Model-based optimized phase-deviation deep brain stimulation for Parkinson ’s disease
Introduction
Parkinson’s disease (PD) is a degenerative disease associated with loss of dopaminergic cells in the substantia nigra pars compacta (SNc) (Obeso et al., 2000). These cells regulate the activities of the basal ganglia (BG) mainly through innervation of the striatum (Stein & Bar-Gad, 2013). Previous experimental studies have shown that pathological synchronous bursting activities occur in the BG of PD patients and 1-methyl-4-phenyl-1,2,3,6-tetrahydropyridine (MPTP)-treated primates (Galvan and Wichmann, 2008, Wichmann and Soares, 2006). To understand mechanisms underlying these pathological activities, knowledge of changes in neural nonlinear dynamic behaviors is required. The development of mathematical models provides useful tools for the study of abnormal synchronous oscillations of PD (Rubin, 2017). Using these ideas and methods of nonlinear dynamics, the pathogenic mechanism of these oscillations can be understood (Rubchinsky, Park, & Worth, 2012). Simulation results show that synchronized activity disrupts the thalamic reliability neurons (TC) to transmit sensory motor signals which may lead to akinesia, rigidity and other symptoms (Pirini et al., 2009, Rubin and Terman, 2004, van Albada and Robinson, 2009). These results can provide theoretical evidence for clinical applications.
So far, deep brain stimulation (DBS) has been considered as the most effective way to treat PD. It has been reported that the degree of Parkinson’s pathological symptoms decreases almost linearly with the increase of DBS frequency which is usually 130–185 Hz (Santaniello, Gale, & Sarma, 2018). The effectiveness of DBS relies on the parameters of the electrical pulses, including frequency, pulse width, and amplitude. In the treatment of most patients, the average stimulation frequencies are determined as 152 Hz for subthalamic nucleus-DBS (STN-DBS) and 162 Hz for globus pallidus internus-DBS (GPi-DBS) (Okun et al., 2012). The parameter configuration of DBS is different from patients to patients (Picillo, Lozano, Kou, Puppi Munhoz, & Fasano, 2016). Plenty of studies have shown that well-designed irregular, low-frequency stimulation patterns may have clinical advantages compared with the high-frequency, conventional DBS (Akbar et al., 2016, Brocker et al., 2017, Brocker et al., 2013, Santaniello et al., 2018), and they have highlighted the potential superiorities of low frequency DBS and encouraged further development of DBS optimization issues. Wongsarnpigoon and Grill proposed to replace the rectangular waveforms with the Gaussian energy efficient DBS waveforms (Wongsarnpigoon & Grill, 2010). Daneshzand et al. introduced a Gaussian Delay Gaussian (GDG) waveforms to disrupt pathological synchronization behavior (Daneshzand, Faezipour, & Barkana, 2017). The stimulation signal is usually performed on a fixed target area of the BG. STN and GPi are usually standard anatomical targets for DBS. Due to the characteristics of HF DBS and long-term processes (Rizzone, 2001), the stimulation intensity is often disruptive and excessive. In clinical applications, stimulation parameters are critical, and stimulation needs to be effective enough to achieve energy savings and avoid side effects. For this purpose, some multi-site and multi-nuclear stimulation strategies have developed. Guo and Rubin developed a multi-site stimulation of STN to diminish TC errors (Guo & Rubin, 2011). Popovych and Tass introduced a coordinated reset stimulation which was stimulated by multiple stimulation sites to achieve a spatially coordinated phase reset in the subpopulations (Popovych & Tass, 2014). Then, a new triplet-structure coordinated reset multi-nuclear stimulation paradigm was proposed to the treatment of PD by Fan and Wang (2015). Meanwhile, a novel pulsatile multisite linear delayed feedback stimulation method is developed (Popovych & Tass, 2018), which can achieve a better desynchronization effect. This feedback stimulus which is more intelligent than the normal DBS can be adjusted based on the brain’s electrical signals. So the energy required to perform this stimulus can be maintained at a low level.
