Here, we report the effect of newly regenerated axons via scaffolds on reorganization of spinal circuitry and restoration of motor functions with epidural electrical stimulation (EES). Motor recovery was evaluated for 7 weeks after spinal transection and following implantation with scaffolds seeded with neurotrophin producing Schwann cell and with rapamycin microspheres. Combined treatment with scaffolds and EES-enabled stepping led to functional improvement compared to groups with scaffold or EES, although, the number of axons across scaffolds was not different between groups. Re-transection through the scaffold at week 6 reduced EES-enabled stepping, still demonstrating better performance compared to the other groups. Greater synaptic reorganization in the presence of regenerated axons was found in group with combined therapy. These findings suggest that newly regenerated axons through cell-containing scaffolds with EES-enabled motor training reorganize the sub-lesional circuitry improving motor recovery, demonstrating that neuroregenerative and neuromodulatory therapies cumulatively enhancing motor function after complete SCI.
Spinal cord injury (SCI) induced cell death, demyelination, and axonal damage leads to loss of independence of daily life. The spinal cord has limited ability to regenerate and currently available therapies including pharmacologic, cellular, and biomaterial agents demonstrated only modest functional recovery. Recent advances in bioelectronics and tissue engineering led to the rise of neuromodulatory and neuroregenerative therapies, which aim to target circuits in the brain or spinal cord to improve neurologic functions. Encouraging results using epidural electrical stimulation (EES; definition of major terms can be found in the glossary in the supplementary information) to restore motor function in humans with SCI1,2,3 have been attributed to the presence of functionally silent fibers and the combination of EES with motor training4,5,6. Most of the patients diagnosed with complete loss of motor control after SCI demonstrate some degree of sub-functional connectivity, which provides the anatomical and functional basis for supraspinal control in the presence of EES6,7. Currently, there is only limited understanding of the mechanisms underlying the effect of EES to restore motor functions after SCI. In this regard, elucidating the mechanisms of EES-enabled improvement in motor control in animal models with limited connectivity will advance EES therapy in SCI subjects and open the possibility of combining EES with neuroregenerative therapies.
According to the current concept, electrical stimulation engages the lumbosacral circuitry and can promote standing and stepping behavior in weight supported mice, rats, and cats without supraspinal input after complete transection8,9,10,11,12,13. The type of movement elicited depends on the level of the spinal cord stimulation, however, the optimal location for step like movement was found at L2 and S1 spinal segments that was applied in monopolar10 and bipolar configurations11,14,15,16,17 improving stepping in complete SCI rats. Another important component of EES-enabled stepping is activity-dependent plasticity of the sensorimotor circuitry induced by intensive motor training8,12,15,16,18,19,20,21,22,23. EES-enabled motor training was able to induce overground walking, stairclimbing, and swimming ability in rats with severe SCI16,24. The motor cortex is likely involved in the recovery of these behaviors though the development of neuronal detours in the brainstem, supralesional spinal neurons, or with intact neuronal tissues across the lesion16,24. In addition, trained rats have less variability in electromyogram (EMG) and greater localized c-fos immunoreactivity in the lumbosacral spinal cord, suggesting the task-dependent plasticity21. Together these findings demonstrated that motor control and improved gait could be achieved through regeneration of the short spinal tracts, formation of detours, and plasticity of neural circuits without necessarily regeneration of long descending tracts25.
One of the reasons for poor regeneration after SCI is the formation of the cyst and scar tissue rich with inhibitory molecules that prevent axons from crossing the injury site. Neuroregenerative therapies aim to promote regrowth through cell replacement, microenvironment modifications, tissue engineering, and promotion of intrinsic and extrinsic growth pathways. One tissue engineering approach is to utilize biomaterials to bridge the lesion following SCI. Polymer scaffolds provide physical guidance and structure for axonal growth through the injury. When implanted alone, they have been found to reduce scar and cyst formation26,27,28,29. Scaffolds combined with other factors to promote tissue growth and vascularization, as well as delivery drugs and cells, demonstrated further improvement in multiple models30,31,32,33,34,35. Xu et al.36 found that loading guidance tubes with Matrigel and Schwann cells significantly improved axon regeneration following spinal cord transection. The delivery of brain derived growth factor (BDNF) and neurotrophin-3 (NT-3) through minipumps along with Schwann cell loaded guidance tubes further enhanced axonal regeneration36. Our group has constructed a multichannel scaffold containing positively charged oligo [poly(ethylene glycol)fumarate] (OPF+). This scaffold has biomechanics similar to the rat spinal cord and the positive charge aids in enhancing cell attachment and axonal outgrowth27,37. When compared to poly (lactic co-glycolic acid) (PLGA) and poly(ɛ-caprolactone fumarate) (PCLF), OPF+ had greater number of axons contained in the channels27. OPF+ scaffolds loaded with Schwann cells overexpressing glial derived growth factor (GDNF) demonstrated enhanced axonal regeneration and myelination associated with recovery in hind-limb movements38. Another important finding of this study is that the regenerating axons were primarily ascending sensory axons located up to 30 mm away from the lesion. The OPF+ biomaterial could be further modified to contain drug eluting microspheres loaded with small molecule such as the anti-fibrotic drug rapamycin, demonstrating functional improvement that could be attributed to reduced fibrotic scarring39. These studies demonstrate that tissue engineering approaches are ideal for use in combinatorial treatments and that regeneration of spinal tracts can be promoted through the injury site, enabling anatomical reconnections that can be further functionally engaged with neuromodulation.
