- Research article
- Open Access
A safety study of 500 μA cathodal transcranial direct current stimulation in rat
BMC Neuroscience volume 20, Article number: 40 (2019)
Transcranial direct current stimulation (tDCS) is a noninvasive neural control technology that has become a research hotspot. To facilitate further research of tDCS, the biosafety of 500 μA cathodal tDCS, a controversial parameter in rats was evaluated.
24 animals were randomly divided into two groups: a cathodal tDCS group (tDCS, n = 12) and control group (control, n = 12). Animals in the tDCS group received 5 consecutive days of cathodal tDCS (500 μA, 15 min, once per day) followed by a tDCS-free interval of 2 days and 5 additional days of stimulation, totally two treatments of tDCS for a total of 10 days. Computational 3D rat model was adopted to calculate the current density distributions in brain during tDCS treatment. Essential brain functions including motor function and learning and memory ability were evaluated. Additionally, to estimate the neurotoxicity of tDCS, the brain morphology, neurotransmitter levels and cerebral temperature were investigated. Our results showed that the current density inside the brain was less than 20 A/m2 during tDCS treatment in computational model. tDCS did not affect motor functions and learning and memory ability after tDCS treatment. In addition, no significant differences were found for the tDCS group in hematology, serum biochemical markers or the morphology of major organs. Moreover, tDCS treatment had no effect on the brain morphology, neural structures, neurotransmitter levels or cerebral temperature.
500 μA cathodal tDCS as performed in the present study was safe for rodents.
Transcranial direct current stimulation (tDCS) is a noninvasive neural control technology that has been increasingly tested as a tool to modulate plasticity in neuropsychiatric diseases [1,2,3,4]. As reported recently, clinical tDCS trials induce beneficial effects in several neurological and psychiatric contexts including pain , motor rehabilitation , chronic stroke , cognitive function , major depression , and epilepsy . Although tDCS has exhibited therapeutic potential and application prospect in clinical trials, its mechanism remains largely unclear.
To facilitate further research of tDCS, it is important to confirm the biosafety of tDCS. Furthermore, as tDCS paradigms employing increased intensities or prolonged stimulation durations are developed, it is necessary to update the safety thresholds. At present, in human studies, relatively large wet sponges (typically 25–35 cm2) are commonly used. Based on a total of more than 33,000 sessions in over 1000 subjects , there has been no evidence for irreversible injury produced by conventional tDCS protocols within a wide range of stimulation parameters (stimulation duration ≤ 40 min, current ≤ 4 mA and conventional charge ≤ 7.2 C). In rats, the safety of tDCS has been more controversial. Liebetanz and colleagues  reported that brain lesions were observed at a current strength of 500 μA in cathodal tDCS with a duration of 10 min, which corresponds to a charge density of 85,714 C/m2 based on the epicranial electrode area of 3.5 mm2. Charge density was commonly used as an important index for definition of tDCS safety threshold. If brain lesions were observed at a certain charge density, this charge density would be defined as the safety threshold. However, recent studies have shown that a current strength of 500 μA over a duration of 15 min were used in cathodal tDCS is safe for rats [13, 14], which corresponds to a charge density of 128,571 C/m2 based on the epicranial electrode area of 3.5 mm2. Accordingly, the safety threshold for tDCS charge density has been increased to at least 128,571 C/m2, despite the fact that Liebetanz and colleagues  consider these levels to be harmful to the rodent brain.
To confirm safety thresholds for tDCS, the biosafety of 500 μA cathodal tDCS was evaluated by observing behavioral changes and neurotoxicology after tDCS administration in rats. Additionally, considering that electricity can flow through the body during tDCS process, general animal health and non-brain organs were also evaluated.
Currents distributions in computational rat model
As shown in Fig. 1a, the typical slice layers at the coordinates: Coronal plane, y = 52 mm, which contain the rat brain. The tissue distribution such as skin, brain, skull, fat and muscle were shown in Fig. 1b. The current density in rat model during tDCS treatment was shown in Fig. 1c and Additional file 1. As we can see, the current density varied from different rat tissues, and the current density inside the brain was less than 20 A/m2 and skull was 40–60 A/m2 in computational model.
