Concurrent transcranial direct current stimulation and progressive resistance training in Parkinson’s disease: study protocol for a randomised controlled trial
© Hendy et al. 2016
Received: 19 February 2016
Accepted: 23 June 2016
Published: 19 July 2016
Parkinson’s disease (PD) results from a loss of dopamine in the brain, leading to movement dysfunctions such as bradykinesia, postural instability, resting tremor and muscle rigidity. Furthermore, dopamine deficiency in PD has been shown to result in maladaptive plasticity of the primary motor cortex (M1). Progressive resistance training (PRT) is a popular intervention in PD that improves muscular strength and results in clinically significant improvements on the Unified Parkinson’s Disease Rating Scale (UPDRS). In separate studies, the application of anodal transcranial direct current stimulation (a-tDCS) to the M1 has been shown to improve motor function in PD; however, the combined use of tDCS and PRT has not been investigated.
We propose a 6-week, double-blind randomised controlled trial combining M1 tDCS and PRT of the lower body in participants (n = 42) with moderate PD (Hoehn and Yahr scale score 2–4). Supervised lower body PRT combined with functional balance tasks will be performed three times per week with concurrent a-tDCS delivered at 2 mA for 20 minutes (a-tDCS group) or with sham tDCS (sham group). Control participants will receive standard care (control group). Outcome measures will include functional strength, gait speed and variability, balance, neurophysiological function at rest and during movement execution, and the UPDRS motor subscale, measured at baseline, 3 weeks (during), 6 weeks (post), and 9 weeks (retention). Ethical approval has been granted by the Deakin University Human Research Ethics Committee (project number 2015-014), and the trial has been registered with the Australian New Zealand Clinical Trials Registry (ACTRN12615001241527).
This will be the first randomised controlled trial to combine PRT and a-tDCS targeting balance and gait in people with PD. The study will elucidate the functional, clinical and neurophysiological outcomes of combined PRT and a-tDCS. It is hypothesised that combined PRT and a-tDCS will significantly improve lower limb strength, postural sway, gait speed and stride variability compared with PRT with sham tDCS. Further, we hypothesise that pre-frontal cortex activation during dual-task cognitive and gait/balance activities will be reduced, and that M1 excitability and inhibition will be augmented, following the combined PRT and a-tDCS intervention.
Australian New Zealand Clinical Trials Registry ACTRN12615001241527. Registered on 12 November 2015.
KeywordsParkinson’s disease Balance Gait Neuroplasticity Non-invasive brain stimulation fNIRS
Parkinson’s disease (PD) is a progressive neurodegenerative movement disorder characterised by depletion of dopamine in the substantia nigra, resulting in physical symptoms such as bradykinesia, postural instability, resting tremor and muscle rigidity. PD is the second most common neurodegenerative disorder , affecting 1 % of people older than 60 years of age , which is of particular concern as populations age. PD causes significant impairments in gait and balance, which are often unresolved by standard dopamine pharmacological treatment  and result in reduced quality of life and increased risk of falls .
There is growing evidence for the use of progressive resistance training (PRT) to improve gait and lower limb muscle strength in PD . The inclusion of other functional tasks, such as balance training, in PRT programmes has also been shown to decrease postural sway, reduce the risk of falls, and improve quality of life . Importantly, functional PRT programmes have been shown to induce neuroplastic changes in the primary motor cortex (M1) of both healthy individuals  and people with PD . This is of particular interest, as maladaptive M1 plasticity in patients with PD has been linked to poorer outcomes in motor learning and movement control [9, 10]. Evidence derived from transcranial magnetic stimulation (TMS) studies has demonstrated that patients with PD present with increased cortical excitability and reduced inhibition at rest, which is evidenced by lower motor threshold, increased motor evoked potential (MEP) amplitude, reduced short-interval intra-cortical inhibition (SICI)  reduced silent period . Furthermore, reduced intra-cortical facilitation and absence of MEP size increase during contraction suggests defective facilitatory cortical inputs, particularly for movement execution . In addition, the absence of a putative neuroplastic response following paired associative stimulation [13, 14], as compared with healthy control subjects, suggests that the facilitation of M1 plasticity in patients with PD may play an important role in the restoration and maintenance of motor performance.
Transcranial direct current stimulation (tDCS) is a form of non-invasive brain stimulation that has been shown to modulate excitability of the M1 in a polarity-specific manner when applied for short periods (10–20 minutes). When anodal tDCS (a-tDCS) is applied to the M1, there is a transient increase (up to 90 minutes) in excitability and reduction SICI of underlying neurons , as well as widespread changes in activation of cortical and subcortical areas . There is substantial evidence to suggest that the application of a-tDCS to the M1 results in improved motor function in healthy populations, including increased performance in skill and strength tasks [17, 18], and this may be especially true when tDCS is applied during concurrent motor practice or training .
The use of tDCS as an independent intervention in PD has produced promising results, with evidence for improved working memory and executive function [20, 21], reduced bradykinesia, and increased walking speed following tDCS . Importantly, clinically significant improvements in the motor component of the Unified Parkinson’s Disease Rating Scale (UPDRS) have been reported following bilateral a-tDCS of the M1 . A recent pilot study of eight participants reported for the first time that combined gait training and M1 a-tDCS showed promising improvements in walking and balance measurements, but the researchers in that study concluded that larger trials were required to produce definitive results .
Given the existing evidence for enhancements in neuroplasticity and motor performance following both PRT and tDCS as independent treatments, it is reasonable to conclude that the combination of these two interventions may further augment functional benefits in patients with PD. Indeed, a combination of a-tDCS and motor training appears to produce a compounding effect on motor performance and neurophysiological adaptations in healthy populations [25, 26] and stroke-affected individuals [27, 28]; however, the application of a-tDCS during PRT and balance training in PD is yet to be investigated.
The primary aim of this pilot study is to determine the effects of a 6-week lower limb balance and PRT intervention with concurrent a-tDCS on gait, balance, strength and UPDRS motor scores in patients with PD. In addition, we will investigate neurophysiological adaptations in M1 excitability and pre-frontal cortex (PFC) activation as potential underlying mechanisms. It is hypothesised that the combination of PRT and a-tDCS will produce favourable functional motor outcomes and neuroplasticity beyond the effects of PRT alone.
