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Electric Stimulation Therapy

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Most cited protocols related to «Electric Stimulation Therapy»

One commonly used approach to image fluorescently reported neuronal dynamics is 2-photon microscopy30 (link). This technique utilizes low energy near infrared (IR) photons to penetrate highly light-scattering brain tissue up to 600–700 μm below the surface of the brain31 (link). A significant advantage of 2-photon microscopy is the ability to selectively excite fluorophores within a well-defined focal plane, resulting in a spatial resolution capable of resolving cellular activity within precisely defined anatomical sub-regions of neurons, such as dendrites and axonal boutons30 (link). Notably, although this imaging modality provides superior spatial resolution, it requires the head fixation of animals and, in the absence of a microendoscope or optical cannula, 2-photon imaging is limited to superficial layers of the brain32 (link),33 (link). Together, these behavioral and optical limitations greatly reduce the scope of scientific questions that can be examined with 2-photon microscopy.
Implantation of small, lightweight fiber optics above a region of interest, such as with fiber photometry, circumvents optical and behavioral limitations posed by 2-photon microscopy34 (link). However, unlike 2-photon microscopy, fiber photometry lacks cellular level resolution and provides only aggregate activity within the field of view (i.e., bulk changes in fluorescent signal)22 . Thus, this method is better suited for monitoring dynamic activity within neural projection fields35 (link). In addition to limitations in optical resolution, fiber photometry requires the test subject to be secured to a rigid fiber optic bundle, which can be difficult for small mammals, such as mice, to maneuver34 (link). Thus, while fiber photometry increases the depth in which neural activity can be monitored, it presents significant limitations in optical resolution, restricts the natural behavioral repertoire of an animal, and limits the animal models that can be optimally utilized.
Large-scale recordings of neural activity within freely behaving mammals36 (link) can also be conducted with techniques that do not rely on the use of fluorescence indicators of neural activity, such as in vivo electrophysiological recordings2 (link). Importantly, compared to in vivo Ca2+ imaging, electrophysiology provides superior temporal resolution, allowing for more accurate spike timing estimations17 (link),37 (link),38 (link) as well as the correlation of neural activity with precisely defined temporal events. In addition, in vivo electrophysiology can be combined with optogenetic perturbations of genetically defined neuronal populations to permit the identification (although not unequivocally) and manipulation of defined neuronal populations39 –41 (link). The ability to monitor and subsequently manipulate a circuit is particularly important to the study of brain function as it allows the causal role of identified computations to be elucidated. Thus, compared to freely behaving in vivo optical imaging methods, in vivo electrophysiology methods offer advantages in the domain of temporal resolution as well as technological integration. One notable limitation of this method is that the spatial location of monitored cells cannot be visualized, making it difficult to assert that an identified cell is similar or unique across recording sessions1 (link). Moreover, because in vivo electrophysiology relies on waveform shapes to differentiate individual cells from each other, it can be challenging to detect cells with sparse firing patterns or that are located within densely populated networks. Finally, the number of cells that can be detected with in vivo electrophysiology methods is often far less than the number of cells that can be monitored with the optical imaging methods described in this protocol29 (link),42 (link). Taken together, these limitations in cell identification and statistical power pose a significant disadvantage for studies that require chronic monitoring of neural activity.
Publication 2016
Animal Model Animals Axon Body Regions Brain Cannula Cells Dendrites Dietary Fiber Electric Stimulation Therapy Fibrosis Fluorescence Head Light Mammals Microscopy Mus Muscle Rigidity Nervousness Neurons Optogenetics Ovum Implantation Photometry Population Group Tissues
Cellular [Ca2+]i and electrophysiological methods are described in the Online Supplement and were used to tune our model and for validation. Table 1 shows key changes made in our new human atrial model vs. our ventricular myocyte model, 12 (link) to account for ionic remodeling in cAF, and to simulate the effects of β-adrenergic and cholinergic stimulation. Further details are in Online Supplement, including formulation of IKur block by AVE0118.
Model differential equations were implemented in Matlab (Mathworks Inc., Natick, MA, USA) and solved numerically using a variable order solver (ode15s). APDs were obtained after pacing digital cells at indicated frequencies at steady-state. APD was measured as the interval between AP upstroke and 90% repolarization level (APD90).
Publication 2011
Adrenergic Effect AVE 0118 Cells Cholinergic Agents Dietary Supplements Electric Stimulation Therapy Heart Atrium Heart Ventricle Homo sapiens Ions Muscle Cells
Mice were anesthetized with isoflurane and held in place with a head post cemented to the skull. All incisions were infiltrated with lido-caine. A small craniotomy was made over barrel cortex approximately 200 μm anterior to the virus injection site. Extracellular single-unit and LFP recordings were made with tetrodes or stereotrodes. Intracellular recordings were conducted by whole-cell in vivo recording in current clamp mode. Stimulus control and data acquisition was performed using software custom-written in LabView (National Instruments) and Matlab (The Mathworks). Further electrophysiology methods and a description of the reversal potential calculation are given in Supplementary Methods.