500 μA cathodal tDCS had no obvious effects on motor function
Motor function did not differ between controls and the tDCS group on either the OFT (which assessed locomotor activity) or the rotarod test (which assessed athletic endurance). Relative to the control group, the tDCS group exhibited no obvious effects from epicranial electrode implantation on total distance traveled in the OFT at the BEFORE timepoint. Similarly, distance traveled did not change in the ERLY, MID and POST phases (Fig. 2a and Additional file 2). Moreover, retention time on the ratarod, a symbol of athletic endurance, exhibited no difference between these two groups (Fig. 2b, c and Additional file 3). In addition, no relationship was found between motor function and cumulative stimulation time. This null finding suggested that the bio-effect of cathodal tDCS did not have significant cumulative effects on animals’ motor behavior in present parameter.
500 μA cathodal tDCS had no discernible effects on learning and memory ability
Learning and memory, which are among the most important brain functions, were evaluated with the MWM. Learning was assessed during the spatial acquisition phases. Our data showed that escape latency to the hidden platform continued to decrease after the first trial in each session, with significant differences observed between the first acquisition day and days 2–7 (p < 0.05). This difference indicated that rats had learned the location of the platform on the second day. However, escape latency increased on the eighth acquisition day relative to the seventh (p < 0.05). This increase may be due to the inclusion of multi-probe trials, i.e., the sudden removal of the platform led to a disorder of spatial memory (Fig. 2d and Additional file 4). On probe trials, durations in the target quadrant, a symbol of reference memory, displayed a similar tendency to durations measured during the spatial acquisition phase (Fig. 2e and Additional file 5). However, no significant differences were found between the tDCS and control groups in either the learning or recall phase.
500 μA cathodal tDCS had no obvious effects on hematology and serum biochemical markers
Hematology and serum biochemical markers are common physiological indexes that were used to evaluate the health of animals. The number of WBC and PLT, the percentage of LYM and GRA, and the concentration of HGB were assessed by hematology analysis. These indexes displayed no significant differences between the tDCS and control groups (Fig. 3a and Additional file 6). Concentrations of serum biochemical markers for liver function (Fig. 3b and Additional file 7) such as ALT, AST, ALP, TBILI and ALB exhibited no remarkable changes after tDCS treatment. A similar result was obtained for serum biochemical markers of kidney function (Fig. 3c and Additional file 8): Namely, concentrations of Scr, BUN and Cys C in the tDCS group did not significantly differ from those of the control group.
500 μA cathodal tDCS had no effect on the morphology of major organs
Histological examination of the brain, heart, lung, liver, kidney and spleen were performed to verify whether 500 μA of cathodal tDCS administration for 10 days resulted in morphological change. After 500 μA cathodal tDCS, histological analysis revealed that none of the rats had suffered from a cortical lesion (Fig. 4a–c). In addition, as one of neural characteristic structures, the Nissl bodies in brain were also observed in this study. It was found that the shape and density of intraneural Nissl bodies in cortex and hippocampus did not change compared with control group (Fig. 4d, e and Additional file 9), which was consistent with the results of the behavior assessment. What’s more, no epileptic seizures were observed during the stimulation period. Additionally, the morphology of other major organs did not obviously change after tDCS treatment compared with the control group, as shown in Fig. 4f–j.
500 μA cathodal tDCS had no effect on brain neurotransmitter levels
Both excitatory (GLU and ASP) and inhibitory amino acids (GABA, GLY and ALA) play important roles in the modulation of neural activity. Therefore, in the present study we assessed all of these molecules using LC–MS chromatograms. Excitatory and inhibitory neurotransmitters in the tDCS group did not significantly differ in either the contralateral or ipsilateral hippocampus and cortex, compared with the control group (Fig. 5 and Additional file 10).
