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Neurostimulation involves modulation of the nervous system and electrically activate neurons in the body. The activation of neural elements in a part of the nervous system can be effectively facilitated by stimulation. Micro-electrodes are utilized to interface with excitable tissue in order to either restore recording experiences to the implant recipient or control an effector organ. Neurostimulation technology improves the life quality of those who are severely paralyzed or suffering from profound losses to various sense organs. It serves as the key part of neural prosthetics for hearing aid, artificial vision, artificial limbs, and brain-machine interfaces. In the case of neural stimulation, mostly an electrical stimulation is utilized and charge-balanced biphasic constant current waveforms or capacitively coupled charge injection approaches are adopted. Alternatively, the transcranial magnetic stimulation has been proposed as a non-invasive method in which a magnetic field causes neurostimulation.
The primary findings about stimulation originated from the idea to stimulate nerves for therapeutic purposes. The 1st recorded use of electrical stimulation for pain relief goes back to 46 AD, when Scribonius Largus used torpedo fish (electric ray) for relieving headaches. In the late 18th century, Luigi Galvani discovered that the muscles of dead frog legs twitched when struck by direct current on the nervous system. The modulation of the brain activity by electrical stimulation of the motor cortex in dogs was shown in 1870 that resulted in limb movement. From the late 18th century to today many milestones have been developed. Nowadays, sensory prosthetic devices, such as visual implants, cochlear implants, auditory midbrain implants, and spinal cord stimulators and also motor prosthetic devices, such as deep brain stimulators, Bion microstimulators, the brain control and sensing interface, and cardiac electro-stimulation devices are widely used.
Brain stimulation has potentials to treat some disorders such as epilepsy. In this method, scheduled stimulation is applied to specific cortical or subcortical targets. There are available commercial devices  that can deliver an electrical pulse at scheduled time intervals. Scheduled stimulation is hypothesized to alter the intrinsic neurophysiologic properties of epileptic networks. The most explored targets for scheduled stimulation are the anterior nucleus of the thalamus and the hippocampus. The anterior nucleus of the thalamus has been studied, which has shown a significant seizure reduction with the stimulator ‘‘on’’ versus ‘‘off’’ during several months after stimulator implantation. Moreover, the cluster headache (CH) can be treated by using a temporary stimulating electrode at sphenopalatine ganglion (SPG). Pain relief is reported within several minutes of stimulation in this method.
Deep Brain Stimulation (DBS)
Deep brain stimulation (DBS) has shown benefits for movement disorders such as Parkinson’s disease, tremor and dystonia and affective disorders such as depression, obsessive-compulsive disorder, Tourette syndrome, chronic pain and cluster headache. Since DBS can directly change the brain activity in a controlled manner, it is used to map fundamental mechanisms of brain functions along with neuroimaging methods. A simple DBS system consists of two different parts. First, tiny microelectrodes are implanted in the brain to deliver stimulation pulses to the tissue. Second, an electrical pulse generator (PG) generates stimulation pulses, which is connected to the electrodes via microwires. Physiological properties of the brain tissue, which may change with disease state, stimulation parameters, which include amplitude and temporal characteristics, and the geometric configuration of the electrode and the surrounding tissue are all parameters on which DBS of both the normal and the diseased brain depend on. In spite of a huge amount of studies on DBS, its mechanism of action is still not well understood. Developing DBS microelectrodes is still challenging.
Spinal Cord Stimulation (SCS)
Spinal cord stimulation (SCS) is an effective therapy for the treatment of chronic and intractable pain including diabetic neuropathy, failed back surgery syndrome, complex regional pain syndrome, phantom limb pain, ischemic limb pain, refractory unilateral limb pain syndrome, postherpetic neuralgia and acute herpes zoster pain. Another pain condition that is a potential candidate for SCS treatment is Charcot-Marie-Tooth (CMT) disease, which is associated with moderate to severe chronic extremity pain. SCS therapy consists of the electrical stimulation of the spinal cord to ‘mask’ pain. The gate theory proposed in 1965 by Melzack and Wall  provided a theoretical construct to attempt SCS as a clinical treatment for chronic pain. This theory postulates that activation of large diameter, myelinated primary afferent fibers suppresses the response of dorsal horn neurons to input from small, unmyelinated primary afferents. A simple SCS system consists of three different parts. First, microelectrodes are implanted in the epidural space to deliver stimulation pulses to the tissue. Second, an electrical pulse generator implanted in the lower abdominal area or gluteal region while is connected to the electrodes via wires, and third a remote control to adjust the stimulus parameters such as pulse width and pulse rate in the PG. Improvements have been made in both the clinical aspects of SCS such as transition from subdural placement of contacts to epidural placement, which reduces the risk and morbidity of SCS implantation, and also technical aspects of SCS such as improving percutaneous leads, and fully implantable multi-channel stimulators. However, there are many parameters that need to be optimized including number of implanted contacts, contact size and spacing, and electrical sources for stimulation. The stimulus pulse width and pulse rate are important parameters that need to be adjusted in SCS, which are typically 400 us and 8–200 Hz respectively.
