Here, we present a protocol for using a high-throughput system that enables the monitoring and quantification of the neuromodulatory effects of focused ultrasound on human-induced pluripotent stem cell (HiPSC) neurons.
The neuromodulatory effects of focused ultrasound (FUS) have been demonstrated in animal models, and FUS has been used successfully to treat movement and psychiatric disorders in humans. However, despite the success of FUS, the mechanism underlying its effects on neurons remains poorly understood, making treatment optimization by tuning FUS parameters difficult. To address this gap in knowledge, we studied human neurons in vitro using neurons cultured from human-induced pluripotent stem cells (HiPSCs). Using HiPSCs allows for the study of human-specific neuronal behaviors in both physiologic and pathologic states. This report presents a protocol for using a high-throughput system that enables the monitoring and quantification of the neuromodulatory effects of FUS on HiPSC neurons. By varying the FUS parameters and manipulating the HiPSC neurons through pharmaceutical and genetic modifications, researchers can evaluate the neural responses and elucidate the neuro-modulatory effects of FUS on HiPSC neurons. This research could have significant implications for the development of safe and effective FUS-based therapies for a range of neurological and psychiatric disorders.
Focused ultrasound (FUS) is a promising neuromodulation modality that enables noninvasive stimulation at centimeter-level depths with sub-millimeter resolution1,2,3. Despite these strengths, the clinical impact of FUS is limited, in part due to a lack of knowledge regarding its mechanism of action. Without a solid theoretical foundation, researchers and clinicians face difficulties in tailoring the therapy to meet the specific needs of individual patients under varying conditions. A prominent theory proposed by Yoo et al.4 suggests that mechanosensitive ion channels are responsible for neuron activation. However, this theory fails to explain FUS activation in human brain neurons, which lack these channels5. This ambiguity limits the utilization of FUS in the clinic, as it precludes the tuning of FUS parameters to optimize treatment outcomes.
Prior related studies have employed a range of approaches to investigate the physiological mechanisms underpinning FUS and to determine the optimal stimulation parameters. A crucial step in this process involves monitoring neuronal responses as feedback, which can be achieved through methods involving ion-gate monitoring, such as calcium ion imaging4, optical imaging1, and ex vivo electrophysiological recording (e.g., electromyography6 or skin-nerve electrophysiology7). However, most of these studies use non-human neurons or in vivo approaches, which can introduce additional variances due to sub-optimal controls. In contrast, using electrodes to measure neuronal signals in in vitro human-induced pluripotent stem cell (HiPSC) neurons offers more sensitive measurements and greater control over the experimental environment. In this work, an in vitro system has been developed using micro-electrode arrays (MEAs) to measure the electrical responses of HiPSC neurons following FUS stimulation, as shown in Figure 1. This system empowers researchers in the community to monitor neuronal responses when varying the ultrasound parameters (e.g., frequency, burst length, intensity). Additionally, this system enables a high level of control of the neuronal sensitivity to physical stimuli (e.g., temperature, pressure, and cavitation)8,9, as the neurons' ion channel functionality can be manipulated genetically and pharmaceutically (e.g., using gadolinium to inhibit ion channels)10,11,12. This molecular-level control may help to elucidate the mechanisms behind the neuromodulatory effects of FUS.
1. Preparation of materials
2. Connection and setup of the peripherals
3. Stimulation and neuronal signal acquisition
4. Data processing and analysis
5. Multi-well MEA plate cleaning and reuse
In summary, we present a protocol that enables in vitro FUS neuromodulation monitoring using neurons cultured from HiPSCs. The overall system platform to stimulate HiPSC-induced neurons and record the corresponding electrical responses for analysis is outlined in Figure 1. This study focuses on the FUS stimulation of neurons and recording the electrical responses in an MEA system, as shown in Figure 2. The peripheral components of the FUS and MEA systems and their connections are illustrated in Figure 3.