Recent advances in bioelectronics and tissue engineering demonstrate that neuromodulatory and neuroregenerative therapies independently can lead to functional restoration after SCI40,41,42,43,44. The combination of the different therapies considered to be critical for treatment of SCI due to multifaceted pathophysiological response to SCI. Recently reported combinatorial approach used in a phase I clinical trial utilized collagen scaffolds (NeuroRegen scaffold, InVivo Therapetuics) loaded with human umbilical cord mesenchymal stem cells implanted into patients with complete SCI (C5-T12) following surgical scar resection45. This study revealed no adverse effects and limited improvements in sensation level, motor evoked potentials, trunk stability, finger activity, and autonomic recovery in some patients 1 year after implantation. Our previous preclinical work demonstrated that axon regeneration was greater when Schwann cell loaded OPF+ scaffolds were used when compared to neural stem cells or mesenchymal stromal cells loaded scaffolds46,47. Regardless, most of the animal studies and clinical trials with cell therapies only demonstrated a modest functional recovery48,49,50,51. Spinal cord neuromodulation was also broadly studied in animal models and was successfully implemented in clinical trials, demonstrating restoration of neurologic functions in patients with clinically complete SCI1,2,52,53,54. Currently, there is little to no evidence that EES of the lumbroscaral spinal cord could promote axon regeneration alone, however, it likely exerts some neuroplasticity effect through increased excitability and plasticity of the local circuitry, as well as by utilizing the remaining connections that may exist following a clinically complete injury25,51. Both biomaterial or cell therapy and neuromodulation therapy being advanced to the clinical trials, however, up to know never been tested for their synergistic effect in preclinical studies on complete SCI models. Particularly, great potential for the combination of neuroregenerative and neuromodulation therapies represent a model with complete spinal transection, and with scaffold placement that could inform a better understanding of the role of sub-functional connectivity via newly regenerating across injury fibers in enabling neurologic functions with EES.
Elucidating the mechanisms of EES-enabled restoration of motor function after SCI with sub-functional connectivity is critical for optimizing combined neurostimulation and neuroregenerative therapy. To this end, we have developed an approach with hydrogel scaffold loaded with cells and small molecules used to enhance regeneration combined with electrodes that deliver EES-enabled rehabilitation. This approach provides application of biotechnologies currently being investigated in preclinical and clinical trials separately1,45,52,53. The positively charged OPF would help bridge the injury and provide scaffolding for axons55,56,57,58, rapamycin is well known for its ability to reduce fibrosis and microglial activation39,59,60,61, Schwann cells would help to remyelinate and provide some trophic support62,63,64, whereas GDNF would help promote axon regeneration and neuroprotection38,65,66,67,68. The synergistic effect of neuroregenerative therapy applied with EES-enabled motor training provides a strong platform to further enhance recovery through the selective regeneration of new fibers, neuroplasticity, and activation of the spinal circuitry involved in functional restoration. In this study, we report evidence of the contribution of newly regenerated axons through a scaffold in reorganization of the spinal circuitry and restoration of EES-enabled motor functions. The results of this work highlight the important interplay between neuroregenerative and neuromodulatory therapies in anatomical and functional restoration following SCI.
Axon number across scaffolds does not differ among experimental groups
The transplantation of scaffolds with GDNF secreting Schwann cells38 or with rapamycin and Schwann cells39 have shown functional and anatomical improvement after SCI. As an experimental platform for this study, we combined hydrogel scaffolds composed of positively charged oligo-[poly(ethylene glycol)fumarate] (OPF+) loaded with neurotrophic factor (GDNF) secreting Schwann cells and rapamycin microspheres (enhanced scaffolds) combined with EES and EES-enabled motor training (Fig. 1a–c)13,69,70,71,72. Groups with SCI and EES-facilitated training (EES only) (n = 4), with enhanced scaffolds (scaffold only) (n = 3), and with combined therapy of scaffold and EES-enabled training (n = 10, 5 with re-transection) were compared (Fig. 1b). At 7 weeks after complete SCI, the number of axons passing through each of the seven channels of the scaffold was assessed (Fig. 1d–g and Supplementary Fig 1).
Groups with scaffold only (Fig. 2a) and with combined therapy (Fig. 2b) demonstrated regeneration through the scaffold, although, with no difference between the groups: 84.46 ± 5.93 and 97.60 ± 26.16 axons/channel, respectively (Fig. 2c). There was also no statistical difference between the axon numbers in the dorsal, central, or ventral channels nor rostral to caudal quarter lengths (Supplementary Fig. 1). Approximately, equal number of axons are present through the length of the scaffold.