BG is a set of interconnected subcortical nuclei of the brain which is related to PD. The loss of dopaminergic input changes the dynamics of the BG, which affects the thalamus and cortex and in turn affects the cerebellum (Bostan & Strick, 2010). The best targets for implementing DBS depend on electrophysiology and macro stimulation, and the most common targets for DBS in PD are GPi and STN. Although surgical experience with globus pallidus externa (GPe) is so far not that positive, some modeling and physiological results show that targeting GPe for DBS to eliminate Parkinson’s motor symptoms is much better than GPi-DBS (Daneshzand, Ibrahim, et al., 2017, Pirini et al., 2009, Vitek et al., 2004). Preceding multi-nuclear stimulation strategies do not consider the optimal combination of the stimulus targets. Innovations in stimulating targets have rarely been considered in previous studies, and it is necessary to find the best combination of stimulating targets to decrease stimulation frequency and reduce the side effects of stimuli. This paper aims to propose new stimulation methods to decrease the symptoms of PD and reduce energy consumption.
It is of great significance to study the dynamic behavior of PD, so various mathematical models have been proposed to reproduce the physiological and pathological activities of these nuclei (Pirini et al., 2009, Rubin and Terman, 2004, Schiff, 2010, So et al., 2012, Terman et al., 2002, van Albada and Robinson, 2009). Based on the basal ganglia-thalamic (BGTC) circuit, Rubin and Terman established a model composed of several different types of neuronal populations (Rubin & Terman, 2004), which is improved by reconstructing the network topology (So et al., 2012). Here we use this model of BGTC network to study the effect of combined DBS of two nuclei (CDBS) on PD. DBS techniques have been employed to disrupt the synchronization behavior (Liang and Wang, 2019, Montaseri et al., 2015, Qin et al., 2013). Therefore, the numerical study of CDBS is mainly based on its ability to de-synchronize, restore the relay capability of the TC, and reduce the energy of the beta band (13–30 Hz). We first propose three stimulation strategies based on different combination of stimulating targets: STN and GPe CDBS (SED), GPe and GPi CDBS (GGD), STN and GPi CDBS (SID). The phase difference between two DBSs would be an important factor of neuron behaviors in the BG, which will be considered in CDBS. Further, we explore the optimal stimulation parameters for the CDBS with phase difference.
Section snippets
Model of basal ganglia–thalamus network
The computational model used in this work is a modified BGTC model network proposed by So et al. (2012). This network includes four types of neurons: GPe, STN, GPi, and TC. Each nucleus is composed of 10 neurons. Sparse connections are used within the BGTC network. As shown in Fig. 1A, each STN neuron can send excitations to the nearest two GPe neurons and two GPi neurons simultaneously. Each GPe neuron projects an inhibitory neurotransmitter to two immediate neighboring STN neurons, two GPe
Effects of different phase-deviation stimulations
We use the computational model of So et al. (2012) to simulate the neuronal firing patterns of various nuclei in healthy and parkinsonian states. The pathogenesis of PD is established by varying the currents applied to different nuclei of the BG. In Fig. 3A, it can be seen that, in the healthy state, TC neurons can transmit the cortical pulse signals faithfully. STN, GPe and GPi neurons exhibit random spiking firing. By calculation, we get EI 0 and SL 0.22. However, in the parkinsonian
Conclusion and discussion
DBS has become a conventional treatment for a variety of neurodegenerative diseases such as Parkinson’s disease. In general, for parkinsonian patients, the frequency of DBS is above 130 Hz for any target in the BG. This high-frequency continuous stimulation for a single nuclear can lead to physical damage to the brain tissue and some prominent side effects.
In this paper, three different CDBS are proposed, i.e., SED, SID, and GGD. First, we investigate the effects of DBS1 and DBS2 with different
Acknowledgment
This research was supported by the National Science Foundation of China (Grants 11572015, 11772019).
References (44)
- et al.
Randomized, blinded pilot testing of nonconventional stimulation patterns and shapes in Parkinson’s disease and essential tremor: Evidence for further evaluating narrow and biphasic pulses: RANDOMIZED, BLINDED PILOT TESTING NONCONVENTIONAL DBS PULSES
Neuromodulation: Technology at the Neural Interface
(2016) - et al.
Improved efficacy of temporally non-regular deep brain stimulation in Parkinson’s disease
Experimental Neurology
(2013) - et al.
Current steering to activate targeted neural pathways during deep brain stimulation of the subthalamic region
Brain Stimulation
(2012) - et al.
Improving desynchronization of parkinsonian neuronal network via triplet-structure coordinated reset stimulation
Journal of Theoretical Biology
(2015) - et al.