Light stimulation was generated by a 473 nm laser (Shanghai Dream Lasers) controlled by a Grass stimulator (Grass Technologies) or computer. Light pulses were given via a 200-μm diameter, unjacketed optical fibre (Ocean Optics) positioned at the cortical surface 75–200 μm from the recording electrodes. For experiments using the broad range of light-stimulation frequencies (8, 16, 24, 32, 40, 48, 80, 100 and 200 Hz), we stimulated in bouts of 3 s of 1-ms pulses at 46 mW mm−2 at each frequency in a random order. In a subset of these experiments, we stimulated at 31, 46 and 68 mW mm−2.
Vibrissae were stimulated by computer-controlled movements of piezoelectric wafers (Piezo Systems). Vibrissa stimulations were single high-velocity deflections in the dorsal and then in the ventral direction (~6 ms duration). In most cases, adjacent vibrissae that yielded indistinguishable amplitude responses during hand mapping were deflected simultaneously. Vibrissa stimulations evoked layer 4 RS spike responses with an onset latency of 9.1 ± 0.08 ms. For RS cell response suppression experiments, light pulses were given on randomly interleaved trials. For gamma-phase experiments, we gave a series of trials each consisting of a 1-s series of 1-ms light pulses at 40 Hz, with a single whisker deflection after the thirtieth light pulse. The precise timing of the whisker deflection relative to the light pulses was varied across five phase points. Each of the five phase points was included in a random order across a minimum of 250 total trials.
Unit and LFP analysis used software custom-written in Igor Pro (Wavemetrics). For each stimulation frequency, we measured the relative power in an 8-Hz band centred on that frequency. For each recording site, we measured power from 5–10 LFP traces under each condition. Example power spectra are averages of the power spectra from 5–10 traces of unfiltered LFPs from individual experiments. Relative power was calculated by measuring the ratio of power within the band of interest to total power in the power spectrum of the unfiltered LFP. We also measured the power ratio: Plight/Pbaseline, where Plight is the relative power in a frequency band in the presence of light stimulation and Pbaseline is the power in that band in the absence of light stimulation. All numbers are given as mean ± s.e.m., except where otherwise noted.
Publication 2009
ARID1A protein, human Cells Cortex, Cerebral Craniotomy Cranium Dreams Electric Stimulation Therapy Eye Gamma Rays Head Isoflurane Light Movement Mus Photic Stimulation Poaceae Protoplasm Pulse Rate Pulses Vibrissae Virus
The final strength of tDCS that we want to emphasize is that it is easily combined with other methods used to measure neural activity. This is because the effects of tDCS last for several hours, allowing sufficient signal averaging of the changed brain. We will briefly describe a couple of examples in which tDCS was combined with functional MRI and recordings of participants’ EEG and the averaged ERPs.
The downside of the long-lasting effects of tDCS is that this type of stimulation results in essentially static changes in the brain. These are slowly evolving effects, and a skeptic might argue that tDCS provides essentially no temporal resolution. However, when it comes to combining tDCS with fMRI, this can be made to be an advantage. For example, with fMRI it is possible to measure far field effects across the entire brain. When this has been done, researchers have shown that tDCS stimulation can result in changes across a large brain-wide network. Chib, Yun, Takahashi and Shimojo (2013) (link) provide a nice example of this combination of methods. They showed that stimulation of prefrontal cortex (i.e., anode at Fp1 and cathode at F3) resulted in signal change in the ventral medial cortex of participants viewing face stimuli. That is, this experiment showed that stimulation of relatively remote brain areas can result in far field activations that are not in the current path. This is a natural combination of methods because fMRI excels in measuring whole brain activity to understand the potentially board networks influenced by the tDCS that is long lasting enough to perform the necessary scans.
We might expect tDCS to have poor temporal resolution due to the sluggish nature of this causal manipulation. However, there is evidence from EEG and ERP studies that tDCS can have surprisingly specific effects at certain points in time during the flow of information processing (Reinhart and Woodman, 2015b (link)). For example, several recent studies showed that tDCS at different locations on the head changed one specific ERP component (lasting approximately 100 ms) while leaving temporally adjacent components unchanged. One such study showed that tDCS stimulation applied to parietal cortex changed the N1 component elicited by visual stimuli, but not P1 or N2pc measured just tens of milliseconds on either side of the N1 (Reinhart and Woodman, 2015e (link)). Another study showed that medial-frontal stimulation changed the error-related negativity (ERN) measured in the first 150 ms following a response, but no other components during the entire flow of information processing in a visual discrimination task (Reinhart and Woodman, 2014 (link)). This means that the temporal precision of tDCS may be better than we think, changing activity during just one 100–150 ms period and not any other periods of processing during a trial lasing 1 second or more. Thus, combining the slow after effects of tDCS with a high temporal resolution technique like electrophysiology can demonstrate that tDCS can have effects with high temporal specificity.