Motor performance is enhanced with combined therapy
EES-enabled motor performance was evaluated with kinematics (Fig. 3), EMG, and electrophysiology (Fig. 4). Open field behavior Basso, Beattie, and Bresnahan (BBB) motor scores were collected with and without EES. BBB scores at week 1 without stimulation were similar across all groups (0–1.5) with no difference during the first four weeks. At week 4 and 6, the BBB score was greater for rats with combined therapy (week 6: 6.62 ± 1.38) compared to EES only (week 6: 2.50 ± 0.67, p < 0.05; Fig. 3b). Kinematic analysis (Fig. 3a–e) at 2–4 weeks demonstrated higher step height in the group with combined therapy compared to animals with scaffold only (p < 0.05) and with EES only (p < 0.001). At week 6 the group with scaffolds only recovered step height almost to the level of group with combined therapy. Both groups with scaffold only and with combined therapy demonstrated higher step height compared to EES only (p < 0.05) (Fig. 3c). An increase in step length was found in the group with combined therapy at 2–4 weeks compared to scaffold only (week 2: p < 0.05, week 4: p < 0.01) or with EES only (week 2 and 4: p < 0.01; Fig. 3d). At week 6, the group with scaffolds only recovered to the level of the group with combined therapy. At 6 weeks after SCI, dragging was greater in the group with EES only compared to both combined therapy (p < 0.001) and scaffold only (p < 0.05) (Fig. 3a). All groups demonstrated recovery of angular displacement that in knee was greater at week 4 and 6 in group with combined therapy compared to other groups (p < 0.05). Metatarsophalangeal (MTP) joint angles were not different at 2 weeks after injury, although at 4–6 weeks, the group with combined therapy demonstrated greater MTP displacement compared to other groups (p < 0.05) (Fig. 3e).
Electrophysiological evidence of functional regeneration across the scaffold
Spinal cord motor evoked potentials (SCMEP)73 were recorded while rats were stimulated above (T8) and below (S1) the injury at week 2 and 6, and after re-transection at week 7 (Fig. 4a). In a representative rat with combined therapy, stimulation above the injury (T8) at week 2 evoked small supralesional evoked polysynaptic response (SEPR) (Fig. 4a). By week 6 SEPR became more prominent and disappeared after re-transection. Stimulation below the injury at S1 evoked middle response (MR) (4.5–5.7 ms) that increased in amplitude following re-transection, indicating the influence of regenerated fibers on the sub-lesional network. In another rat, with stimulation at T8, SEPR was detected only at week 6 and also disappeared after re-transection (Fig. 4a). Stimulation below the injury at S1 in this rat also demonstrated facilitation of MR response after re-transection. The mean MR peak-to-peak amplitude before re-transection at week 6 was 4.28 mV and increased to 10.67 mV after re-transection (p < 0.001) (Fig. 4b).
Electrophysiological and behavioral features of motor performance were compared during EES-enabled motor training at 6 weeks after SCI and after re-transection. Rats with combined therapy demonstrated gradual recovery of EES-enabled stepping and after re-transection they retained some improvements compared to EES only group, suggesting influence of regenerated axons on reorganization of sub-lesional circuitry (Fig. 4c). Following re-transection, rats with combined therapy lost step length (p < 0.001) (Fig. 4d) as well as had a decrease in knee and ankle angles that still were greater compared to EES only group (p < 0.05) (Fig. 4e). The MTP angle did not change after re-transection, although was greater (p < 0.001) compared to EES only group (Fig. 4e). Interestingly, rats with combined therapy demonstrated similar BBB scores with EES turned OFF and ON, although, after re-transection, BBB score with EES-ON at optimal intensity for motor performance was increased for three of the four rats compared to when the EES was completely OFF. This may indicate on predominant role of trans-lesional connectivity on motor performance in case of partial connectivity. These results also suggest more evident role of EES on motor performance after complete spinal cord injury compared to partial connectivity.