Eligibility and recruitment
Diagnosed with PD by an independent neurologist
Moderate motor symptoms (score between 2 and 4 on the Hoehn and Yahr scale, as assessed by an independent neurologist and confirmed at initial assessment by a blinded researcher)
Stable drug regime for the full duration of the study and the 6 weeks preceding the study
Self-reported history of one or more falls in the last 24 months
Not currently undertaking a regular exercise programme
Severe motor impairments or injuries that will impair the ability to perform lower limb PRT (confirmed at initial assessment by blinded researcher)
Previously diagnosed neurological condition separate from PD (stroke, dementia, epilepsy)
Metal implants in the head (i.e., deep brain stimulator or aneurysm clips), which are contraindicated with non-invasive brain stimulation techniques
Randomisation and blinding
Once recruited, simple randomisation using a computerised sequence generator will be used to allocate participants to one of three study groups (a-tDCS, sham or control). Opaque envelopes will be used to conceal the group allocation, which will not be revealed until after all data have been analysed. A researcher who is otherwise removed from the study will program the tDCS machine before PRT sessions to ensure double-blinding of both researcher and participant. Participants allocated to the control group will be notified of their allocation and will be asked to attend assessment sessions only.
a-tDCS (required to perform PRT and balance training while receiving a-tDCS)
Sham (required to perform PRT and balance training while receiving sham tDCS)
Control (to receive standard care)
Strength and balance training
Participants will perform three sets of six to eight repetitions of each exercise, with resistance set at 70 % of their recorded single-repetition maximum (1RM). Repetition timing will be externally paced by an audible metronome consisting of 3-second concentric and 3-second eccentric contractions. For each exercise, resistance will be increased by 5 % when all sets can be completed with correct repetition timing and technique, as assessed by a trained exercise physiologist.
Tandem stance, 4 × 15 seconds alternating the leading foot
Single-leg stance, 4 × 15 seconds alternating the leading foot
Tandem walk, 3 × 12 steps, heel to toe, in a straight line
Hurdle walk, six laps of four hurdles (height = 30 cm)
Stance tasks will be performed with the assistance of the trainer if required and will be progressed by using unstable foam surfaces, duraDiscs (AOK Health, Newcastle, Australia), performing with the eyes closed, and receiving multi-directional perturbations. Walking tasks will be progressed by performing a concurrent dual task (naming colours, cities, countries, and so forth), adding 1-kg ankle weights, and being instructed to ‘pause’ and ‘reverse’ mid-task. Participants will advance to the next progression when the exercise physiologist deems that they can competently complete the task.
Transcranial direct current stimulation
Participants will be required to complete a minimum of 16 of the 18 scheduled training sessions (representing >85 % attendance). Testing of outcome measures (T0, T3, T6 and T9) will be completed within 72 h of the scheduled time point, determined from the commencement of the training programme.
Functional strength of the lower limb
Participants will perform 1RM tests to assess maximal voluntary strength of the lower limb muscles. A standard leg press and leg extension exercise will be performed on fixed pneumatic gym equipment (Air300; Keiser). Plantarflexion will be measured bilaterally on the seated leg press by placing the toes on the footplate and using the ankle dorsiflexion to press the plate forward while maintaining 180-degree knee extension. The unweighted movement distance is marked on the equipment, allowing the researcher to ensure that full range of movement is maintained during maximal attempts. Dorsiflexion will be measured unilaterally while the participant is seated with the heel positioned on a 25-cm step. A custom-made static strap weighted with an adjustable dumb-bell will be placed over the metatarsophalangeal joint, and the participant will be required to lift the dumb-bell smoothly through 45 degrees of dorsiflexion, measured by the researcher with a goniometer. All exercises have been chosen carefully to minimise any risk of falling or injury whilst being performed.
An initial starting resistance of approximately 20 % 1RM will be estimated by the researcher to familiarise the participant with the movement, and five to ten repetitions will be performed to provide a warm-up. The researcher will then select an appropriate resistance for a near-maximal effort, and the participant will be required to perform a single repetition of the exercise while maintaining correct technique. The resistance will be increased in 5–10 % increments as appropriate, until the participant can no longer perform a full repetition. Two minutes of rest will separate each attempt, and verbal encouragement will be provided. The highest resistance used to perform a successful repetition will be recorded as the 1RM in kilograms.
Motor function specific to PD will be assessed with section III of the UPDRS-III. The same independent assessor will perform the test at all time points and will be blinded to the intervention group. The assessment will be performed at the same time of day and will precede all other tests to ensure fatigue does not confound performance.
A Timed Up-and-Go Test (TUG) will also be performed to assess motor function and speed . Participants will be asked to rise from a 46-cm chair, walk around a plastic cone located 3 m away and return to the chair as quickly as possible. The arms of the chair may be used if necessary. The test ends when the participant assumes the original seated position, and time is recorded. Regular enclosed footwear will be worn, and customary walking aids may be used if required. The average time in seconds from three trials will serve as the TUG score.
The Berg Balance Scale will be used to assess functional balance . The assessment will take approximately 20 minutes and will consist of 14 static and dynamic balance tasks which are scored from 0 to 4 by a trained exercise physiologist. The same assessor will perform the test at all time points and will be blinded to the intervention group. High validity and reliability of the Berg Balance Scale in neurological patient populations have previously been established .
The Five Times Sit-to-Stand Test (FTSTS) will be used to assess mobility and lower limb acceleration . Participants will be seated in a 46-cm chair without armrests and will be asked to begin with their arms folded across the chest and their back upright against the backrest. Participants will perform five repetitions of moving from the seated position to standing, with the legs fully extended and hip and knee joints, as quickly as possible. The total time taken to complete five repetitions will be recorded in seconds. An inertial measurement unit (Nanotrak; Catapult Innovations, Docklands, Australia) worn on the right hip, sampling accelerations and gyrations at 100 Hz, will be used to determine vertical acceleration . Previous researchers have reported high validity and reliability of the FTSTS in patients with PD .
