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Jo, Oh, and Lee: Microelectromechanical Systems-Based Neurotools for Non-Invasive Ultrasound Brain Stimulation


In the current aging society, the number of patients suffering from degenerative brain diseases is continuously increasing. However, many of these brain disorders are intractable and difficult to treat. Non-invasive brain stimulation is an attractive alternative method to a pharmaceutical approach that attempts to treat brain disorders through physical stimulation. Among the various direct brain stimulation techniques, such as electrical, magnetic, and optical, ultrasound has been proposed as a new modality for neuromodulation due to its distinct advantages such as high spatial resolution and in-depth targeting. As ultrasound modality is still in the early stages of development, further investigations on various aspects such as neuromodulation mechanism, therapeutic effects, and safety are still required. Although ultrasound technology is a mature biomedical tool developed from ultrasound imaging, many new technological advancements such as miniaturized devices based on microelectromechanical systems technology have been recently introduced for the specific purpose of neuromodulation. In this review, we introduce these new neurotools which are essential to uncovering the fundamental mechanisms of ultrasound brain stimulation and ultimately to developing an effective therapeutic means for brain disorders.


While the number of people suffering from brain disorders continues to increase in the modern aging society, it is still a challenge to develop effective treatments for many of these diseases. For example, the risk of Alzheimer’s disease (AD), an age-dependent disorder, doubles every five years after the age of 65. However, there is still no medication to treat AD. While pharmaceutical means offers the highest patient compliance, it is difficult to discover an effective drug for brain disorders because of the existence of the brain-blood barrier (BBB) within the brain capillary endothelia [1]. BBB, a tight junction that exists between the blood vessel and extracellular space of the brain, allows passage of only a fraction of small-molecule drugs. In addition to this physical limitation, the pharmacological approach suffers from drug resistance, sideeffects, tolerance, and dependence, which further complicates the pharmaceutical method to treat brain disorders.
Thus, direct brain stimulation serves as a promising alternative for the treatment of brain disorders. A number of modalities, such as electrical, magnetic, and optical, have been explored to treat brain disorders and modulate brain activities. Electrical stimulation, such as transcranial direct current stimulation (tDC), transcranial alternating current stimulation (tAC), and deep brain stimulation (DBS), is the most commonly used method of direct brain stimulation [2-4]. Although invasive, DBS is currently clinically used to treat Parkinson’s disease through implantation of a long probe to the target region of the brain [3,5]. A relatively new modality, optical stimulation, is based on genetic modification of cells with light-sensitive opsins and thus allows for cell-type specific stimulation with high spatial resolution [6]. However, while DBS and optical stimulation are capable of achieving high spatial resolution and deep penetration depth, the operation is highly invasive, which results in low patient compliance and limited clinical application. Transcranial magnetic stimulation (TMS), which induces electrical activity within the brain through a magnetic field, is widely used for the treatment of depression [7]. However, TMS is limited to the stimulation of shallow regions and it is difficult to achieve high spatial resolution [8].
Deep brain regions such as the subthalamic nucleus, globus pallidus, and ventral intermediate nucleus of the thalamus are often associated with many critical brain circuits and stimulation of such regions have shown to alleviate the symptoms of various disorders, such as pain, tremor, depression, and addiction [9-11]. Yet, there have been no reports of a non-invasive stimulation modality that has targeted these deep brain regions with high spatial resolution. Non-invasiveness is a crucial feature of neuromodulation as high patient compliance implies an increase in the number of applicable pathologies. Among the various direct brain stimulation modalities, optogenetics is highly invasive, TMS is limited in penetration depth, and electrical stimulation suffers from low spatial resolution. Thus, there is an imperative need for a non-invasive modality, which is capable of both in-depth targeting and high spatial resolution.
Low-intensity transcranial focused ultrasound stimulation (LIFU or tFUS) is a promising modality for direct brain stimulation because of its inherent advantage of focusing capability [12]. Ultrasound can be focused either through a mechanical means using an acoustic lens or through an electrical means using a beam-forming array of ultrasound transducers. In addition to beam-steering capabilities, tFUS offers various advantages such as non-invasiveness, in-depth targeting, and technical maturity of ultrasound technology [13]. By calibrating for attenuation and scattering through the skull, an ultrasound beam with a focal point away from the transducer surface can target deep brain regions without exposing the other regions within its focal width to a strong intensity of ultrasound. Most importantly, because of the long history of ultrasound medical imaging, technological and biophysical aspects such as beam-forming, circuit integration, magnetic resonance (MR) compatibility, skull and scattering modeling, transducer design, and biological effects are well established [14-16].
Consequently, many studies have been conducted on tFUS over the past decade including investigations into in vivo effects in small animals to large non-human primates [17-25], neuromodulation mechanisms [26-28], safety [12], and stimulation protocols [28]. Compared to other direct brain stimulation modalities, ultrasound stimulation is a relatively new methodology and requires further investigation of the exact neuromodulation mechanisms, therapeutic effects, and safety as a potential clinical tool. However, in order to investigate in vivo and in vitro effects, the current tFUS device technology is limited in terms of size, portability, and spatial resolution. For example, due to the abundance of rodent disease models, mice in vivo experiments are useful in the evaluation of the therapeutic effects of tFUS. However, ultrasound transducer systems used for mice in vivo experiments are not only heavy and bulky but also require large collimators [20-22]. Thus, there is a need to develop a new set of neurotools based on microelectromechanical systems (MEMS), which enables fabrication of devices at the micron scale with high accuracy and reproducibility. In this review, the new types of MEMS-based neurotools specifically developed for in vitro and in vivo tFUS is summarized in detail.