Regenerating axons influence synaptic reorganization of L2-S1 cord with combined therapy
Morphological reorganization below the injury was evaluated with synaptophysin co-localized to ChAT positive motor neurons and calbindin positive interneurons (spinal segments L2-S1) (Fig. 5a–d). Rats with combined therapy (0.46 ± 0.088) trended towards greater ratio of co-localization area of ChAT and synaptophysin compared to EES only group (0.28 ± 0.07; Fig. 5e). There was also a trend towards greater synaptophysin co-localized to calbindin in rats with combined therapy (0.45 ± 0.07) compared to EES only (0.31 ± 0.062; Fig. 5f). When the distribution of synaptophysin boutons was quantified on ChAT+ neuronal cell bodies, the EES only group had significantly lower numbers (38,615 synaptophysin boutons per ChAT+ neuron/mm2, mean: 54,486,CIL: 50,993 CIU: 57,979) compared to the animals from the combined therapy group (78,656, mean: 93,287, CIL: 89,534 CIU: 97,039; p < 0.0001) and with scaffold only (53,387, mean: 66,105, CIL: 60,893 CIU: 71,317; p < 0.001). The amount of synaptophysin boutons on ChAT+ neuronal cell bodies was greater in rats with combined therapy compared to scaffold only (p < 0.0001; Fig. 5g). Similar difference was found in the distribution of synaptophysin boutons on calbindin+ cell bodies (Fig. 5g). The amount of synaptophysin was greater in rats with combined therapy (118,512 synaptophysin boutons per calbindin+ neuron/mm2, mean: 127,661, CIL: 122,482 CIU: 132,839; p < 0.0001) compared to EES only (73,194, mean: 90,682, CIL: 85,918 CIU: 95,445). The amount of synaptophysin boutons in rats with scaffold only (77,738, mean: 92,142, CIL: 85,732 CIU: 98,551) was less than the combined therapy groups (p < 0.0001), but was not different from EES only. These results indicate that the regenerating axons affect synaptic reorganization below SCI, although, the combined therapy has greater influence on reorganization on the motor and interneuron cells bodies. The synaptophysin distribution was greater on calbindin+ interneurons than the ChAT+ motor neurons (p < 0.0001), suggesting the greater role of synaptic reorganization on interneurons with the ratio of synaptophysin per neuron/mm2 on calbindin+ to ChAT+ greater for the EES only group (1.89) than the scaffold only (1.46) or combined therapy group (1.51). The synaptic reorganization within the motor neurons (ChAT+ to calbindin+ ratio) was greater for the scaffold only (0.68) and combined therapy (0.66) than the EES only group (0.53).
The results of this study demonstrate the effect of newly regenerated axons on motor performance facilitated with EES through synaptic reorganization of sub-lesional circuitry, suggesting that neuroregenerative and neuromodulatory therapies cumulatively improve motor function after complete SCI. Reconnection across complete transection has been previously achieved with a nerve autograft and scaffolds74,75, particularly when delivering cell types and growth factors57,75,76,77,78,79,80. The functional outcome in our study was better in rats who received combined therapy, at the same time, the number of axons through scaffolds was not different between the groups and was in between previously reported with scaffold loaded GDNF secreting Schwann cells57 or loaded with rapamycin and Schwann cells58. Rapamycin in fact may reduce the number of regenerating axons, although several previous studies demonstrated functional and anatomical improvement when compared with OPF+ scaffolds loaded with Schwann cells alone39, which could be attributed to altering synaptic excitability81,82,83,84. Rapamycin can also block mTOR required for axon regeneration85,86, although, its impact on behavior is not evident61,87,88,89. In this study the BBB score at 6 weeks with combined therapy (6.62 ± 1.38) was greater compared to OPF+ with rapamycin microspheres and Schwann cells (4.69 ± 0.57) reported in previous study39. BBB score at week 4 in group with combined therapy (4.33 ± 1.31) in this study was similar to effect of OPF+ scaffolds with GDNF Schwann cells (3.67 ± 0.4) reported previously38.
Considering limitations of BBB90,91 we added electrophysiological and kinematic analysis accommodating our recently developed Multifactorial Behavioral Assessment system92. The BBB scale depends on subjective observations of basic hindlimb function on a 21-point scale that may lack sensitivity for some subtle locomotor changes and electrophysiological outcomes of activity90,93,94,95,96. Measures such as kinematics and EMG provide information on motor recovery, combining multiple sensitive parameters91,92,97,98. The Multifactorial Behavioral Assessment system used in this study simultaneously recorded limb and joint kinematics and electrophysiological measurements, such as EMGs and fMEPs92. In addition, the body weight support system and treadmill stepping help to record subtle changes in locomotion not possible with traditional BBB testing. Using this assessment, we found improvements in group with combined therapy vs. EES only, and with intermediate effect in scaffolds only group. Following re-transection, group with combined therapy still demonstrated better performance compared to EES only group with complete transection. The difference between EES only vs. combined (scaffold + EES) therapy group indicates on the role of newly regenerating axons in reorganization of sub-lesional circuitry. Electrophysiological changes tested with stimulation of the spinal cord above and below the injury demonstrated two types of functional connectivity with sub-lesional network. The long latency SEPR induced by stimulation of the spinal cord above the injury, likely indicates on activation of polysynaptic network via translesional connectivity and its inhibition after re-transection. Facilitation of the monosynaptic middle response (MR) after re-transections indicates on different mechanism, likely related with pre-synaptic inhibition.
Further observed greater synaptophysin co-localization with motor neurons and interneurons in animals treated with combined therapy suggests that regenerating axons form functional connections with sub-lesional circuitry, facilitating reorganization with EES-enabled training. Synaptic reorganization below the SCI has been attributed to various rehabilitation strategies94,99, while the quality of movement is largely depends on descending commands and sensory feedback integration on interneuronal populations6,13,100,101,102,103. Here we demonstrate that newly regenerating axons along with EES-enabled motor training together influence the sub-lesional circuity through synaptic reorganization. This synaptic reorganization strengthens the network, so that even following re-transection there is improved EES-enabled stepping compared to controls. Although the number of rats in this study is relatively small, the concordance of behavioral, electrophysiological, and histological results convincingly demonstrates that greater synaptic reorganization on the interneurons in the presence of regenerated axons is leading to restoration in polysynaptic responses and improving gait, particularly in group with combined treatment.