Gait will be assessed using the ProtoKinetics Zeno 4.9-metre walkway (ZenoMetrics LLC, Peekskill, NY, USA). The walkway has a 2-foot-wide grid of pressure-sensing pads with a spatial resolution of 0.5 cm and a sampling frequency of 120 Hz. Participants will be asked to perform the walking trials at their preferred walking speed while wearing comfortable footwear. Two different gait conditions will be assessed: (1) normal walking and (2) walking while counting backward in 7s from a random three-digit number, termed dual-task gait. Three trials of each condition will be performed in random order. A trial begins by sitting silently on a chair for 30 seconds, then standing up and walking to a starting line located 1 m from the walkway. From the start line, the participant is asked to walk up and back four times to another line 1 m beyond the end of the walkway before returning to the seated position. The 30-second rest periods between each trial allow for accurate functional near-infrared spectroscopy (fNIRS) hemodynamic brain imaging (see ‘Functional near-infrared spectroscopy’ section below for details). The mean asymmetry and variability will be calculated using all of the steps of all of the trials for a given condition: step velocity (in meters/second), step duration (in seconds) step length (in centimetres), double support time (in seconds) and stride width (in centimetres). Step variability will be calculated on the basis of residuals, as suggested in previous literature . Gait assessments using instrumented walkways have been shown to be repeatable in older adults [35, 36].
While undertaking the gait assessments, the participants will be asked to wear an inertial measurement unit on an elastic belt (Nanotrak) for sampling of accelerations and gyrations at 100 Hz at lumbar vertebrae L3–L5, in line with the spinous processes. Harmonic ratio  and multi-scale sample entropy will be calculated from the recorded vertical and resultant signals . These inertial measurement unit-based variables have previously been shown to be repeatable .
Static balance will be assessed with a 45-second bipedal standing test in three separate conditions: (1) eyes open, (2) eyes closed and (3) dual-task balance (eyes open while counting backwards in serial 7s from a random three-digit number). All tests will be conducted at preferred stance width, which will be recorded at baseline and maintained during all subsequent tests. A black dot (10-cm diameter) printed on white paper will be affixed 3 m in front of the participants at eye height, and the participants will be asked to fix their gaze on the dot while undertaking the eyes-open tests. Again, 30-second rest periods between each trial will be provided for concurrent fNIRS sampling. The measurement will be conducted on a portable force plate (AccuGait; AMTI, Watertown, MA, USA) sampling ground reaction forces at 500 Hz. Instantaneous centre of pressure will be calculated on the basis of recorded signals, and centre-of-pressure travel velocity (millimetres/second) will be calculated to represent static balance. The repeatability of centre-of-pressure travel analyses has been demonstrated in previous studies .
Transcranial magnetic stimulation and electromyography
Corticospinal excitability and intra-cortical inhibition of the tibialis anterior (TA) muscle will be assessed using two Magstim 2002 stimulators (Magstim, Whitland, UK) connected to a 110-mm, concave, double-cone coil (maximum output 1.4 T). The coil will be positioned with anterior-to-posterior current flow, and sites near the estimated right TA motor representation (approximately 1–3 cm lateral and anterior to the vertex) will be explored to determine the optimal site, which will be marked on the scalp with a permanent marker. Resting motor threshold (RMT) and active motor threshold (AMT) will be defined as the lowest stimulator output required to achieve an MEP with an amplitude greater than 0.05 mV and 0.20 mV in six of ten stimuli, respectively. Corticospinal excitability will be determined by delivering ten single-pulse stimuli at suprathreshold intensities of 1.3 × RMT and 1.5 × RMT. In accordance with previous literature , SICI will be determined by delivering ten paired-pulse stimuli, with the conditioning stimulus set at 0.8 × RMT, the test stimulus set at 1.3 × RMT, and an interstimulus interval of 3 milliseconds. Intra-cortical inhibition will be determined by calculating the SICI ratio (average paired-pulse MEP amplitude/average single-pulse MEP amplitude); thus, SICI ratio values closer to 1 will represent lower levels of intra-cortical inhibition, while SICI ratio values closer to 0 will represent higher levels of intra-cortical inhibition. The total of 30 stimuli (20 single pulses and 10 paired pulses) will be delivered in sets of 5 in a randomised order.
Once the TMS protocol has been completed with the TA muscle at rest, the same protocol will be repeated in an active muscle state while the participant maintains a low-level background contraction (10 % of maximum force). The participant’s maximal voluntary isometric contraction (MVIC) of the right TA will first be determined using a force transducer (LMD500; Futek, Irvine, CA, USA) mounted in a custom-made timber frame. The participant will be seated with the knee and ankle positioned at 90 degrees and the transducer positioned above the distal end of the metatarsals. The participant will be instructed to dorsiflex at the ankle with the base of the heel remaining on the floor, producing an isometric contraction against the force transducer. The peak force obtained from three maximal efforts with 2 minutes rest between attempts with the highest force output will be recorded as the participant’s MVIC. Verbal encouragement will be provided, and visual feedback of force will be visible on a monitor directly in front of the participant at eye level. To complete the TMS protocol in the active muscle condition, 10 % of the MVIC will be calculated and indicated by a line on the monitor. The participant will be asked to maintain the force feedback level with the line while TMS is delivered, with short rest periods (5–10 seconds) between each set of five stimuli. AMT will be defined as the lowest stimulator output required to achieve an MEP with an amplitude greater than 0.2 mV in six of ten stimuli.
Maximal compound waves (M-waves) will be collected during each session and used to normalise MEP responses. This method prevents any changes in peripheral muscle excitability acting as a confounder when determining corticospinal excitability . A DS7A constant current electrical stimulator (Digitimer, Welwyn Garden City, UK) will be used to deliver supramaximal stimulation to the common peroneal nerve. The head of the fibula will be palpated, and a stimulating bar will be positioned directly inferior, with light pressure applied. Stimulation will be delivered at increasing current strengths until the muscle response reaches a plateau, then increased 10–20 % to ensure maximal stimulation is achieved. The largest resulting peak-to-peak muscle response will be reported as maximal M-wave amplitude. The M-wave will be obtained in both resting and active (10 % MVIC) muscle conditions and will be used to normalise resting and active MEPs, respectively.