The neuromodulation mechanism of ultrasound must be clearly understood in order for tFUS to be accepted as a new treatment in clinical applications. Although many hypotheses have been proposed, there is yet a universal agreement on the exact mechanism of ultrasound neuromodulation [13,26,27,29,30]. Hypotheses on heat activation and modulation of membranes due to cavitation have been proposed but are limited to higher intensities of ultrasound stimulation than that required for neuromodulation [30]. New hypotheses focus on the biophysical effects of acoustic radiation force generated by ultrasound such as modulation of mechanosensitive channels and mechanical plasma deformation [27,29,30].
For evaluating the effects of radiation force in the cellular level, the existing ultrasound stimulation technology is too bulky to devise a compact system and it is difficult to devise a single system with variable frequency, variable intensity, and high throughput. For example, the work on ultrasound neuromodulation of sciatic nerves used a commercially available bulky transducer with a 1.1 MHz center frequency [31]. Not only was the focal area large with an ellipsoidal focal region (1.3 mm wide and 9.7 mm long), but the overall system was also tens of centimeters in size because the width of the transducer was 6.5 cm (Figure 1A). On the other hand, MEMS-based ultrasound transducers, such as capacitive micromachined ultrasound transducers (CMUT), piezoelectric micromachined ultrasound transducers (PMUT), and piezoelectric ultrasound transducers (PUT), allow for a wide range of experiments to investigate ultrasound neuromodulation mechanisms. By utilizing micromachining technology, ultrasound transducers with a wide range of frequencies, varying intensities, and diverse shapes (e.g., linear, circular, and ring arrays) can be readily fabricated [32-34].
For in vitro application, Ko et al. [35] demonstrated for the first time a PMUT array capable of neuromodulation of cultured cells with a high spatial resolution. The proposed PMUT array consisted of 16 elements [one-dimensional (1D) array] and exhibited a resonant frequency of 780 kHz in immersion with 8 mW/cm2 of spatial-peak temporal-average intensities (ISPTA) (Figure 1B). The fabricated device was custom-packaged on a printed circuit board (PCB) with a biocompatible polydimethylsiloxane (PDMS) chamber. This setup allowed for continuous flow of medium to sustain the viability of the cultured cells. To observe the ultrasound neuromodulation using the PMUT device, transient receptor potential ankyrin 1 (TRPA1) channels, a mechanoreceptor that mediates intracellular Ca2+ transient, were expressed in the human embryonic kidney (HEK) 293T cells. By using Fura-2 ratiometric Ca2+ imaging, successful neuromodulation using the PMUT was demonstrated for the first time. Compared to the 6.4-cm-wide single-element commercial transducer, the newly developed 1Darray PMUT fabricated using MEMS technology consisted of 500-μm-diameter elements, which allows for highly localized targeting. Thus, further development of MEMS-based ultrasound neurotools could allow simultaneous neuromodulation of different ultrasound frequencies and intensities.