In summary, in this work a combination of neuroregenerative scaffold technology with neuromodulatory bioelectronics to delivery EES-enabled rehabilitation was validated and tested in rats with complete spinal transection. The results of this study demonstrate that newly regenerated axons through the cell-containing scaffold with EES-enabled motor training can reorganize sub-lesional circuitry and improve EES-enabled motor performance, providing a platform for synergistic testing and translation of regenerative and neuromodulatory therapies to maximize functional restoration after SCI.
Seventeen Adult female rats (Sprague–Dawley, 250–300 g body weight) were used in this study. All rats were implanted with stimulating electrodes epidurally at T8 and S1 spinal cord levels and EMG electrodes implanted in the hind limb muscles tibialis anterior (TA) and medial gastrocnemius (MG). The groups studied include, (1) rats implanted with EES electrodes but no Scaffold and received EES (EES only; n = 4), (2) rats implanted with EES electrodes and scaffold but received no EES (scaffold only; n = 3) and (3) rats implanted with EES electrodes and scaffold and received EES-enabled motor training (combined therapy; n = 10). In order to study the functional effect of fibers regenerated across the scaffold, group 3 animals were re-transected 6 weeks after complete SCI at level T9.
The rats were deeply anesthetized by a combination of ketamine (100 mg/kg) and Xylazine (10 mg/kg) administered intraperitoneally (IP) and maintained at a surgical level with supplemental doses of ketamine as needed. Buprenorphine was administered as a single dose at the beginning of the experiment. All surgeries were performed under aseptic conditions. All procedures involving animals were approved by the Mayo Clinic Institutional Animal Care and Use Committee and all guidelines were followed in accordance with the National Institute of Health as well as Institute for Laboratory Animal Research and the United States Public Health Services Policy on the Humane Care and Use of Laboratory Animals.
Electromyography wire and electrode implants for SCI rats
A small skin incision was made at the midline of the skull. The muscles and fascia were retracted laterally, and the skull was thoroughly dried. A 12-pin Omnetics circular connector (Omnetics, Minneapolis, MN) and 12 Teflon-coated stainless-steel wires (AS632, Cooner Wire, CA) were attached to the skull with screws and dental cement as previously described10,73,104. Skin and fascia incisions were made to expose the bellies of the MG and TA muscles bilaterally. Using hemostats, the EMG wires were routed subcutaneously from the back incision to the appropriate locations in the hind-limb. Bipolar intramuscular EMG electrodes were inserted into the muscles as described previously73,104. The EMG wires were coiled near each implant site to provide stress relief. Electrical stimulation through the head-plug was used to visually verify the proper response of the electrodes in each muscle73. A partial laminectomy was then performed at the L2 vertebral level (S1 spinal segment) and one wire was affixed to the dura at the midline using 9.0 sutures as previously described10. A small notch made in the Teflon coating (about 0.5–1.0 mm) of the wire used for EES was placed toward the spinal cord and served as the stimulating electrode. Another laminectomy was performed to expose the area for implantation of the electrode at T8 spinal segment. The wire was coiled in the back region to provide stress relief. Teflon coating (about 1 cm) was stripped from the distal centimeter of one wire that was inserted subcutaneously in the back region and served as a common ground12,73.
Poly-lactic-co-glycolic acid (PLGA)-rapamycin microsphere fabrication
Microspheres fabricated from PLGA were used to slowly elute the antifibrotic drug rapamycin. The polymer used to form the PLGA microspheres was 50:50 lactic acid to glycolic acid with 29 kDA molecular weight (Resomer RG 503 H; Sigma-Aldrich). An oil-in-water emulsion with solvent evaporation technique as previous described39,105,106. Briefly, 1 mg of rapamycin was dissolved in 100 µL of absolute ethanol. The rapamycin-ethanol solution vortex emulsified dropwise for 30 s in 250 mg PLGA dissolved in 1 mL of methylene chloride. The mixture was then emulsified in 2 mL of 2% (w/v) poly vinyl alcohol for 30 s. This solution was then mixed with 100 mL of 0.3% (w/v) poly vinyl alcohol and 100 mL of 2% (w/v) isopropanol and stirred for 1 h to evaporate methylene chloride. The microspheres are then centrifuged at 2000 rpm for 3 min and washed three times with distilled water and centrifugation. The liquid is then discarded, and the microspheres are frozen at −80 °C for 1 h. Lastly, the microspheres are dried overnight under vacuum and then used for scaffold manufacture.