All muscle responses (MEPs and M-waves) will be recorded using surface electromyography (sEMG). The area of electrode placement will be shaved to remove hair, rubbed with abrasive gel to remove dead skin, and then cleaned with 70 % isopropyl alcohol. Bipolar gel Ag-AgCl electrodes (8-mm diameter, model E258S; BIOPAC Systems, Goleta, CA, USA) will be placed over the TA muscle belly with an inter-electrode distance of 2 cm. A grounding electrode will be placed over the patella and used as a common reference. The electrode sites will be marked with a permanent marker, measured in reference to the tibial tuberosity, and photographed to ensure consistent electrode placement between sessions. All cables will be fastened with tape to prevent movement artifact. All sEMG signals (including MEPs) will be amplified (×1000) with band-pass filtering between 13 Hz and 1000 Hz, digitised online at 2 KHz for 500 milliseconds, and recorded and analysed using PowerLab 4/35 (ADInstruments, Bella Vista, Australia).
Functional near-infrared spectroscopy
Mechanisms underlying difficulties in dual-task gait and balance are largely unclear. However, the PFC, which is primarily involved in attention and executive function, is also involved in human balance and locomotion , which likely plays an important role. Although attention and executive function that depend on the PFC are often affected in PD [43–45], patients may rely more on the PFC because of reduced movement automaticity of dysfunctional basal ganglia circuits [46–48]. Consequently, altered functioning of the PFC during dual-task gait and balance in PD might explain the difficulties of patients with PD and therefore will be examined in this study using fNIRS.
fNIRS neuroimaging uses optical technology to measure the relative concentrations of oxygenated haemoglobin (O2Hb) and deoxygenated haemoglobin (HHb) in the cortical layer microcirculation , producing cortical activation data consistent with data obtained from functional magnetic resonance imaging [50, 51]. Portable fNIRS has successfully been used to measure PFC activation during dual-task walking in patients with PD  and in other populations [53–55]. A PortaLite™ fNIRS system (Artinis Medical Systems, Elst, The Netherlands) will be used to assess PFC activation during several tasks, including counting backwards in 7s from a random three-digit number while seated and during the simple and dual-task gait-and-balance assessments described in the previous section.
The PortaLite™ device has three transmitters and one receiver, with transmitter-receiver distances of 30, 35 and 40 mm. Near-infrared light is transmitted with two wavelengths, 760 nm and 850 nm, and data will be sampled with a frequency of 10 Hz. The PortaLite™ device uses wireless technology (Bluetooth, Kirkland, WA, USA), allowing participants to perform the tasks without restriction of wires. Since a previous preliminary study showed no significant differences between left- or right-side PFC activation during dual-task walking in PD  the PortaLite™ device will be placed on the left forehead F3 site using the international 10–20 electroencephalography system. This location will target the left Brodmann’s areas 9 and 10, which correspond to the dorsolateral and anterior PFC [56, 57]. The device will be shielded from ambient light by covering the forehead with a black piece of fabric. Oxysoft software (Artinis Medical Systems) will be used for data collection and analysis.
On the basis of different absorption spectra, concentration changes of O2Hb and HHb in the targeted PFC area will be calculated from the changes in detected light intensity. This is done using the modified Beer-Lambert law, assuming constant scattering . The differential path length factor, which accounts for the increased distance travelled by light due to scattering, will be set to 6 for all participants. For analysis, O2Hb and HHb signals of the three channels (the three transmitter-receiver distances) will be averaged. The moving SD-based movement artifact reduction algorithm method will be used within each trial to remove movement artifacts and other noise from the fNIRS signals . The threshold for artifact detection will be set to 0.45 for O2Hb and 0.18 for HHb , with a window length for moving SD calculation at 0.5 seconds and a window length for artifact correction (locally weighted scatterplot smoothing window) on 1 second. The fNIRS signals will then be linearly de-trended per trial and low-pass-filtered at 0.1 Hz to remove heart rate from the signals. To enable direct comparison of the different trials within each task, the filtered signals will be biased, using the average concentration of the 5 seconds before the ‘start’ instruction as a reference (zero). Then, individual trials will be averaged per task to create three mean time course signals per person, which will then be averaged over all participants. Finally, the peak and mean concentrations (O2Hb and HHb) during the task and rest periods will be calculated over all trials for all participants and then averaged for each of the tasks.
All adverse events will be self-reported by the participants at 3, 6 and 9 weeks and assessed by the research staff for seriousness, expectedness and causality following the guidelines recommended by the National Health and Medical Research Council (NHMRC) position statement for monitoring and reporting of safety for clinical trials (https://www.nhmrc.gov.au/guidelines-publications/e112). In this study, an adverse event will be defined as any health-related unfavourable or unintended medical occurrence (sign, symptom, syndrome, illness) that develops or worsens during the period of the trial. Adverse events will be closely monitored until resolution or stabilisation is achieved or until it has been shown that the study intervention is not the cause of the injury. Participants will be asked to contact the research staff immediately in the event of a serious adverse event. Any adverse event sustained during the exercise programme will be recorded by the trainers and immediately reported to the research staff. The chief investigator will be informed of the adverse event and shall determine its seriousness and causality in conjunction with any medical staff treating the event. A serious adverse event that is deemed related to, or suspected to be related to, the exercise intervention will be reported to the ethics committee.
Data management and archiving
All data will be de-identified, coded and stored on a Deakin University server that can be accessed only from password-protected computers. Any physical copies of the data recording sheet will be stored in locked filing cabinets at Deakin University (Burwood). All data will be checked monthly by the chief investigator to ensure that all protocols and ethical guidelines for data collection and analysis are followed. All study-related documents will be archived at Deakin University at the end of the study for a minimum of 6 years, which is in line with current ethical requirements.
Findings derived from the primary outcome analysis of this trial will be reported in journal articles, which will include results regardless of the direction or magnitude of the effect. The results will also be presented at leading national and international conferences and clinical forums and to other relevant health professionals and stakeholders, as well as to the participants. All investigators will have the opportunity to be listed as an author of future publications, in accordance with the Australian Government National Health and Medical Research Council guidelines .
Sample size calculation and statistical analysis
Gait speed, static balance and UPDRS-III at T6 will serve as primary outcome measures, with all other assessments and time points serving as secondary outcome measures. Based on the effect size observed in a recent study using a-tDCS during walking exercise , it is estimated that 42 participants randomised equally to three groups will be needed. Fourteen participants in each intervention group (a-tDCS, sham, control) will provide at least 80 % power to detect a 10–15 % difference in gait speed and static balance (centre of pressure), assuming a 5 % significance level. In functional assessments, a 10–15 % difference equates to an increase of 5.2 points on the UPDRS-III, which indicates a moderate clinically important difference .