500 μA cathodal tDCS had no effects on cerebral temperature
In the present study, cerebral temperatures detected by thermal imaging after 15 min of cathodal tDCS exhibited no significant difference between the control and tDCS groups either when averaged over the entire cortex or when measured under the stimulation site. Furthermore, temperatures at the stimulation site did not significantly rise with increased stimulation time (Fig. 6a–c and Additional file 11).
tDCS is a powerful brain modulation tool validated by an increasing number of studies. tDCS treatment may lead to neuromodulation and lasting changes in cortical excitability. Although tDCS has demonstrated therapeutic potential, little is known about potential harmful effects of continuous weak direct current stimulation. Tissue heating (burning) through joule heat has been proposed as a probable mechanism for damage. Such heating is linearly dependent on charge density but is polarity-independent, assuming a linear relation between charge density (current density × time) and lesion size [12, 15]. We chose cathodal tDCS instead of anodal tDCS in the present study because cathodal tDCS has been shown to be effective in a range of neurological diseases [13, 14, 16, 17], and because the safety of 500 μA cathodal tDCS has remained controversial in rats [12,13,14].
As we know, protein denaturation usually occurs when the temperature of tissue is above 43 °C. Bikson et al.  reported that a tDCS charge density of 85,714 C/m2 would theoretically increase the temperature of brain tissue to 47.75 °C, in this case, probably it would lead to brain lesions. In the present study, a charge density of 128,571 C/m2 was applied; according to the theory of Bikson and colleagues , this density would induce much higher temperature and cause more obvious histopathological brain damage. However, no brain damage under the stimulation site was found, which were probably due to the complicated temperature self-regulating mechanism of living body, as well as the environmental temperature and the type of stimulating electrode. In addition, it was found that the current density in brain tissue (< 20 A/m2) and skull (40–60 A/m2) calculated by a computational model was much lower than that calculated with the formula (142.9 A/m2) . We also found that the current density was different even in the same tissue but different spatial positions, which indicated that the charge density (current density × time) merely calculated by the formula in theory without taking these elements into consideration was unreasonable. In a previous study , tDCS was applied transcranially to the frontal cortex with 500 μA for 15 min, brain lesions were detected. However, in other studies [13, 14] and our study, no brain lesions were found after tDCS treatment on motor cortex with the same paremeters (500 μA for 15 min). Therefore, the position of stimulating electrode implanted may be a vital factor for safety evaluation. Besides, much higher current density distribution was found in skull instead of brain, which indicated that more joule heat generated in skull than that in brain tissue. Considering the previous reports that brain lesion occurred only in cortex under the skull where the stimulating electrode was implanted , we speculated that it was the joule heat produced in skull instead of in brain tissue itself caused the brain lesion.
Prior studies have reported that current injected into the brain during tDCS is diffused by the skull. Thus, the current is not focused on the brain surface [18, 19], which may lead to a weaker actual current. Other research has demonstrated that sponge electrodes can achieve better current on the scalp near the sponge edges [18, 20]. Additionally, a counter electrode with a large contact area placed on the ventral thorax creates an asymmetric current density with highest density directly beneath the epicranial electrode . In this study, the similar electrode material to Liebetanz’s group  was used, but the contact area of our counter electrode placed on the ventral thorax was a little smaller (7 cm2) than Liebetanz’s group (10 cm2). Considering the inconsistent reulsts of biosafety of tDCS on brain between Liebetanz’s study and ours, the contact area of counter electrode should be considered. These findings indicated that the geometry and materials of tDCS play an important role in its biosafety and a recognized standard should be established for tDCS study.
Essential brain functions including motor function and learning and memory ability were not significantly affected by cathodal tDCS administration in present parameter (500 μA, 15 min, once per day, totally for 10 days). However, a robust meta-analysis indicated that anodal tDCS had significantly positive effects on cognitive and motor function in healthy older adults over a variety of experimental tasks . Additionally, cathodal tDCS may exert positive effects on functional recovery after stroke; such recovery involves neurogenesis, oligodendrocyte precursor recruitment, and microglial polarization . The inconsistency of the present results with the literature may be due to differences in the modulatory effect of tDCS, selected parameters, position of the implanted stimulating electrode, or even the composition of study samples (e.g., mice, rats or humans).