Positively charged OPF+ scaffolds with seven channels (Fig. 1a; and Supplementary Fig. 2) were fabricated as previously described39,107,108. Briefly, the liquid polymer consists of 1 g of OPF macromere (16,246 g/mol) dissolved in 650 µL of deionized water, 0.05% (w/w) photoinitiator (Irgacure 2959; Ciba Specialty Chemicals) 0.3 g N-vinyl pyrrolidinone (NVP; Sigma), and 20% [2-(methacryloyloxy) ethyl]-trimethylammonium chloride (MAETAC; Sigma). To embed the rapamycin microspheres, 25 mg of microspheres was stirred into 250 µL of OPF+ polymer liquid. The liquid polymer containing the microspheres is then mold injected over seven equally spaced wires with 290 µm diameter in a glass cylinder. After 1 h exposure the UV light (365 nm) ay 8 mW/cm2, the individual scaffolds are cut into 2 mm lengths. Before use, they are serially washed in ethanol three times for 30 min each followed by 4 1× PBS washes39.
The characteristics of this scaffold have been described in earlier studies27,39,58. Briefly, the OPF+ hydrogel has a compression moduli of 0.13 ± 0.03 MPa and flexural moduli of 1.87 ± 1.03 MPa, which was similar to the rat spinal cord compression moduli of 0.19 ± 0.09 MPa and flexural moduli of 0.74 ± 0.14 MPa27. There is a weight loss of 14% for OPF+ in PBS after 5 weeks, showing a slow degradation rate due to the highly crosslinked structure58. The PGLA microspheres were found to be of a mean diameter of 57.42 ± 17.63 μm58. The encapsulation efficiency of rapamycin was 100 ± 10% for a loading dose of 1 mg/250 mg PLGA39. The release kinetics in vitro of rapamycin from PLGA microspheres were found to be a burst release in the first week (approximately 25%), following by a slower release over the second week (approximately 10%), and steady release of rest of the contents over the next 3 weeks39.
Primary and GDNF-secreting Schwann cells
Glial derived neurotrophic factor (GDNF, accession: NM_000514) secreting SCs were created as described previously57. Briefly, primary rat SCs were harvested from the sciatic nerve of Sprague Dawley pups between postnatal day 2 and 5. The nerves are stripped of connective tissue and the epineurium and cut into 1 mm sections. Then are enzymatically treated with 0.25% trypsin EDTA (Mediatech Inc.) and 0.03% collagenase (Sigma). The cells are mechanically dissociated by pipetting and centrifuges for 5 min at 188G. The primary SCs were then genetically modified by seeding 80,000 cells/mL and grown with high titer (2 × 1010 cfu) retroviral (GDNF-eGFP) supernatant media with 8 µg/mL polybrene for 24 h. Transduced SCs were selected for 12 days with 1 mg/mL G418 analog in SC media containing 50:50 DMEM: F12 media (GIBCO) supplemented with 10% FBS, 1% antibiotic–antimycotic, 2 µM Froskilin (Sigma), and 10 ng/mL neuregulin-1 (recombinant human NRG-1; R&D Systems)) at 37 °C in 5% CO2. The cells were expanded and frozen until ready for use.
Sterile RAPA-OPF+ scaffolds were loaded with GDNF-SC at a density of 100,000 cells/μL suspended in Matrigel (BD Biosciences) using gel loading pipette tips as previous described38. The internal volume of channels the scaffolds are 0.67 μL, therefore the total amount of cells loaded into the scaffold were 476,000 cells. The loaded scaffolds were incubated for 48 h at 37 °C in 5% CO2 before implantation into animals.
Spinal cord transection and scaffold implantation
One week after electrode implantation surgery, a complete spinal cord transection was performed. Rats were anaesthetized with a mixture of oxygen and Isoflurane (≈1.5%). Mid-dorsal skin incision was made between T6 and L4 and the paravertebral muscles were retracted as needed. A partial laminectomy was performed at the T9 level and the dura was opened longitudinally. Lidocaine was applied locally and the spinal cord was completely transected using a microscissors. Completeness of the lesion was verified by two surgeons under microscope. The spinal cord retracted as a result of the transection resulting in a 2 mm gap (Supplementary Fig. 2D). Then, some rats were implanted with 2 mm GDNF/SC-RAPA-OPF+ scaffold in the space created by transection (Supplementary Fig. 2E) with the channels aligned with the rostral and caudal stumps as previously described27. Tight contact in between the stumps were confirmed through observation under a surgical microscope. The muscle was sutured with a deep tight first suture over the scaffold in order to hold it in place. Buprenorphine (0.5–1.0 mg/kg subcutaneous injections twice a day) were administered for analgesia. Tissues were sutured by layers and animals were allowed to recover in individual cages with soft bedding. Manual bladder expression was performed four times daily for two weeks post transection. Similar to our previous studies with complete SCI, about 2 weeks after injury rats have regained bladder function and then were monitored twice daily 5 days a week for the duration of the study. The rats that demonstrated delayed in bladder functions recovery were continued to be manually expressed 4 times daily until the function has recovered. The rats were allowed to move over an open field surface to help stimulate their bladder and reflexes once daily for 2 weeks. The hind limbs of the spinal rats were also moved passively through a full range of motion once per day to maintain joint mobility.