A two-way, repeated-measures, mixed-design analysis of variance with factors time (T0 vs. T3 vs. T6 vs. T9) and treatment (a-tDCS vs. sham vs. control) will be used to determine any effect of the intervention on balance, gait speed and measures of brain physiology. False discovery rate analysis will be applied to determine when and where significance is found. An alpha level of P < 0.05 will be set to determine significance.
Where possible, we will obtain endpoint measures from all withdrawals and will include all randomised subjects in the final analysis. For participants who are lost to follow-up, missing data will be handled with multiple imputation. As this approach makes an untestable assumption that data are missing at random (i.e., missing data can be predicted from the observed data) , we will perform sensitivity analysis to evaluate the effect of potential non-random attrition . Sensitivity analyses will employ simulation and will test a range of scenarios assuming plausible arm-specific differences in outcomes for individuals who were lost to follow-up .
To our knowledge, this pilot study will be the first randomised controlled trial to combine functional PRT and a-tDCS of the M1 to target balance and gait in people with PD. The study has been designed to elucidate the functional, clinical and neurophysiological outcomes of combined PRT and a-tDCS. It is hypothesised that the combination of PRT and a-tDCS will benefit lower limb strength, postural sway, gait speed and stride variability by a greater magnitude than PRT with sham-tDCS. Further, we hypothesise that PFC activation during dual-task cognitive and gait-and-balance activities will be reduced, and that M1 corticospinal excitability and inhibition will be augmented, following the combined PRT and a-tDCS intervention.
The study is strengthened by a double-blind approach to tDCS stimulation type (a-tDCS or sham), with participants, outcome assessors and exercise supervisors remaining unaware of stimulation type for the duration of the study. Because of the nature of the exercise interventions, participants in the control group cannot be blinded; however, outcome assessors will remain unaware of allocation. The PRT programme used in this study has been developed specifically to target lower limb strength and incorporate functional balance tasks that will maximise gains in mobility and reduce postural sway. All PRT sessions will be conducted one-to-one with an experienced exercise physiologist to ensure each participant will be trained consistently. Progressions will be administered according to individual performance and will be recorded in detail to enable a post-intervention comparison, which will allow us to detect any potential inequality of exercise load between groups. Outcome measures have been carefully selected to enable us to detect functionally and clinically relevant effects of the intervention (UPDRS, TUG, FTSTS, Berg Balance Scale and 1RM lower limb strength tests), as well as to provide sensitive biomechanical analysis with previously validated techniques (step velocity, duration, length, double-support time, stride width and centre-of-pressure travel velocity). Neurophysiological assessments will provide insight into adaptive plasticity that may underpin any changes in functional capability, with TMS used to detect changes in corticospinal excitability and inhibition of the M1 lower limb representation and fNIRS neuroimaging of the PFC used during combined cognitive and motor tasks to quantify changes in PFC activation.
A limitation of this study is the reduced sample size, which has been selected for the feasibility of conducting a one-to-one, 6-week exercise intervention. Despite this, sample size calculations indicate that any clinically significant benefits of combining a-tDCS with PRT will be detected statistically. If successful, pilot data from this study are vital to informing larger-scale clinical trials in patients with PD, and the additional investigation of underpinning neurophysiological mechanisms may also be translated to inform future treatment options for a range of other movement disorders.
The safe and inexpensive nature of a-tDCS is well suited for translation to existing and established PD rehabilitation programmes and services. While current pharmacological treatments in PD provide significant benefits to reduce the impact of some motor symptoms, bradykinesia and impaired postural stability often continue to impact patients significantly . These symptoms have a detrimental effect of the quality of life of patients with PD and contribute to an increased risk of falls . Rates of falls among patients with PD are twice as high as those in the general older population, with 46 % of people with PD experiencing recurrent falls each year [65, 66]. Falls often result in hospitalisation  as well as longer-term injuries such as fractures that further restrict physical capability and contribute to a cycle of secondary health complications and a loss of independence . Effective interventions targeting balance and gait will reduce the burden of PD on the individual, family and carers, as well as the healthcare system. We anticipate that the findings of this study will inform large-scale randomised controlled trials aimed at implementing PRT and a-tDCS in community- and home-based settings to treat the motor symptoms of PD.
Seventeen participants have completed the protocol in full, and six are currently undergoing PRT. One participant has failed to complete the intervention due to illness. Recruitment of participants is ongoing.
AMT, active motor threshold; a-tDCS, anodal transcranial direct current stimulation; fNIRS, functional near-infrared spectroscopy; FTSTS, Five Times Sit-to-Stand Test; HHb, deoxygenated haemoglobin; M1, primary motor cortex; MEP, motor evoked potential; MVIC, maximum voluntary isometric contraction; M-wave, maximal compound wave; O2Hb, oxygenated haemoglobin; PD, Parkinson’s disease; PFC, pre-frontal cortex; PRT, progressive resistance training; 1RM, single-repetition maximum; RMT, resting motor threshold; sEMG, surface electromyography; SICI, short-interval intra-cortical inhibition; SPIRIT, Standard Protocol Items: Recommendations for Interventional Trials; TA, tibialis anterior; tDCS, transcranial direct current stimulation; TMS, transcranial magnetic stimulation; TUG, Timed Up and Go Test; UPDRS, Unified Parkinson’s Disease Rating Scale
The authors acknowledge the help and support they received from the Australian Parkinson’s Disease Registry.
This project will be funded by the Deakin University Central Research Grants Scheme. WPT and TR are supported by Alfred Deakin post-doctoral research fellowships. PGE is supported by a career development fellowship from the National Health and Medical Research Council (Australia). LJ was supported to conduct this research with Commonwealth Collaborative Research Network funding provided to Victoria University.
Availability of supporting data
All supporting data will be published as supplements together with the main papers in their respective journals.
WPT conceptualised the project and obtained funding. AMH drafted the manuscript and was involved in the project design and implementation. AT carried out the project and was involved in drafting the manuscript. TR was involved with analysis of gait and posturographic data. DW was involved in implementation of gait and posturographic tests and collection of data. MM was involved with analysis and interpretation of NIRS data. LJ was involved in the collection and analysis of functional assessments. DJK was involved in analysis and interpretation of TMS data. PGE provided supervision of WPT and input into the project design. All authors helped to draft the manuscript, and all read and approved the final manuscript.