This study assessed not only the effect of cathodal tDCS on the brain but also on animals’ physiological health. Such health-related outcomes have been largely ignored in previous research. Although it is well understood that current from tDCS flows through the entire body, the effects of this current have only been evaluated in the brain; whether the current is beneficial or harmful to other organs has remained unknown. Therefore, the current study assessed the morphology of major organs and selected physiological indexes. No morphological effects were observed in the brain, heart or other major organs. Similarly, no obvious change was found in hematology and serum biochemical markers. These results suggested that the cathodal tDCS protocol used in the current study does not affect the health of animals.
Additionally, levels of neurotransmitters and Nissl bodies in the brain were determined to evaluate potential brain damage after tDCS treatment. Neither the level of excitatory and inhibitory neurotransmitters, nor the Nissl bodies in cortex and hippocampus were affected by cathodal tDCS, which was consistent with the behavioral results. However, Peruzzotti-Jametti et al. reported decreases in cortical GLU and ALA after cathodal tDCS treatment in mice , indicating that tDCS may promote efficient conversion of GLU into glutamine . Inconsistencies between the results of our study and the previous report may be due to the differences of the experimental animals, tDCS duration and tDCS site.
In conclusion, our results demonstrated that 500 μA cathodal tDCS had no effects on the behavior of adult male rats, including locomotor activity, athletic endurance and spatial learning and memory. Moreover, hematology indexes, serum biochemical markers and brain neurotransmitters were not altered by tDCS treatment. Furthermore, tDCS did not affect the major organs’ morphology and cerebral temperature. The data suggested that 500 μA cathodal tDCS performed in present study was safe for rodents.
Animals and groups
Male Sprague–Dawley rats (260–280 g) purchased from the Laboratory Animal Center of the Fourth Military Medical University (Xi’an, China) were housed in a temperature-controlled room in plastic cages (3 animals per cage) with free access to food and water at 22–25 °C on a 12 h light/dark cycle. We selected 24 animals that were capable of running continuously on the rotarod for a minimum of 300 s at 4 rpm. These animals were randomly divided into two groups: a cathodal tDCS group (tDCS, n = 12) and control group (control, n = 12). All experiments reported in this study were conducted according to an experimental protocol approved by the Animal Use and Care Committee for Research and Education of Fourth Military Medical University (NO. 20170607). After experiments, animals were deeply anesthetized by intraperitoneal injection of pentobarbital (60 mg/kg) to minimize the pain of the animals.
Three days before the administration of tDCS, epicranial electrode implantation was carried out in rats under 1% pentobarbital sodium anesthesia (45 mg/kg i.p.). After removal of the scalp and underlying tissues, an epicranial electrode with a defined contact area of 3.5 mm2 was mounted on the intact skull at the coordinates bregma AP + 2.0 mm, ML + 2.0 mm using glass ionomer dental cement (Ketac Cem, ESPE Dental AG, Seefeld, Germany). This electrode remained in place for the duration of the experiment. The counter electrode, a large conventional rubber plate electrode (7 cm2, Ai Kang Technology, China), was placed onto the ventral thorax of the unrestrained animal using a corset as previously described . Animals received 5 consecutive days of tDCS (500 μA, 15 min, once per day) followed by a tDCS-free interval of 2 days and 5 additional days of stimulation. Thus, tDCS administration comprised 10 days in total; this duration has been frequently adopted in studies of therapeutic tDCS effects on disease states [13, 14].
Prior to tDCS, the stimulation electrode was filled with saline solution (0.9% NaCl) to reduce the skull impedance . To avoid stimulation break effects, the current intensity was automatically ramped up and down over a 10 s period instead of being switched on and off abruptly . tDCS was applied continuously for 15 min at a current strength of 500 μA using a constant current stimulator (PMP18-3TR, Kikusui, Japan), resulting in a charge density of 128,571 C/m2. Notably, animals were maintained in an awake state during tDCS to avoid possible interactions between tDCS and anesthetic. Prior research has reported interactions of tDCS with benzodiazepines and another antidepressant drugs . Furthermore, stimulation in awake rats may mimic the clinical application of tDCS.