Spinal cord electrical epidural stimulation
A single channel manually controllable isolated stimulator (A-M systems, Sequim, WA) or an eight independent channel real-time programmable (STG4008, Multichannel Systems, Reutlingen) stimulator were used to deliver biphasic square wave electrical stimulation (250 μs pulse width) at 40 Hz with amplitudes ranging from 0.5 to 2.5 V to the epidural electrode placed on the rat’s lumbosacral (S1) spinal cord to facilitate motor activity.
Training and animal care
Rats were acclimated to a specially designed motor-driven rodent treadmill and body weight support system92 for a period of 7 days prior to surgery for 15–20 min each day (Fig. 1b). One week post-surgery, the rats went through a manual bipedal step training rehabilitation process (30 min a day, 3 days a week) for 6 weeks under the influence of EES at 40 Hz subthreshold level (0.4–2 V). Chronic step training was used because it helps to engage and reinforce the locomotor networks.
Basso, Bettie, and Bresnahan (BBB) assessment
The BBB locomotor rating scale was used to access the hind-limb function weekly starting one-week post-injury (Fig. 1c). Three independent observers were blinded to the animal groups and score was given on the 21-point scale. The BBB scoring was performed as previously described93, except that the animals were scored twice with and without subthreshold EES (40 Hz). At least 30 min of rest was given between the sessions. The BBB scores from the independent observers were averaged and then the left and right limb scores were averaged for each rat. Two-way ANOVA with Tukey’s multiple comparisons was used to determine statistical difference between groups.
A motion tracking system (Vicon, UK) was used to record three-dimensional digital position of back and the hind limb joints at 100 Hz. Six motion-sensitive Infrared (IR) cameras were aimed at the treadmill or the open field volumes. Another high-speed video camera synchronized with motion tracking system was positioned in a side to provide a lateral view of the motor performance. Retro-reflective markers were placed on bony landmarks at the iliac crest, greater trochanter, lateral condyle of the femur, lateral malleolus and the distal end of the fifth metatarsal on both legs of the rat to record the kinematics of the hip, knee, and ankle joints. Nexus system was used to obtain three-dimensional coordinates of the markers. Analysis of kinematic data was performed using method previously described92.
EMG activity was collected from TA and MG muscles on both legs at 4000 Hz during stepping and later high-pass filtered at 0.5 Hz to remove direct current offset. In order to determine flexor (TA) and extensor (MG) coordination, EMG signals were band pass filtered (10–1000 Hz), rectified, normalized and plotted on X and Y axis consecutively92. The excitability of the spinal cord were determined by stimulating the spinal cord at S1 spinal level while SCMEP were recorded from the hind-limb muscles via EMG73, while the rats were suspended in the body weight support system92. The functional connectivity across the injury and reflexes below the injury were tested by stimulating T8 spinal level above the injury, while recording SEPR from hindlimb muscles. During testing, the rats were suspended allowing hind limbs to freely respond and stimuli of increasing intensity (amplitude 0.5–4.5 V, pulse width 0.25 ms, frequency 0.5 Hz) were applied to epidural spinal electrodes. Ten consecutive responses were collected during spinal cord stimulation above (T8) and below (S1) the injury with a single pulse to evaluate SEPR and SCMEP in awake animals to assess the influence of information delivered across scaffold during standing and during stepping on a treadmill.
Perfusion and dissection
Seven weeks of post-injury that rats were transcardially perfused using 4% paraformaldehyde (PFA) in phosphate buffered saline (PBS). The spinal column was removed en block and post-fixed in 4% PFA in PBS for 2 days at 4 °C. The spinal columns were then washed three times in PBS and dissected out. Then 6 mm segment containing the scaffold at the center and adjacent spinal cord was embedded in paraffin. A 1 cm block covering L2-S1 spinal cord segment was also embedded in paraffin. Transverse or longitudinal serial sections of 10 μm thick were made on a Reichert-Jung 23 Biocut microtome (Leica, Bannockburn, IL) of the scaffold and spinal cord areas.
Post-mortem immunohistochemistry was performed in all groups of animals in order to assess regeneration through the scaffold and plasticity change in lumbosacral spinal cord (Fig. 1d). Primary antibodies used were against β-III tubulin (Tuj-1; mouse anti-rat, 1:300; Millipore), choline acetyltransferase (ChAT; goat anti-rat. 1:50, Millipore), calbindin (CB38; rabbit, 1:1000, SWANT), and synaptophysin (mouse, 1:50, Abcam). The secondary antibodies used were against mouse Cy3 (donkey, 1:200, Jackson ImmunoResearch Laboratories), goat Alexa 647 (donkey, 1:200, Jackson ImmunoResearch Laboratories), rabbit Cy2 (donkey, 1:200, Jackson ImmunoResearch Laboratories). The slides were deparaffinized through serial washes through xylene, ethanol, and distilled water. Antigen retrieval was performed through incubation in 1 mM EDTA in PBS for 30 min in a rice steamer. The sections were then blocked using 10% normal donkey serum in 0.3% Triton X-100 in PBS for 1 h. Next, TrueBlack (Biotium) was used as per manufacturer’s instructions to quench autofluorescence due to lipofuscin. Then, the sections were incubated overnight in the primary antibody diluted in 5% normal donkey serum in PBS at 4 °C. The next day after three washes in PBS, the sections were incubated in secondary antibody diluted in PBS containing 5% normal donkey serum for 1 h at room temperature. Lastly, the sections were washed three times in PBS containing, and then mounted with SlowFade Gold Antifade Reagent with DAPI (Molecular Probes, Eugene, Oregon, USA).