Transcranial Magnetic Stimulation (TMS)
Compared to electrical stimulation that utilizes brief, high-voltage electric shock to activate neurons, which can potentially activate pain fibers, transcranial magnetic stimulation (TMS) was developed by Baker in 1985. TMS uses a magnetic wire above the scalp, which carries a sharp and high current pulse. A time variant magnetic filed is induced perpendicular to the coil due to the applied pulse which consequently generates an electric field based on Maxwell law. The electric field provides the necessary current for a non-invasive and much less painful stimulation. There are two TMS devices called single pulse TMS and repetitive pulse TMS (rTMS) while the latter has greater effect but potential to cause seizure. TMS can be used for therapy particularly in psychiatry, as a tool to measure central motor conduction and a research tool to study different aspects of human brain physiology such as motor function, vision, and language. The rTMS method has been used to treat epilepsy with rates of 8–25 Hz for 10 seconds. The other therapeutic uses of rTMS include parkinson diseases, dystonia and mood diseases. Also TMS can be used to determine the contribution of cortical networks to specific cognitive functions by disrupting activity in the focal brain region.
Cochlear implants have provided partial hearing to more than 120,000 persons worldwide as of 2008. The electrical stimulation is used in a cochlear implant to provide functional hearing in totally deafened persons. Cochlear implants include several subsystem components from the external speech processor and radio frequency (RF) transmission link to the internal receiver, stimulator, and electrode arrays. Modern cochlear implant research started in the 1960s and 1970s. In 1961, a crude single electrode device was implanted in two deaf patients and useful hearing with electric stimulation was reported. The first FDA approved complete single channel device was released in 1984. In cochlear implants, the sound is picked up by a microphone and transmitted to the behind-the-ear external processor to be converted to the digital data. The digitized data is then modulated on a radio frequency signal and transmitted to an antenna inside a headpiece. The data and power carrier are transmitted through a pair of coupled coils to the hermetically sealed internal unit. By extracting the power and demodulating the data, electric current commands are sent to the cochlea to stimulate the auditory nerve through microelectrodes. The key point is that the internal unit does not have a battery and it should be able to extract the required energy. Also to reduce the infection, data is transmitted wirelessly along with power. Inductively coupled coils are the best candidate for power and data telemetry. Parameters needed by the internal unit include the pulse amplitude, pulse duration, pulse gap, active electrode, and return electrode that are used to define a biphasic pulse and the stimulation mode. An example of the commercial devices include Nucleus 22 device that utilized a carrier frequency of 2.5 MHz and later in the newer revision called Nucleus 24 device, the carrier frequency was increased to 5 MHz. The internal unit in the cochlear implants is an ASIC (Application-Specific Integrated Circuit) chip that is responsible to ensure safe and reliable electric stimulation. Inside the ASIC chip, there is a forward pathway, a backward pathway, and control units. The forward pathway recovers digital information from the RF signal which includes stimulation parameters and some handshaking bits to reduce the communication error. The backward pathway usually includes a back telemetry voltage sampler that reads the voltage over a period of time on the recording electrode. The stimulator block is responsible to deliver predetermined current by external unit to the microelectrodes. This block includes a reference current and a digital to analog converter to transform digital commands to an analog current.
Theoretical and experimental clinical evidences suggest that direct electrical stimulation of the retina might be able to provide some vision to subjects who have lost the photoreceptive elements of their retina. Therefore, visual prostheses are developed to restore vision for the blind by using the stimulation. Depending upon which visual pathway location is targeted for neural stimulation, different approaches have been considered. Visual pathway consists mainly of the eye, optic nerve, lateral geniculate nucleus (LGN), and visual cortex. Therefore retinal, optic nerve and visual cortex stimulation are the three different methods used in visual prostheses. Retinal degenerative diseases, such as retinitis pigmentosa (RP) and age-related macular degeneration (AMD), are two likely candidate diseases in which retinal stimulation may be helpful. Three approaches called intraocular epiretinal, subretinal and extraocular transretinal stimulation are pursued in retinal devices that stimulate remaining retinal neural cells to bypass lost photoreceptors and allow the visual signal to reach the brain via the normal visual pathway. In epiretinal approach, electrodes are placed on the top side of the retina near ganglion cells, whereas the electrodes are placed under the retina in subretinal approaches. Finally, the posterior scleral surface of the eye is the place in which extraocular approach electrodes are positioned. Second Sight and the Humayun group at USC are the most active groups in the design of intraocular retinal prostheses. The ArgusTM 16 retinal implant is an intraocular retinal prosthesis utilizing video processing technologies. Regarding to the visual cortex stimulation, Brindley, and Dobelle were the first ones who did the experiments and demonstrated that by stimulating the visual cortex most of the electrodes can produce visual percept.