In this study, a 3D rat model obtained from Brooks Fourth Military Laboratory (BAFL) was used to calculate the current density distributions in rat brain during tDCS treatment. The model has 36 different tissues with voxel size 0.5 mm × 1 mm × 0.5 mm. The electrical properties of head tissues were modeled using the 4-Cole–Cole method and obtained by fitting to experimental measurements . The currents distributions in rat model was calculated by the impedance method . In brief, the rat model was described by using a uniform 3D Cartesian grid and was composed of small cubic voxels. There are nearly seven million voxels in the computational space. Assuming that, in each voxel, the electric conductivities are isotropic and constant in all directions, the model was represented as a 3D network of impedances. Kirchhoff voltage law applied in this network generates a system of equations for the loop currents. These loops currents were driven by the injected current from the tDCS electrodes. The net currents and current density within the rat model are then calculated from these loop currents, and the electric field are in turn calculated using Ohm’s Law.
Open field test
Immediately after tDCS administration, the open field test (OFT) was conducted blindly to evaluate locomotor activity . Rats were gently placed at the center of the open field device (100 cm × 100 cm × 40 cm) with their backs towards the investigator. Each rat was allowed to explore freely for 5 min. Movement traces and total distance moved were recorded and automatically analyzed by the Noldus Ethovision XT 5 video tracking system. Prior to each testing session, animals were habituated to the testing environment for at least 30 min. The device was wiped with 70% ethanol and disposable absorbent paper before each rat was tested. During testing, light and sound cues were controlled to prevent these cues from influencing the results. A baseline measure of total distance traveled was acquired 2 days before tDCS administration (BEFORE). The OFT was conducted three times during the tDCS administration period: once each in the early phase (ERLY, immediately after 2 days of tDCS), middle phase (MID, 24 h after the fifth day of tDCS) and post-stimulation phase (POST, immediately after the tenth day of tDCS).
Immediately after OFT detection, about 1.5 h after tDCS administration, athletic endurance was evaluated with a rotarod treadmill for rats (Ugo Basile, Italy), under the accelerating rotor mode (10 speeds from 4 to 40 rpm for 5 min) as previously described . The duration from the time the animal mounted the rod to the time it fell off was recorded as the performance time. Performance on the rotarod test was measured 5 times per day with a minimum interval between two trials of 10 min to ensure energy recovery. Animals were trained for 5 trials per day at the speed of 4 rpm for 3 days before tDCS administration, and baseline performance (BEFORE) was recorded on the last training day. Like the OFT, the rotarod test was performed in the ERLY, MID and POST phases.
Morris water maze test
After rotarod test, animals were allowed to rest for 2 h, and then about 5 h after tDCS administration, the Morris water maze (MWM) test was administered under dim white light in a black plastic pool 150 cm in diameter. Rats were trained for 5 days consecutively. Each animal received 4 trials per day from different randomly-selected quadrants with target location remain constant; the latency to reach the platform was recorded . Rats were allowed to swim until they reached the platform or until 60 s had elapsed. Rats who were unable to locate the MWM platform within the allotted time were led to the platform by the experimenter. Rats were allowed to remain on the platform for 15 s and then removed from the pool. The interval between trials was at least 10 min, and animals were placed in holding cages in front of an air heater. To assess reference memory at the end of learning, a probe trial was given 24 h after the last acquisition day from the quadrant contralateral to target quadrant. During the probe trial the platform was removed, and the duration in the target quadrant was measured; this observation served as the baseline (BEFORE). We note that 24 h before the probe trial in ERLY, MID and POST phases, an extra spatial acquisition training was performed. Prior to performance, the animals were habituated to the testing environment for at least 30 min and the water temperature was equilibrated to room temperature (23 °C).
