecting bone metabolism. This will also enable researchers to unravel, how these master regulators contribute to their important extraskeletal roles.