LGN, which is located in the midbrain to relay signals from the retina to the visual cortex, is another potential area that can be used for stimulation. But this area has limited access due to surgical difficulty. The recent success of deep brain stimulation techniques targeting the midbrain has encouraged research to pursue the approach of LGN stimulation for a visual prosthesis.
Cardiac Electrostimulation Devices
Implantable pacemakers were proposed for the first time in 1959 and became more sophisticated since then. The therapeutic application of pacemakers consists of numerous rhythm disturbances including some forms of tachycardia (too fast a heart beat), heart failure, and even stroke. Early implantable pacemakers worked only a short time and needed periodic recharging by an inductive link. These implantable pacemakers needed a pulse generator to stimulate heart muscles with a certain rate in addition to electrodes. Today, modern pulse generators are programmed non-invasively by sophisticated computerized machines using RF, obtaining information about the patient’s and device’s status by telemetry. Also they use a single hermetically sealed lithium iodide (LiI) cell as the battery. The pacemaker circuitry includes sense amplifiers to detect the heart’s intrinsic electrical signals, which are used to track heart activity, rate adaptive circuitry, which determine the need for increased or reduced pacing rate, a microprocessor, memory to store the parameters, telemetry control for communication protocol and power supplies to provide regulated voltage.
Stimulation Microelectrode Technologies
Microelectrodes are one of the key components of the neurostimulation, which deliver the current to neurons. Typical microelectrodes have three main components: a substrate (the ‘‘carrier’’), a conductive metal layer, and an insulation material. In cochlear implants, microelectrodes are formed from platinum-iridium alloy. State-of-the-art electrodes include deeper insertion to better match the tonotopic place of stimulation to the frequency band assigned to each electrode channel, improving efficiency of stimulation, and reducing insertion related trauma. These cochlear implant electrodes are either straight or spiral such as Med El Combi 40+ and Advanced Bionics Helix microelectrodes respectively. In visual implants, there are two types of electrode arrays called planar type or three dimensional needle or pillar type, where needle type array such as Utah array is mostly used for cortical and optic nerve stimulations and rarely used in retinal implants due to the possible damage of retina. However, a pillar-shaped gold electrode array on thin-film polyimide has been used in an extraocular implant. On the other hand, planar electrode arrays are formed from flexible polymers, such as silicone, polyimide, and parylene as candidates for retinal implants. Regarding to DBS microelectrodes an array, which can be controlled independently, distributed throughout the target nucleus would permit precise control of the spatial distribution of the stimulation, and thus, allow better personalized DBS. There are several requirements for DBS microelectrodes that include long lifetime without injury to the tissue or degradation of the electrodes, customized for different brain sites, long term biocompatibility of the material, mechanically durable in order to reach the target without being damaged during handling by the implant surgeon, and finally uniformity of performance across the microelectrodes in a particular array. Tungsten microwire, iridium microwires, and platinum–iridium microelectrodes are the examples of microelectrode used in DBS.
Non-clinical (Laboratory) Stimulation Applications
In addition to the enormous usage of neurostimulation for clinical applications, it is also used widely in laboratories started dates back to 1920s by people link Delgado who used stimulation as an experimental manipulation to study basics of how the brain works. The primary works were on the reward center of the brain in which stimulation of those structures led to pleasure that requested more stimulation. Another most recent example is the electrical stimulation of the MT area of primary visual cortex to bias perception. In particular, the directionality of motion is represented in a regular way in the MT area. They presented monkeys with moving images on screen and monkey throughput was to determine what the direction is. They found that by systematically introducing some errors to the monkey’s responses, by stimulating the MT area which is responsible for perceiving the motion in another direction, the monkey responded to somewhere in between the actual motion and the stimulated one. This was an elegant use of stimulation to show that MT area is essential in the actual perception of motion. Within the memory field, stimulation is used very frequently to test the strength of the connection between one bundle of cells to another by applying a small current in one cell which results in the release of neurotransmitters and measuring the postsynaptic potential. Generally a short but high frequency current such as 100 Hz helps strengthening the connection called as long term potentiation. However, longer but low frequency current leads to weaken the connections called as long term depression. Finally, combining neurostimulation with neural recording devices can lead us to the brain-computer interface, which currently seems to be more than just a reality, but a daily necessity.