Hematological analysis and serum biochemical marker assay
After 10 days of tDCS administration, animals were deeply anesthetized by intraperitoneal injection of pentobarbital (60 mg/kg), and blood samples were taken from the left ventricle of the heart. Samples of 1 ml were collected in EDTA-K2 vacuum tubes (Boyi Medical Equipment Company, Shandong, China). Hematological analysis was performed with an automated hematology analyzer (XE-2100, Sysmex, Tokyo, Japan) and the number of white blood cells (WBC) and platelets (PLT), the percentage of lymphocytes (LYM) and neutrophile granulocytes (GRA), and the concentration of hemoglobin (HGB) were detected. Additionally, 3 ml of serum was collected from blood after centrifugation at 3000 rpm for 10 min at 4 °C. Serum biochemical markers including markers of liver and kidney function, such as alanine aminotransferase (ALT), aspartate transaminase (AST), alkaline phosphatase (ALP), total bilirubin (TBILI), albumin (ALB) serum creatinine (Scr), blood urea nitrogen (BUN) and cystatin C (Cys C), were detected by commercial kits and a multifunctional biochemistry analyzer (AU600; Olympus, Tokyo, Japan) according to the manufacturer’s instructions.
HE staining and Nissl’s staining
After the collection of blood samples, animals were immediately transcardially perfused with 200 ml of 5 mM sodium phosphate-buffered 0.9% (w/v) saline (PBS, pH 7.2–7.4) and 4% paraformaldehyde in a phosphate buffer (0.1 M, pH 7.4). The major organs, including the brain, heart, lung, liver, kidney and spleen, were embedded in paraffin. Continuous 4 μm thick horizontal slices were obtained. For hematoxylin and eosin (HE) staining, the sections were dipped in hematoxylin for 3 min, washed in running tap water until the sections appeared blue to the naked eyes, and destained in hydrochloric acid alcohol for several seconds. The sections were washed again in running water for 10 min and dipped in eosin for 15 s prior to washing again for 5 min. They were subsequently dehydrated in an alcohol gradient, cleared in xylene, and coverslipped. For Nissl’s staining, the sections were dipped in 1% toluidine blue for 30 min at 45 °C, and differentiated in 75% alcohol for seconds, then rinsed quickly in distilled water. Digital images were acquired using an inverted microscope (TE2000-S, Nikon, Tokyo, Japan).
Liquid chromatograph mass spectrometer (LC–MS)
Animals were anesthetized and sacrificed as previously described. The hippocampus and surrounding cortex ipsilateral to the tDCS site as well as their contralateral homologues were immediately separated and frozen to avoid protein degradation. Samples were subsequently weighed and homogenized with 0.4 ml of a solution of 1% formic acid prepared in cold (− 20 °C) acetonitrile using a homogenate device (Leica, Heidelberg, Germany). Two hundred microliters of the supernatant were collected after centrifugation at 12,000 rpm for 20 min at 4 °C. Levels of neurotransmitters such as glutamic acid (GLU), aspartic acid (ASP), γ-aminobutyric acid (GABA), glycine (GLY) and alanine (ALA) were determined using LC–MS equipment (QqQ-6410B, Agilent Technologies, China) as reported . This equipment was provided by the Centers for Disease Control and Prevention of Xi ‘an.
Cerebral temperature changes during tDCS are an important safety factor associated with risk for brain damage . A thermal imager (Ti400, FLUKE, USA) was used to monitor and visualize temperature changes in the brain during the 15 min stimulation period of 500 μA cathodal tDCS. The bundled software (SmartView 3.14, FLUKE, USA) was used to measure temperature. The brain temperature detected before tDCS was considered the control, and average temperatures for cortex under the stimulation site as well as for the entire cortex were recorded every 5 min during the stimulation period. Each animal received 3 trials at each test point. Since the thermal imager used in this study could only detect the surface temperature, in order to get accurate brain temperature changes after tDCS stimulation, the electrode was not fixed on the intact skull with dental cement as before, instead, it was placed on the surface of the intact dura mater after removal of the scalp and skull by using a stereotaxic apparatus (RWD life Science, Shengzhen, China) and then the surface temperature of stimulating site and the whole brain was measured.
All data were collected and analyzed by researchers blinded to the surgery and reagents that were used. Repeated measures analysis of variance (ANOVA) were conducted on data from the behavioral experiments and on cerebral temperature values. Hematology results, serum biochemical markers, and neurotransmitter levels were analyzed using a one-way ANOVA. All data were presented as the mean ± standard error of mean (SEM), and all statistical analysis were performed using SPSS version 20.0 (SPSS Inc., Chicago, IL, USA). p-values less than 0.05 were considered statistically significant.