The characterization of the focal point is performed prior to the neuronal experiments to ensure the bottom of the well is fully covered by the FUS focal point. The visualization of the focal spot on thermochromic sheets, as shown in Figure 4, should be performed to evaluate the FUS system. Following focal spot characterization, the post-processing steps, including filtering, thresholding, and calculating the firing rate, should be performed, and these are summarized in Figure 5 and Figure 6. These steps are essential to retrieve useful signals by filtering noise from the environment and, thus, to gain insight into the neuronal activity changes caused by FUS. The Raster plots in Figure 6A–B show the detected spikes in each channel. As the entire bottom of the well is within the focal point of the FUS transducer, it is expected that the FUS should alter the firing rate across all the electrodes. This change in firing rate is visualized in the firing rate plot shown in Figure 6C, which shows that the chosen stimulation parameters resulted in an increase in the neuronal firing rate. Specifically, the pre-FUS (i.e., baseline) firing rate was 140 Hz ± 116.7 Hz, while the post-FUS firing rate was 786 Hz ± 419.4 Hz with continuous-wave FUS. Additionally, Figure 6C shows how altering the FUS parameters (e.g., using pulsed-wave FUS instead of continuous-wave) can alter the magnitude of change in the firing rate, as well as change the amount of time before the neurons return to their baseline state. Low-intensity focused ultrasound (LIFU) does not cause significant warming of cultures, especially when compared to high-intensity focused ultrasound, which intends to achieve thermal lesion. The lack of clinically impactful temperature change is supported by theoretical calculations and simulations (Supplementary Figure 2). Even in extreme cases of the experimental FUS parameters listed in Table 1, only a minimal increase in temperature could be observed of approximately 0.04 °C.
The use of a firing rate plot enables the quantification of the neuromodulatory effects of FUS and can be used to differentiate between excitatory and inhibitory responses. A significant advantage of the multi-well MEA plate is that it can be reused multiple times to study varying neuronal states and stimulation parameters in a high-throughput manner.
Figure 1: Overview of the in vitro platform for the focused ultrasound (FUS) neuromodulation of neurons in a well and the measurement of their neuronal activity using a microelectrode array. Each electrode (red, green, and blue lines) records from a population of neurons within a single well. A processing pipeline is implemented to convert the raw neuronal electrical recordings into the detection of neuronal firing patterns. Please click here to view a larger version of this figure.
Figure 2: FUS neuromodulation with a multi-well microelectrode array (MEA). (A) Schematic of the setup for FUS neuromodulation with a multi-well MEA. The acoustic waves generated by the FUS transducer propagate through an FUS cone filled with degassed water and are coupled using ultrasound gel. The parafilm is secured to the well using a rubber band to prevent contamination. The MEA plate sends electrical recordings from the neurons to the MEA system. (B) A photograph of the FUS transducer on the multi-well plate contained in the MEA system. Please click here to view a larger version of this figure.
Figure 3: In vitro platform setup. (A) The front of the in vitro platform setup. The transducer power output (TPO; left) is used to program the FUS parameters. The MEA system (right) records electrical activity from the neurons in the well plate, which are neuromodulated by the FUS transducer. (B) The back of the in vitro platform setup with connections from the matching network (1) to the TPO and (2) to the transducer. (3) The connection from the MEA system to the TPO synchronizes the data acquisition. (4) The connection from the MEA system to the computer for data transfer. (5) The power connection to the MEA system. (6) The power connection to the FUS system. (7) The sonication button. Please click here to view a larger version of this figure.
Figure 4: Characterization of the FUS transducer. (A) A pressure map of the focal spot using the FUS parameters detailed in Table 1 measured by the AMPLITUDE system15. (B) Pre- and post-sonication of a thermochromic sheet placed at the bottom of a well using the experimental setup shown in Figure 3. The thermochromic sheet changes color in response to temperature changes, which provides a visual validation of successful stimulation at the location of the neurons. The maximal spatial-peak pulse average intensity (ISPPA) of 30 W/cm2 and continuous sonication of 3 min were adjusted to change the local temperature drastically for the better visualization of such a focal point. Please click here to view a larger version of this figure.
Figure 5: Processing pipeline. Step 1: Raw electrical recordings are captured from N = 16 channels. The future steps show the process using channel 16 (outlined in red). Step 2: For each channel, a Butterworth bandpass filter (5 Hz to 3 kHz bandpass) is applied, followed by a Gaussian filter (σ = 3). A threshold is set as five times the standard deviation of the signal within a 2 s window centered at the start of the sonication. Step 3: Signals above or below the threshold are characterized as spikes. Please click here to view a larger version of this figure.