Pathophysiology of Parkinsonism
Clinical Neurophysiology
(2008) - et al.
Multi-site stimulation of subthalamic nucleus diminishes thalamocortical relay errors in a biophysical network model
Neural Networks
(2011) - et al.
Current-controlled deep brain stimulation reduces in vivo voltage fluctuations observed during voltage-controlled stimulation
Clinical Neurophysiology
(2010) - et al.
Designing a deep brain stimulator to suppress pathological neuronal synchrony
Neural Networks
(2015) - et al.
Pathophysiology of the basal ganglia in Parkinson’s disease
Trends in Neurosciences
(2000) - et al.
Subthalamic deep brain stimulation with a constant-current device in Parkinson’s disease: An open-label randomised controlled trial
The Lancet Neurology
(2012)
Programming deep brain stimulation for Parkinson’s disease: The toronto western hospital algorithms
Brain Stimulation
Control of synchronization and spiking regularity by heterogenous aperiodic high-frequency signal in coupled excitable systems
Communications in Nonlinear Science and Numerical Simulation
Computational models of basal ganglia dysfunction: The dynamics is in the details
Current Opinion in Neurobiology
Beta oscillations in the cortico-basal ganglia loop during parkinsonism
Experimental Neurology
Mean-field modeling of the basal ganglia-thalamocortical system. II
Journal of Theoretical Biology
Mean-field modeling of the basal ganglia-thalamocortical system. I
Journal of Theoretical Biology
The cerebellum and basal ganglia are interconnected
Neuropsychology Review
Optimized temporal pattern of brain stimulation designed by computational evolution
Science Translational Medicine
Effects of dopamine depletion on information flow between the subthalamic nucleus and external globus pallidus
Journal of Neurophysiology
Computational stimulation of the basal ganglia neurons with cost effective delayed Gaussian waveforms
Frontiers in Computational Neuroscience
Desynchronization and energy efficiency of Gaussian neurostimulation on different sites of the basal ganglia
Failure of delayed feedback deep brain stimulation for intermittent pathological synchronization in Parkinson’s disease
PLoS One
Cited by (26)
Bifurcation analysis of a Parkinson's disease model with two time delays
2024, Mathematics and Computers in SimulationStability of Hopfield neural network with resistive and magnetic coupling
2023, Chaos, Solitons and FractalsThe possible mechanism of direct feedback projections from basal ganglia to cortex in beta oscillations of Parkinson's disease: A theoretical evidence in the competing resonance model
2023, Communications in Nonlinear Science and Numerical SimulationExploring phase–amplitude coupling from primary motor cortex-basal ganglia–thalamus network model
2022, Neural NetworksCitation Excerpt :Therefore, the correlation between M1 and STN seems to provide a new approach for us to study the dynamic mechanism of PD (Sanders & Jaeger, 2016). However, in previous modeling studies on PD, we focused on the interior of the BG, and studied the PD related abnormal behavior caused by the firing changes of various nuclei in the BG (Yu, Hao and Wang, 2020; Yu, Wang, Wang and Wang, 2020). The projection from M1 to STN is mainly through the classic hyperdirect pathway, and the influence of STN on M1 is generally to be achieved through multi-nuclei connections such as STN- globus pallidus interna (GPi) -thalamus -cortex (Yu, Wang et al., 2020).
Model-based Quantitative optimization of deep brain stimulation and prediction of Parkinson's states
2022, NeuroscienceCitation Excerpt :Also, the inhibitory and excitatory effects of DBS were emphasized (Boraud et al., 1996; Dostrovsky et al., 2000; Johnson and Mcintyre, 2008; Mccairn and Turner, 2009; Galati et al., 2010; Lafreniere-Roula et al., 2010; Reese et al., 2011; Chiken and Nambu, 2013; Alavi et al., 2021). Other studies were conducted for multi-site and multi-nuclear stimulation strategies (Guo and Rubin, 2011), triplet-structure coordinated reset multi-nuclear stimulation paradigm (Popovych and Tass, 2014), pulsatile multisite linear delayed feedback stimulation method (Popovych and Tass, 2018), and combined DBS of dual nuclei (Yu et al., 2019). In order to overcome the shortcomings in the clinical application of DBS, this paper proposes a BG network model for personalized treatment.