Availability of data and materials
Raw data has been provided as additional file.
transcranial direct current stimulation
open field test
Morris water maze
white blood cells
blood urea nitrogen
- Cys C:
hematoxylin and eosin
liquid chromatograph mass spectrometer
analysis of variance
standard error of mean
Bai Y, Xia X, Wang Y, Guo Y, Yang Y, He J, Li X. Fronto-parietal coherence response to tDCS modulation in patients with disorders of consciousness. Int J Neurosci. 2017;23:1–8.
McCambridge AB, Stinear JW, Byblow WD. Revisiting interhemispheric imbalance in chronic stroke: a tDCS study. Clin Neurophysiol. 2017;129:42–50.
Thibaut A, Russo C, Hurtado-Puerto AM, Morales-Quezada JL, Deitos A, Petrozza JC, Freedman S, Fregni F. Effects of transcranial direct current stimulation, transcranial pulsed current stimulation, and their combination on brain oscillations in patients with chronic visceral pain: a pilot crossover randomized controlled study. Front Neurol. 2017;8:576.
Aurore Thibaut SWAD, Olivia Gosseries MBSL. Controlled clinical trial of repeated prefrontal tDCS in patients with chronic minimally conscious state. Brain Inj. 2017;31(4):466–74.
O’Brien AT, Amorim R, Rushmore RJ, et al. Motor cortex neurostimulation technologies for chronic post-stroke pain: implications of tissue damage on stimulation currents. Front Hum Neurosci. 2016;10:545.
Fregni F, Simon DK, Wu A, et al. Non-invasive brain stimulation for Parkinson’s disease: a systematic review and meta-analysis of the literature. J Neurol Neurosurg Psychiatry. 2005;76:1614–23.
Kazuta T, Takeda K, Osu R, et al. Transcranial direct current stimulation improves audioverbal memory in stroke patients. Am J Phys Med Rehabil. 2017;96(8):565–71.
Richmond LL, Wolk D, Chein J, et al. Transcranial direct current stimulation enhances verbal working memory training performance over time and near transfer outcomes. J Cogn Neurosci. 2014;26:2443–54.
Gogler N, Willacker L, Strube JW, et al. Single-session transcranial direct current stimulation induces enduring enhancement of visual processing speed in patients with major depression. Eur Arch Psychiatry Clin Neurosci. 2017;267(7):671–86.
Zoghi M, O’Brien TJ, Kwan P, et al. The effects of cathodal transcranial direct current stimulation in a patient with drug-resistant temporal lobe epilepsy (case study). Brain Stimul. 2016;9:790–2.
Bikson M, Grossman P, Thomas C, et al. Safety of transcranial direct current stimulation: evidence based update 2016. Brain Stimul. 2016;9:641–61.
Liebetanz D, Koch R, Mayenfels S, et al. Safety limits of cathodal transcranial direct current stimulation in rats. Clin Neurophysiol. 2009;120:1161–7.
Braun R, Klein R, Walter HL, Ohren M, Freudenmacher L, Getachew K, Ladwig A, Luellin J, Neumaier B, Endepols H. Transcranial direct current stimulation accelerates recovery of function, induces neurogenesis and recruit’s oligodendrocyte precursors in a rat model of stroke. Exp Neurol. 2016;279:127–36.
Rueger MA, Keuters MH, Walberer M, et al. Multi-session transcranial direct current stimulation (tDCS) elicits inflammatory and regenerative processes in the rat brain. PLoS ONE. 2012;7:e43776.
Bikson M, Datta A, Elwassif M. Establishing safety limits for transcranial direct current stimulation. Clin Neurophysiol. 2009;120:1033–4.
Vaseghi B, Zoghi M, Jaberzadeh S. A meta-analysis of site-specific effects of cathodal transcranial direct current stimulation on sensory perception and pain. PLoS ONE. 2015;10:e0123873.