Figure 6: Raster and firing rate plots. (A) Raster plot of the detected spikes at each channel as a function of the sonication time. The time of FUS stimulation is annotated using a red line. (B) Raster plot of neurons under different FUS settings with continuous FUS for comparison. (C) The firing rate was calculated using a 50 ms sliding window. The mean firing rates pre- and post FUS neuromodulations were 140 Hz and 786 Hz, respectively. With pulsed FUS, the mean firing rates were 230 Hz and 540 Hz. A shorter activation and less rate change were observed to be induced by this set of varying FUS stimulation. The process for calculating the firing rate is detailed in Supplementary Figure 1. Please click here to view a larger version of this figure.
Parameter | Value |
Max Power/Ch. | 1.200 W |
Pactual | 0.749 W/channel. |
ISPPA | 10.79 W/cm2 |
ISPTA | 0.05 W/cm2 |
Burst Length | 0.100 ms |
Frequency | 250.00 kHz |
Focus | 39.800 mm |
Period | 20.000 ms |
Timer | 60.000 s |
Table 1: Focused ultrasound (FUS) parameters set on the TPO for the study presented in Figure 4.
Supplementary Figure 1: Processing from the Raster plot to the firing rate. Step 1: Count the spikes among all the channels to obtain the count number within a given sliding window. Note: Here, a larger sliding window (set to 0.1 s) was chosen for better illustration. Step 2: Convert the spikes per window length to spikes per second (e.g., here, multiply the counts by 10 to convert to hertz [Hz], and then divide by 1,000 to obtain the value in kilohertz [kHz]). Step 3: The firing rate curve acquired as a result. An open-source toolkit, along with sampled data, is available on GitHub (https://github.com/Rxliang/FUSNeuromod). Please click here to download this File.
Supplementary Figure 2: K-wave simulation result temperature profile of LIFU16. Based on the acoustic intensity map shown in Figure 4, the K-wave simulation result suggests a maximal temperature increase of 0.04 °C within the center region of the focal zone (radius: 2 mm) using the extreme case of the experimental FUS parameters listed in Table 1. Please click here to download this File.
This manuscript describes a novel method that can be used to record neuronal activity in HiPSCs during FUS neuromodulation. This protocol is generalizable to different FUS transducers and MEA systems. To replicate the results observed with the described protocol, the researcher should ensure that the focal point of the transducer is greater than the area of the bottom of the MEA well. Furthermore, if different neuronal cell lines are used, the filter parameters must be tuned to the expected frequency response for the cells within the well. If representative results cannot be achieved, one should consider modifying the aforementioned parameters (e.g., the burst length, intensity, duty cycle, etc.).
Though this work demonstrated an increase in the firing rate following FUS stimulation, more data must be collected to demonstrate the repeatability of this finding before any conclusions are drawn. This protocol inherits the limitations of MEA systems, which typically have weaknesses stemming from the direct microelectrode current signal recording. Though direct contact with the neuron provides better sensitivity, it may alter the cell and affect the measurement accuracy. Furthermore, due to the small size of the wells, our system does not include peripheral tissue, which may also play a role in neuromodulation17. This may limit the applicability of conclusions drawn from this setup to in vivo environments. To study more complex network responses, a higher-channel density MEA system must be designed to improve its sensitivity18. Several future directions for this proposed system have been identified, including using a 3D gantry to hold the transducer and ensure accurate placement19. Additional improvements could be made regarding the post-processing algorithm, including utilizing a spiking sorting algorithm20 to classify individual neurons. This process would be beneficial for disentangling the responses of multi-unit neurons in future studies on the mechanisms of FUS. Most importantly, it is essential to incorporate additional modalities of stimulation, such as chemical, electrical, and optical stimuli, to elucidate the underlying mechanisms. These methods can alter neuronal properties and behaviors, such as by inhibiting specific ion channels15 or modifying the membrane characteristics21. By modulating the main factors within the hypothesized signaling pathway, researchers can identify the contributions of each factor in controlled environments and, ultimately, shed light on the complex interactions at play.