AMH is a lecturer in motor learning at Deakin University. She completed her doctoral degree in 2014 by investigating the use of tDCS to facilitate adaptations to strength training and the cross-facilitation phenomenon. She has a keen interest in understanding how various forms of exercise and brain stimulation can underpin improvements in mood and cognitive function.
AT is a graduate student and exercise scientist currently supervised by WPT at Deakin University. He is focused on developing clinical skills and experience with working with people with neurological disorders.
TR is a lecturer in biomechanics at Deakin University specialising in gait and balance kinematics in healthy and clinical populations. In particular, TR is interested in understanding gait variability in people with cognitive impairments and neurological disorders.
MM is a post-doctoral research fellow at the University of Montpellier who specialises in the application of brain and muscle near-infrared spectroscopy techniques. MM’s research is focused on changes in brain activation profiles during gait and dual-tasking in PD.
LJ is a post-doctoral research fellow and exercise scientist at The Florey Institute. He specialises in exercise prescriptions for clinical populations such as stroke and PD. His research is focused on developing optimal exercise guidelines for people with stroke and neurological disorders.
DJK is a senior lecturer at La Trobe University specialising in the central and peripheral changes associated with strength training. His research includes investigating mechanisms that drive neuroplasticity and cross-education after strength training.
DW is a post-doctoral research fellow in biomechanics at La Trobe University. As a former doctoral student of TR, his research is focused on gait variability and balance in healthy and clinical populations.
PGE heads the cognitive neuroscience unit at Deakin University and is an expert in various brain stimulation protocols in people with autism spectrum disorder. PGE provides mentorship for WPT and AMH on several projects and offers advice on the optimal brain stimulation protocol for the present study.
WPT is currently an Alfred Deakin post-doctoral research fellow at Deakin University whose research is focused on understanding maladaptive brain plasticity in Parkinson’s disease. His research interests include the use of non-invasive brain stimulation techniques and exercise to improve motor and cognitive function in people with PD.
The authors declare that they have no competing interests.
Consent for publication
Written informed consent was obtained from the patients for publication of this manuscript and any accompanying images. All participants’ details will be de-identified and coded to ensure that participants’ confidentiality before, during and after the trial will be protected. A copy of the written consent is available for review by the Editor-in-Chief of this journal.
Ethics approval and consent to participate
Written informed consent was provided by the participants prior to the commencement of the study. Ethics approval has been granted by the Deakin University Human Research Ethics Committee (project number 2015-014).
Open AccessThis article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. The Creative Commons Public Domain Dedication waiver (http://creativecommons.org/publicdomain/zero/1.0/) applies to the data made available in this article, unless otherwise stated.
- de Lau LM, Breteler MM. Epidemiology of Parkinson’s disease. Lancet Neurol. 2006;5:525–35.View ArticlePubMedGoogle Scholar
- Nussbaum RL, Ellis CE. Alzheimer’s disease and Parkinson’s disease. N Engl J Med. 2003;348:1356–64.View ArticlePubMedGoogle Scholar
- Brozova H, Stochl J, Roth J, et al. Fear of falling has greater influence than other aspects of gait disorders on quality of life in patients with Parkinson’s disease. Neuro Endocrinol Lett. 2009;30:453–7.PubMedGoogle Scholar
- Leroi I, Ahearn DJ, Andrews M, et al. Behavioural disorders, disability and quality of life in Parkinson’s disease. Age Ageing. 2011;40:614–21.View ArticlePubMedGoogle Scholar
- Tillman A, Muthalib M, Hendy AM, et al. Lower limb progressive resistance training improves leg strength but not gait speed or balance in Parkinson’s disease: a systematic review and meta-analysis. Front Aging Neurosci. 2015;7:40.View ArticlePubMedPubMed CentralGoogle Scholar
- Hirsch MA, Toole T, Maitland CG, et al. The effects of balance training and high-intensity resistance training on persons with idiopathic Parkinson’s disease. Arch Phys Med Rehabil. 2003;84:1109–17.View ArticlePubMedGoogle Scholar
- Leung M, Rantalainen T, Teo WP, et al. Motor cortex excitability is not differentially modulated following skill and strength training. Neuroscience. 2015;305:99–108.View ArticlePubMedGoogle Scholar
- Fisher BE, Wu AD, Salem GJ, et al. The effect of exercise training in improving motor performance and corticomotor excitability in people with early Parkinson’s disease. Arch Phys Med Rehabil. 2008;89:1221–9.View ArticlePubMedPubMed CentralGoogle Scholar
- Lindenbach D, Bishop C. Critical involvement of the motor cortex in the pathophysiology and treatment of Parkinson’s disease. Neurosci Biobehav Rev. 2013;37:2737–50.View ArticlePubMedGoogle Scholar
- Ridding MC, Inzelberg R, Rothwell JC. Changes in excitability of motor cortical circuitry in patients with Parkinson’s disease. Ann Neurol. 1995;37:181–8.View ArticlePubMedGoogle Scholar
- Milanović S, Filipović SR, Radovanović S, et al. Changes in motor cortex excitability associated with muscle fatigue in patients with Parkinson’s disease. Vojnosanit Pregl. 2013;70:298–303.View ArticlePubMedGoogle Scholar
- Lefaucheur JP. Motor cortex stimulation for Parkinson’s disease and dystonia: lessons from transcranial magnetic stimulation? A review of the literature [in French]. Rev Neurol. 2005;161:27–41.View ArticlePubMedGoogle Scholar