- Brain-computer interface
- implanted pulse generator
- Transcutaneous electrical nerve stimulation
- Sexual stimulation
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- ↑ 2.0 2.1 Hallett M (July 2000). Transcranial magnetic stimulation and the human brain. Nature 406 (6792): 147–50.
- ↑ Jensen JE, Conn RR, Hazelrigg G, Hewett JE (1985). The use of transcutaneous neural stimulation and isokinetic testing in arthroscopic knee surgery. Am J Sports Med 13 (1): 27–33.
- ↑ Weisstein, Eric W. (2002). Galvani, Luigi (1737–1798). Eric Weisstein's World of Scientific Biography. Wolfram Research.
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- ↑ 6.0 6.1 6.2 6.3 Greenbaum, Elias S.; David Zhou (2009). Implantable Neural Prostheses 1: Devices and Applications, Berlin: Springer.
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- ↑ Jobst BC, Darcey TM, Thadani VM, Roberts DW (July 2010). Brain stimulation for the treatment of epilepsy. Epilepsia 51 (Suppl 3): 88–92.
- ↑ Ansarinia M, Rezai A, Tepper SJ, et al. (July 2010). Electrical stimulation of sphenopalatine ganglion for acute treatment of cluster headaches. Headache 50 (7): 1164–74.
- ↑ Kringelbach ML, Jenkinson N, Owen SL, Aziz TZ (August 2007). Translational principles of deep brain stimulation. Nat. Rev. Neurosci. 8 (8): 623–35.
- ↑ Skaribas I.M., Washburn S.N. (January 2010). Successful treatment of charcot-marie-tooth chronic pain with spinal cord stimulation: A case study. Neuromodulation 13 (3): 224–8.
- ↑ Melzack R, Wall PD (November 1965). Pain mechanisms: a new theory. Science 150 (3699): 971–9.
- ↑ House WF, Urban J (1973). Long term results of electrode implantation and electronic stimulation of the cochlea in man. Ann. Otol. Rhinol. Laryngol. 82 (4): 504–17.
- ↑ An SK, Park SI, Jun SB, et al. (June 2007). Design for a simplified cochlear implant system. IEEE Trans Biomed Eng 54 (6 Pt 1): 973–82.
- ↑ P. Crosby, C. Daly, D. Money, and et al., Aug. 1985, ” Cochlear implant system for an auditory prosthesis,” United States Patent 4532930.
- ↑ Ghovanloo M., Najafi K. (December 2004). A modular 32-site wireless neural stimulation microsystem. IEEE J. Solid State Cir. 39: 2457–66.
- ↑ Clausen J (1955). Visual sensations (phosphenes) produced by AC sine wave stimulation. Acta Psychiatr Neurol Scand Suppl 94: 1–101.
- ↑ Weiland J.D., Humayun M.S. (July 2008). Visual prosthesis. Proceedings of the IEEE 96 (7): 1076–84.
- ↑ Humayun MS, de Juan E, Dagnelie G, Greenberg RJ, Propst RH, Phillips DH (January 1996). Visual perception elicited by electrical stimulation of retina in blind humans. Arch. Ophthalmol. 114 (1): 40–6.
- ↑ Chow AY, Chow VY (March 1997). Subretinal electrical stimulation of the rabbit retina. Neurosci. Lett. 225 (1): 13–6.
- ↑ Pezaris JS, Reid RC (May 2007). Demonstration of artificial visual percepts generated through thalamic microstimulation. Proc. Natl. Acad. Sci. U.S.A. 104 (18): 7670–5.
- ↑ Elmvquist R., Senning A. (1960). "Implantable pacemaker for the heart" Smyth CN Medical electronics, Paris: Iliffe & Sons.
- ↑ Warren J., Nelson J. (2000). "Pacemakers and ICD pulse generator circuitry" Ellenbogen KA, Kay GN, Wilkoff BL Clinical cardiac pacing and defibrillation, 2nd, 194–216, Philadelphia: WB Saunders.
- ↑ Interview with Dr. J. Manns, Emory University, Oct. 2010
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