Electrical stimulation22 is one of the most established techniques for neuromodulation, with a long history of successful applications in clinical and research settings. In contrast, FUS and optogenetics23 are relatively new modalities that have gained attention in recent years. The major advantages of FUS are its non-invasiveness and ability to stimulate neurons at depths that may be difficult to reach with other techniques, including electrical stimulation and optogenetics. However, like optogenetics24, FUS has some limitations related to modeling the wave propagation and associated neuronal responses. Capturing the complexity of tissue's heterogeneous acoustic properties in vivo can be challenging, which leads to uncertainties in the pressure field and, consequently, in the neuronal responses. This difficulty in accurately modeling these properties presents a challenge when optimizing the technique for specific real-world applications. The inherent complexities emphasize the importance of in vitro systems like the one in this study, as they enable the direct study of responses under controlled acoustic intensity conditions.
In conclusion, this system provides a high-throughput, in vitro platform for studying the neuro-modulatory effects of FUS on human neurons. With this system, the mechanisms of action of FUS can be explored by measuring the electrical responses from human neurons when exposed to varying levels and types of stimulation in a controlled environment. Therefore, it offers a valuable supplementary tool to the human and animal models commonly used in the field.
The authors have nothing to disclose.
Amir Manbachi and Nitish Thakor acknowledge funding support from the Defense Advanced Research Projects Agency, DARPA, Award Contract: N660012024075. In addition, Amir Manbachi acknowledges funding support from the Johns Hopkins Institute for Clinical and Translational Research (ICTR)'s Clinical Research Scholars Program (KL2), administered by the National Center for Advancing Translational Sciences (NCATS), National Institutes of Health (NIH). Nitish Thakor acknowledges funding support from the National Institutes of Health (NIH): R01 HL139158-01A1 and R01 HL071568-15.
MEA System | Axion Biosystem Inc. | Maestro Edge | Sampling Rate: 11500 Hz |
MEA Plate | Axion Biosystem Inc. | CytoView MEA | Electrode and Well: 16 electrodes in 24 wells |
Well plate Interface | Amcor Inc. | Parafilm PM996; P7793 | Thickness: 127 µm |
CO2 Tank and Regulator for culture | AirGas Inc./ Harris Inc. | 9296NC | Concentration: 5% |
Culture Media | ThermoFisher Inc. | Laminin; 23017-015 | Concentration: 1 µg/mL |
HiPSC Neurons | Peprotech | CIPS and GM01582 Derived; 450-10 | Concentration: 10 ng/mL (Refer Taga et al [2021]13) |
Transducer | Sonic Concepts Inc. | CTX250; 008 | Center Frequency: 250 kHz |
Matching Network | Sonic Concepts Inc. | CTX250; NFS102v2 | Impedance: 50 Ω |
Transducer Power Output (TPO) | Sonic Concepts Inc. | Version 4.1; 020 | Frequency: From 250 kHz to 2.5 MHz |
Membrane | McMaster Inc. | Silicone Rubber; 5542N115 | Thickness: 0.0127 cm |
Coupling Gel | Parker Laboratory Inc. | Aquasonic 100; B08DDWG GXB | Viscosity: 130,000–185,000 cops |
Connection to Probe holder | McMaster Inc. | Steal Threaded Rod; 90322A661 | Length: 1–1/2" Long |
Centrifuge | ThermoFisher Inc. | Sorvall Legend X1R; 75004261 | Max acceleration: 10–25,830 x g |
Hydrophone | Sonic Concepts Inc. | Y-104; 009 | Range: 50 kHz–1.9 MHz |
Water Tank | Sonic Concepts Inc. | WT | Size: 30 cm x 30 cm x 30 cm |
Water Conditioning Unit | Sonic Concepts Inc. | WCU; SN006 | Flow Velocity: 50 mL/s maximum |
Oscilloscope | Rohde-Schwarz Inc. | RTC1002 | Sampling rate: Up to 50 MHz |
Stage | Sonic Concepts Inc. | MicroStage; 2 | Accuracy: 1 µm |
Thermochromic sheet | TIPTEMP Inc. | Liquid Crystal Sheet; TLCSEN337 | Range: 22–24 °C |
Computer | Microsoft Surface | Surface Pro | CPU i5 1035G4: 3.7 GHz |
Data Transfer Software | Mathworks Inc. | MATLAB | Version 2021b |
Processing Software | Python Software Foundation | Python | Version 3.7.10 |