Peruzzotti-Jametti L, Cambiaghi M, Bacigaluppi M, et al. Safety and efficacy of transcranial direct current stimulation in acute experimental ischemic stroke. Stroke. 2013;44:3166–74.
Miranda PC, Lomarev M, Hallett M. Modeling the current distribution during transcranial direct current stimulation. Clin Neurophysiol. 2006;117:1623–9.
Datta A, Elwassif M, Battaglia F, et al. Transcranial current stimulation focality using disc and ring electrode configurations: FEM analysis. J Neural Eng. 2008;5:163–74.
Wagner T, Fregni F, Fecteau S, et al. Transcranial direct current stimulation: a computer-based human model study. Neuroimage. 2007;35:1113–24.
Nitsche MA, Doemkes S, Karakose T, et al. Shaping the effects of transcranial direct current stimulation of the human motor cortex. J Neurophysiol. 2007;97:3109–17.
Summers JJ, Kang N, Cauraugh JH. Does transcranial direct current stimulation enhance cognitive and motor functions in the ageing brain: a systematic review and meta-analysis. Ageing Res Rev. 2016;25:42–54.
Dadsetan S, Bak LK, Sorensen M, Waagepetersen HS, et al. Inhibition of glutamine synthesis induces glutamate dehydrogenase-dependent ammonia fixation into alanine in co-cultures of astrocytes and neurons. Neurochem Int. 2011;59:482–8.
Dundas JE, Thickbroom GW, Mastaglia FL. Perception of comfort during transcranial DC stimulation: effect of NaCl solution concentration applied to sponge electrodes. Clin Neurophysiol. 2007;118:1166–70.
Bindman LJ, Lippold OC, Redfearn JW. The action of brief polarizing currents on the cerebral cortex of the rat during current flow and in the production of long-lasting after-effects. J Physiol. 1964;172:369–82.
Brunoni AR, Ferrucci R, Bortolomasi M, et al. Interactions between transcranial direct current stimulation (tDCS) and pharmacological interventions in the Major Depressive Episode: findings from a naturalistic study. Eur Psychiatry. 2013;28:356–61.
Gabriel S, Lau RW, Gabriel C. The dielectric properties of biological tissues: III. Parametric models for the dielectric spectrum of tissues. Phys Med Biol. 1996;41:2271–93.
Orcutt N, Gandhi OP. A 3-D impedance method to calculate power deposition in biological bodies subjected to time varying magnetic fields. IEEE Trans Biomed Eng. 1998;35:577–83.
Bădescu SV, Tătaru CP, Kobylinska L, et al. Effects of caffeine on locomotor activity in streptozotocin-induced diabetic rats. J Med Life. 2016;9:275–9.
Yanagisawa D, Kitamura Y, Takata K, et al. Possible involvement of P2X7 receptor activation in microglial neuroprotection against focal cerebral ischemia in rats. Biol Pharm Bull. 2008;31:1121–30.
Vorhees CV, Williams MT. Morris water maze: procedures for assessing spatial and related forms of learning and memory. Nat Protoc. 2006;1:848–1858.
Sari Y, Hammad LA, Saleh MM, et al. Alteration of selective neurotransmitters in fetal brains of prenatally alcohol-treated C57BL/6 mice: quantitative analysis using liquid chromatography/tandem mass spectrometry. Int J Dev Neurosci. 2010;28:263–9.
We thank Mr. Qin Guo Fu and clinical laboratory of Xijing Hospital for excellent technical assistance.
This work was supported by the special fund of Fourth Military Medical University (2016TSA-004). The authors declare that the funding bodies play no role in the design or conclusion of this study.
Ethics approval and consent to participate
Ethics approval was conducted by the Animal Use and Care Committee for Research and Education of Fourth Military Medical University (NO. 20170607).
Consent for publication
The authors declare that they have no competing interests.
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
About this article
Cite this article
Zhang, K., Guo, L., Zhang, J. et al. A safety study of 500 μA cathodal transcranial direct current stimulation in rat. BMC Neurosci 20, 40 (2019). https://doi.org/10.1186/s12868-019-0523-7