MEMS-based in vivo neurotools are also essential in expanding the horizon of ultrasound neuromodulation. These tools not only facilitate in vivo experiments to uncover the mechanism of neuromodulation, but also allows neuroscientists to evaluate the effects of ultrasound on various brain functions. While the investigation into neuromodulation mechanisms is often conducted in vitro, recently, two in vivo experiments have been reported that demonstrated an indirect pathway of ultrasound neuromodulation through auditory or cochlear neuronal circuits [36,37]. In addition, ultrasound modality, which is non-invasive and highly patient compliant, has great potential to be used to treat brain disorders. Thus, the effects of ultrasound neuromodulation on various brain functions, such as sensory, motor, and cognition, need to be investigated. Since the effects are often monitored through behavior studies, ultrasound neuromodulation in vivo setup must be compact and light to accommodate freely-moving animal experiments. In addition, when such freely-moving systems are developed, it would be possible to observe the long-term safety of ultrasound neuromodulation without the need for anesthesia and stereotaxic fixation.
Since MEMS technology enables fabrication of miniaturized devices with high accuracy and versatile functionality, MEMS-based ultrasound transducers are excellent candidates for behavioral studies. Most of the previous works demonstrated ultrasound neuromodulation on immobile or sedated animals because commercially available transducers are often bulky, heavy, and requires a collimator [19-25]. Recently, three pioneering works on MEMS-based ultrasound transducers have successfully demonstrated in vivo neuromodulation in freely-moving behaving animals [38-41]. The first of these reports was based on a CMUT ring array composed of 32 elements with a 183-kHz resonant frequency [38,39]. The overall system was 0.73 g in weight and no collimator was required for the system (Figure 2).
The other two works were based on piezoelectric transducers (Table 1) [40,41]. Lee et al. [41] developed a miniaturized tFUS system for freely-moving animals. The transducer was about 6 g in weight and packaged in a three-dimensional-printed wearable headgear. The developed freely-moving system was verified by performing tFUS in awake and anesthetized groups. Li et al. [40] optimized the size of the PZT and produced piezoelectric transducers with 5 mm in diameter and 0.49 g in weight. By attaching a concave epoxy acoustic lens in front of the transducer, a lateral spatial resolution of 1.2 mm was achieved. The effect of ultrasonic neuromodulation was demonstrated by observing the changes in the in situ electrophysiological signals. In addition to these works, beam-forming circuitry has been implemented with the CMUT devices for the application of in vivo ultrasound neuromodulation [42]. These systems offer a greater level of versatility to the current neuromodulation in vivo experiments by allowing behaviors studies on various characteristics such as cognition, social behavior, and sleep.


With the convergence of ultrasound technology and neuroscience, new neurotools are actively being developed for more versatile in vitro and in vivo experiments. MEMS-based devices such as PMUTs and CMUTs are excellent candidates for investigating the mechanisms, effects, and safety of ultrasound neuromodulation because of the light and compact structure and multifunctional capabilities. Since these developments are relatively new, we expect further improvements and advancement with regards to MR compatibility, operational reliability, biological safety, and translatability to clinical applications.


This research was supported by the Brain Research Program through the National Research Foundation of Korea (NRF) funded by the Ministry of Science and ICT (No. 2016M3C7A1904343) and by the National Research Foundation of Korea (NRF) grant funded by the Korea government (MSIT) (No. 2019R1A2C2002084).


The authors have no potential conflicts of interest to disclose.

Author Contributions

Conceptualization: Hyunjoo Jenny Lee. Data curation: Yehhyun Jo. Formal analysis: Chaerin Oh. Funding acquisition: Hyunjoo Jenny Lee. Investigation: Chaerin Oh and Yehhyun Jo. Methodology: Yehhyun Jo. Project administration: Hyunjoo Jenny Lee. Supervision: Hyunjoo Jenny Lee. Validation: Chaerin Oh. Writing—original draft: Yehhyun Jo and Chaerin Oh. Writing—review & editing: Hyunjoo Jenny Lee.

Figure 1.
In vitro systems for ultrasound stimulation. A: Schematic diagram of the in vitro system utilizing a commercially available transducer; Reprinted from Ilham. Ultrasonic neuromodulation in vitro at single neuron resolution 2017, with permission of University of Connecticut [31]. B: Scanning electron microscope image of the PMUT array (left) and schematic diagram of the compact overall system (right); Reprinted from Ko et al. 28th IEEE Int Conf Micro Electro Mechan Syst (MEMS) 2015:651-654, with permission of IEEE [35]. PMUT: piezoelectric micromachined ultrasound transducers, PDMS: polydimethylsiloxane, SMA: SubMiniature version A, DIP: dual in-line package, PCB: printed circuit board.
Figure 2.
Schematics and descriptions of three different miniature ultrasound transducers. A: Assembly of miniaturized ultrasound transducer; Reprinted from Li et al. IEEE Trans Biomed Eng 2019;66:217-224, with permission of IEEE [40]. B: Images of capacitive micromachined ultrasound transducers ring array (left) and fully packaged device (right); Reprinted from Kim et al. Brain Stimul 2009;12:251- 255, with permission of Elsevier [39]. C: Images of wearable miniature ultrasound transducer on wooden board (left) and mounted on an anesthetized rat (right); Reprinted from Lee et al. BMC Neurosci 2018;19:57, with permission of Springer [41].
Table 1.
Characteristics of miniaturized transducers
Study Device diameter (mm) Resonant frequency (kHz) Focal length (mm) Spatial resolution (lateral) (mm) Fabrication method Freely-moving system
Li et al. [4040] 5.0 2000 7.0 1.20 Piezoelectric ceramic Possible
Kim et al. [39] 8.1 183 2.3 2.75 MEMS Possible
Lee et al. [41] 16.0 600 10.0 3.00 Piezoelectric ceramic Possible

MEMS: microelectromechanical systems.


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