- Ueki Y, Mima T, Kotb MA, et al. Altered plasticity of the human motor cortex in Parkinson’s disease. Ann Neurol. 2006;59:60–71.View ArticlePubMedGoogle Scholar
- Kojovic M, Bologna M, Kassavetis P, et al. Functional reorganization of sensorimotor cortex in early Parkinson disease. Neurology. 2012;78:1441–8.View ArticlePubMedPubMed CentralGoogle Scholar
- Nitsche MA, Paulus W. Excitability changes induced in the human motor cortex by weak transcranial direct current stimulation. J Physiol. 2000;527:633–9.View ArticlePubMedPubMed CentralGoogle Scholar
- Lang N, Siebner HR, Ward NS, et al. How does transcranial DC stimulation of the primary motor cortex alter regional neuronal activity in the human brain? Eur J Neurosci. 2005;22:495–504.View ArticlePubMedPubMed CentralGoogle Scholar
- Reis J, Schambra HM, Cohen LG, et al. Noninvasive cortical stimulation enhances motor skill acquisition over multiple days through an effect on consolidation. Proc Natl Acad Sci U S A. 2009;106:1590–5.View ArticlePubMedPubMed CentralGoogle Scholar
- Tanaka S, Hanakawa T, Honda M, et al. Enhancement of pinch force in the lower leg by anodal transcranial direct current stimulation. Exp Brain Res. 2009;196:459–65.View ArticlePubMedPubMed CentralGoogle Scholar
- Stagg CJ, Jayaram G, Pastor D, et al. Polarity and timing-dependent effects of transcranial direct current stimulation in explicit motor learning. Neuropsychologia. 2011;49:800–4.View ArticlePubMedPubMed CentralGoogle Scholar
- Boggio PS, Ferrucci R, Rigonatti SP, et al. Effects of transcranial direct current stimulation on working memory in patients with Parkinson’s disease. J Neurol Sci. 2006;249:31–8.View ArticlePubMedGoogle Scholar
- Doruk D, Gray Z, Bravo GL, et al. Effects of tDCS on executive function in Parkinson’s disease. Neurosci Lett. 2014;582:27–31.View ArticlePubMedGoogle Scholar
- Benninger DH, Lomarev M, Lopez G, et al. Transcranial direct current stimulation for the treatment of Parkinson’s disease. J Neurol Neurosurg Psychiatry. 2010;81:1105–11.View ArticlePubMedPubMed CentralGoogle Scholar
- Fregni F, Boggio PS, Santos MC, et al. Noninvasive cortical stimulation with transcranial direct current stimulation in Parkinson’s disease. Mov Disord. 2006;21:1693–702.View ArticlePubMedGoogle Scholar
- Kaski D, Dominguez RO, Allum JH, et al. Combining physical training with transcranial direct current stimulation to improve gait in Parkinson’s disease: a pilot randomized controlled study. Clin Rehabil. 2014;28:1115–24.View ArticlePubMedGoogle Scholar
- Hendy AM, Teo WP, Kidgell DJ. Anodal transcranial direct current stimulation prolongs the cross-education of strength and corticomotor plasticity. Med Sci Sport Exerc. 2015;47:1788–97.View ArticleGoogle Scholar
- Hendy AM, Kidgell DJ. Anodal tDCS applied during strength training enhances motor cortical plasticity. Med Sci Sport Exerc. 2013;45:1721–9.View ArticleGoogle Scholar
- Rocha S, Silva E, Foerster A, et al. The impact of transcranial direct current stimulation (tDCS) combined with modified constraint-induced movement therapy (mCIMT) on upper limb function in chronic stroke: a double-blind randomized controlled trial. Disabil Rehabil. 2016;38:653–60.View ArticlePubMedGoogle Scholar
- Fusco A, Iosa M, Venturiero V, et al. After vs. priming effects of anodal transcranial direct current stimulation on upper extremity motor recovery in patients with subacute stroke. Restor Neurol Neurosci. 2014;32:301–12.PubMedGoogle Scholar
- Podsiadlo D, Richardson S. The timed “Up & Go”: a test of basic functional mobility for frail elderly persons. J Am Geriatr Soc. 1991;39:142–8.View ArticlePubMedGoogle Scholar
- Berg KO, Wood-Dauphinee SL, Williams JI, et al. Measuring balance in the elderly: validation of an instrument. Can J Public Health. 1992;83 Suppl 2:S7–11.PubMedGoogle Scholar
- La Porta F, Caselli S, Susassi S, et al. Is the Berg Balance Scale an internally valid and reliable measure of balance across different etiologies in neurorehabilitation? A revisited Rasch analysis study. Arch Phys Med Rehabil. 2012;93:1209–16.View ArticlePubMedGoogle Scholar
- Csuka M, McCarty DJ. Simple method for measurement of lower extremity muscle strength. Am J Med. 1985;78:77–81.View ArticlePubMedGoogle Scholar
- Doheny EP, Walsh C, Foran T, et al. Falls classification using tri-axial accelerometers during the five-times-sit-to-stand test. Gait Posture. 2013;38:1021–5.View ArticlePubMedGoogle Scholar
- Duncan RP, Leddy AL, Earhart GM. Five times sit-to-stand test performance in Parkinson’s disease. Arch Phys Med Rehabil. 2011;92:1431–6.View ArticlePubMedPubMed CentralGoogle Scholar
- Lord S, Howe T, Greenland J, et al. Gait variability in older adults: a structured review of testing protocol and clinimetric properties. Gait Posture. 2011;34:443–50.View ArticlePubMedGoogle Scholar
- Montero-Odasso M, Casas A, Hansen KT, et al. Quantitative gait analysis under dual-task in older people with mild cognitive impairment: a reliability study. J Neuroeng Rehabil. 2009;6:35.View ArticlePubMedPubMed CentralGoogle Scholar
- Bellanca JL, Lowry KA, Vanswearingen JM, et al. Harmonic ratios: a quantification of step to step symmetry. J Biomech. 2013;46:828–31.View ArticlePubMedGoogle Scholar
- Riva F, Bisi MC, Stagni R. Gait variability and stability measures: minimum number of strides and within-session reliability. Comput Biol Med. 2014;50:9–13.View ArticlePubMedGoogle Scholar
- Rogind H, Simonsen H, Era P, et al. Comparison of Kistler 9861A force platform and Chattecx Balance System for measurement of postural sway: correlation and test-retest reliability. Scand J Med Sci Sports. 2003;13:106–14.View ArticlePubMedGoogle Scholar