Axons were identified as punctate staining of β-III tubulin and were counted in transverse paraffin sections at quarter lengths throughout the scaffold. Tiled 20× images of the whole scaffold were imaged using a Zeiss LSM 780 inverted confocal microscope. StereoInvestigator software suite (MBF) was used to count the axons in each channel using Optical Fraction Probe. Briefly, a square grid measuring 100 µm × 100 µm was overlaid on the image after contouring around the channel. The axon was counted if it fell either in the quadrant frame or overlapped with the acceptance lines (top horizontal and right vertical boundary). The average axon counts per channel for each quarter length were averaged yielding one value per animal. The total axon counts of rats with scaffolds and with/without EES were compared using two sample t-test.
Colocalization of synaptophysin with neuronal populations
Antibody against ChAT was used to identify motor neuron populations, while Calbindin was used to identify interneuron subtype on sections taken from transverse and longitudinal spinal cords between spinal segments L2-S1. The co-localization tool in Image-Pro (Media Cybernetics) was used to determine the amount of overlap of synaptophysin with ChAT or Calbindin according to manufacturer’s instructions. The synaptophysin labeled presynaptic boutons interacting with these cell types. Color pairs were created between the red (synaptophysin) and green (Calbindin) channels and the red and far red channels (ChAT). A threshold was applied using the auto-bright feature. The process was standardized and automated to have consistent, unbiased analysis. The analysis was done using 40× images taken on a Zeiss LSM 780 inverted confocal microscope serially through the lumbosacral spinal cord every 1500 µm. On each slide two sections 20 µm apart were chosen and on each section four areas were chosen and titled: the left and right dorsal horn and ventral horn (Supplementary Fig. 3A). The areas of interest were then averaged per section, the two sections per slide were averaged, and then all the slides were averaged to yield one average per animal. The amount of co-localization was compared between animals with scaffolds and EES that were re-transected, scaffold only, and no scaffold and EES using a one-way ANOVA with Tukey’s multiple comparisons.
Distribution of synaptophysin boutons on ChAT+ and calbindin+ cell bodies was analyzed using a semiautomated image analysis system on the QuPATH open source software109 with the images described above. The cell bodies labeled with ChAT or calbindin were first traced (Supplementary Fig. 3B). The cell area of the traced space was recorded. Then the cell detection tool was used to identify the synaptophysin boutons. The detection channel was set for the red channel and then optimized parameters were used (requested pixel size 0 µm, background radius 0 µm, median filter radius 1 µm, sigma 0.5 µm, minimal area 0.01 µm2, maximum area 5 µm2, threshold 30). The number of synaptophysin boutons per neuron were normalized to cell body area and all the neurons were plotted. Then the median with upper 95% confidence interval (CIU) and lower 95% confidence interval (CIL) was used to indicate the peak of the distribution. Kruskal–Wallis test with Dunn’s multiple comparison was used to analyze the distribution.
Statistical analysis was performed using SigmaPlot (Systat Software, UK) or Prism (GraphPad). The data were first tested for normality and then one-way Analysis of Variance (ANOVA) was performed to determine if the groups had different outcomes. If the groups were found significantly different (p < 0.05) a post-hoc analysis was performed using Holm-Sidak method (unless otherwise stated) to compare against control and p values were reported. When compared between two groups, two samples t-test was performed. All results were reported as mean ± standard error, and *,#,$p < 0.05, **,##,$$p < 0.01, and ***,###,$$$p < 0.001, unless otherwise noted. Nonparametric analysis was done using Kruskal–Wallis test with Dunn’s multiple comparison. Two-way ANOVA with Tukey’s multiple comparisons was done where there were multiple groups and conditions.
Further information on research design is available in the Nature Research Reporting Summary linked to this article.
All data is available on reasonable request.
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This work was generously funded by Minnesota State Office for Higher Education Spinal Cord Injury and Traumatic Brain Injury Research Grant Program (FP00093993), North American Spine Society, Morton Cure Paralysis Fund, and the Bowen Foundation.
The authors declare no competing interests.
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Siddiqui, A.M., Islam, R., Cuellar, C.A. et al. Newly regenerated axons via scaffolds promote sub-lesional reorganization and motor recovery with epidural electrical stimulation. npj Regen Med 6, 66 (2021). https://doi.org/10.1038/s41536-021-00176-6
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