- Kujirai T, Caramia MD, Rothwell JC, et al. Corticocortical inhibition in human motor cortex. J Physiol. 1993;471:501–19.View ArticlePubMedPubMed CentralGoogle Scholar
- Carroll TJ, Riek S, Carson RG. Reliability of the input-output properties of the cortico-spinal pathway obtained from transcranial magnetic and electrical stimulation. J Neurosci Methods. 2001;112:193–202.View ArticlePubMedGoogle Scholar
- Nutt JG, Horak FB, Bloem BR. Milestones in gait, balance, and falling. Mov Disord. 2011;26:1166–74.View ArticlePubMedGoogle Scholar
- Hausdorff JM, Doniger GM, Springer S, et al. A common cognitive profile in elderly fallers and in patients with Parkinson’s disease: the prominence of impaired executive function and attention. Exp Aging Res. 2006;32:411–29.View ArticlePubMedPubMed CentralGoogle Scholar
- Kudlicka A, Clare L, Hindle JV. Executive functions in Parkinson’s disease: systematic review and meta-analysis. Mov Disord. 2011;26:2305–15.View ArticlePubMedGoogle Scholar
- Williams-Gray CH, Evans JR, Goris A, et al. The distinct cognitive syndromes of Parkinson’s disease: 5 year follow-up of the CamPaIGN cohort. Brain. 2009;132:2958–69.View ArticlePubMedGoogle Scholar
- Kelly VE, Eusterbrock AJ, Shumway-Cook A. A review of dual-task walking deficits in people with Parkinson’s disease: motor and cognitive contributions, mechanisms, and clinical implications. Parkinsons Dis. 2012;2012:918719.PubMedGoogle Scholar
- Bohnen NI, Jahn K. Imaging: What can it tell us about parkinsonian gait? Mov Disord. 2013;28:1492–500.View ArticlePubMedPubMed CentralGoogle Scholar
- Amboni M, Barone P, Hausdorff JM. Cognitive contributions to gait and falls: evidence and implications. Mov Disord. 2013;28:1520–33.View ArticlePubMedPubMed CentralGoogle Scholar
- Perrey S. Possibilities for examining the neural control of gait in humans with fNIRS. Front Physiol. 2014;5:204.View ArticlePubMedPubMed CentralGoogle Scholar
- Steinbrink J, Villringer A, Kempf F, et al. Illuminating the BOLD signal: combined fMRI-fNIRS studies. Magn Reson Imaging. 2006;24:495–505.View ArticlePubMedGoogle Scholar
- Cui X, Bray S, Bryant DM, et al. A quantitative comparison of NIRS and fMRI across multiple cognitive tasks. Neuroimage. 2011;54:2808–21.View ArticlePubMedGoogle Scholar
- Mirelman I, Maidan F, Nieuwhof H, et al. The role of the frontal lobe in complex walking among healthy older adults and patients with Parkinson’s disease: An fNIRS study [abstract]. Mov Disord. 2016;31 (suppl 2). (http://www.mdsabstracts.org/abstract/the-role-of-the-frontal-lobe-in-complex-walking-amonghealthy-older-adults-and-patients-with-parkinsons-disease-an-fnirs-study/).
- Atsumori H, Kiguchi M, Katura T, et al. Noninvasive imaging of prefrontal activation during attention-demanding tasks performed while walking using a wearable optical topography system. J Biomed Opt. 2010;15:046002.View ArticlePubMedGoogle Scholar
- Holtzer R, Mahoney JR, Izzetoglu M, et al. Online fronto-cortical control of simple and attention-demanding locomotion in humans. Neuroimage. 2015;112:152–9.View ArticlePubMedPubMed CentralGoogle Scholar
- Mirelman A, Maidan I, Bernad-Elazari H, et al. Increased frontal brain activation during walking while dual tasking: an fNIRS study in healthy young adults. J Neuroeng Rehabil. 2014;11:85.View ArticlePubMedPubMed CentralGoogle Scholar
- Okamoto M, Dan H, Sakamoto K, et al. Three-dimensional probabilistic anatomical cranio-cerebral correlation via the international 10–20 system oriented for transcranial functional brain mapping. Neuroimage. 2004;21:99–111.View ArticlePubMedGoogle Scholar
- Maidan I, Bernad-Elazari H, Gazit E, et al. Increased activation of the frontal lobe is associated with freezing of gait in patients with Parkinson’s disease: an fNIRS study. Mov Disord. 2015;28:324–24.Google Scholar
- Sakatani K, Yamashita D, Yamanaka T, et al. Changes of cerebral blood oxygenation and optical pathlength during activation and deactivation in the prefrontal cortex measured by time-resolved near infrared spectroscopy. Life Sci. 2006;78:2734–41.View ArticlePubMedGoogle Scholar
- Scholkmann F, Spichtig S, Muehlemann T, et al. How to detect and reduce movement artifacts in near-infrared imaging using moving standard deviation and spline interpolation. Physiol Meas. 2010;31:649–62.View ArticlePubMedGoogle Scholar
- National Health and Medical Research Council. Australian code for the responsible conduct of research. Canberra: Australian Government; 2007. https://www.nhmrc.gov.au/guidelines-publications/r39. Accessed 11 Jul 2016.
- Shulman LM, Gruber-Baldini AL, Anderson KE, et al. The clinically important difference on the Unified Parkinson’s Disease Rating Scale. Arch Neurol. 2010;67(1):64–70.View ArticlePubMedGoogle Scholar
- Schafer JL. Analysis of incomplete multivariate data. Boca Raton, FL: Chapman & Hall/CRC Press; 1997.View ArticleGoogle Scholar
- White IR, Horton NJ, Carpenter J, Pocock SJ. Strategy for intention to treat analysis in randomised trials with missing outcome data. BMJ. 2011;342:d40.View ArticlePubMedPubMed CentralGoogle Scholar
- White IR, Carpenter J, Evans S, Schroter S. Eliciting and using expert opinions about dropout bias in randomized controlled trials. Clin Trials. 2007;4(2):125–39.View ArticlePubMedGoogle Scholar
- Bloem BR, Grimbergen YA, Cramer M, et al. Prospective assessment of falls in Parkinson’s disease. J Neurol. 2001;248:950–8.View ArticlePubMedGoogle Scholar
- Ashburn A, Stack E, Pickering RM, et al. Predicting fallers in a community-based sample of people with Parkinson’s disease. Gerontology. 2001;47:277–81.View ArticlePubMedGoogle Scholar
- Temlett JA, Thompson PD. Reasons for admission to hospital for Parkinson’s disease. Intern Med J. 2006;36:524–6.View ArticlePubMedGoogle Scholar
- Masud T, Morris RO. Epidemiology of falls. Age Ageing. 2001;30:3–7.View ArticlePubMedGoogle Scholar