Publication 2017
Brain Cortex, Cerebral Discrimination, Psychology Electric Stimulation Therapy Evoked Potentials Face fMRI Head Nervousness Parietal Lobe Prefrontal Cortex Radionuclide Imaging Toxic Epidermal Necrolysis Transcranial Direct Current Stimulation
The modeling platform of this study is our recently developed human atrial myocyte model that enables the simulation of emergent spatiotemporal characteristics of intracellular Ca2+ dynamics [13] (link). Methods for simulation of tissue-level electrophysiology and its analysis are presented in the Supporting Information and are detailed in [35] (link). Contrary to most previous in silico studies of cAF, we performed a broad literature search on cellular remodeling to define the average remodeled parameter values (Figure 1A) instead of using a single in vitro data set or small subset. We have included those remodeling targets that have been established in more than one study. Full sets of referenced human data are shown in Supporting Information (Tables S2S4).
The modifications of existing model components, as well as the simulation protocols are described in detail in the Supporting Information. Briefly, we reformulated the ICaL to increase the contribution Ca2+-dependent vs. voltage-dependent inactivation of the current, and decreased the time constants based on recent in vitro data [36] (link), Supporting Information Figure S1. Parameters of the SERCA pump have been modified according to a previously developed scheme [37] (link), [38] (link) to enable the representation of changed expression of phospholamban (PLB) and sarcolipin (SLN) in cAF.
In our analysis of cAF-related cellular remodeling, we use the following three biomarkers:
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Publication 2014
Biological Markers Cells Electric Stimulation Therapy Heart Atrium Homo sapiens Muscle Cells phospholamban Protoplasm sarcolipin Tissues

Most recents protocols related to «Electric Stimulation Therapy»

The exclusion criteria were as follows: (1) pregnancy or planning to conceive in the next 6 months; (2) a history of allergy to solifenacin; (3) cardiac problems (e.g., heart failure); (4) a history of surgery to treat urinary incontinence or other surgeries of the urinary system; (5) stress urinary incontinence or prostatic hyperplasia; (6) diabetes; (7) Parkinson’s disease; (8) a history of anticholinergic drug therapy for OAB in the last month; (9) a history of electrotherapy of the lower limbs and the back; (10) performing the pelvic floor muscle exercise in the last month; and (11) having a heart pacemaker and/or leg prosthesis.
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Publication 2023
Allergic Reaction Anticholinergic Agents Benign Prostatic Hyperplasia Diabetes Mellitus Electric Stimulation Therapy Heart Heart Failure Leg Prostheses Lower Extremity Muscle Tissue Operative Surgical Procedures Pacemaker, Artificial Cardiac Pelvic Diaphragm Pharmacotherapy Pregnancy Solifenacin Therapeutics Urinary Incontinence Urinary Stress Incontinence Urologic Surgical Procedures
Before the initial testing, each patient was given a screening form for a primary health evaluation that also contained demographic details such as age, gender, education level, occupation, and body mass index. The patients were asked to fill out QBPDS-H, the Hindi version of the Roland-Morris Disability Questionnaire (H-RMDQ), and the Visual Analogue Scale (VAS) at the first visit. All participants received an individually tailored similar multimodal physical therapy rehabilitation program of electrotherapy (Interferential current), thermotherapy (moist heat), and muscular motor training exercises targeting trunk core muscles stabilization and strength, along with stretching, for one hour. However, the treatment given and the gap between the assessments helped only as a construct for achieving a change [24 (link),25 (link)]. It was neither a part of this study’s interests, nor was it considered. The follow-up evaluation was performed after eight weeks of the rehabilitation program, including QBPDS-H, H-RMDQ, VAS, and the H-PGIC scale. Based on their rating on the Hindi version of the Patient’s Global Impression of Change scale (H-PGIC), the patients were dichotomized into two subgroups, and ratings of 1–4 were categorized as “clinically unimproved”, while ratings of 5–7 were categorized as “clinically improved” [26 (link)]. The changes in QBPDS-H scores (∆QBPDS-H) were calculated for each subgroup as the differences in scores between the baseline and at the end of the eighth week. A positive score indicated functional ability improvement. The percentage change in scores was calculated by dividing the change by the original value and multiplying it by a hundred ((∆QBPDS-H/QBPDS-H baseline) × 100). Overall changes experienced in their CLBP status were also acquired using the H-PGIC scale, which was achieved by observing how significant differences occurred in their pain-related disability in activities of daily living from the baseline and after eight weeks.
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Publication 2023
Combined Modality Therapy Disabled Persons Electric Stimulation Therapy Gender Index, Body Mass Induced Hyperthermia Muscle Tissue Pain Patients Physical Examination Rehabilitation Screening Visual Analog Pain Scale
Family physicians had to indicate which rehabilitation treatments they would prescribe (physiotherapy referral, advice and education, home exercise program or other). Physiotherapists also had to indicate rehabilitation interventions they would provide, but possible answers detailed more specific interventions offered by physiotherapists. For each proposed rehabilitation intervention (education, active mobility exercises, passive mobility exercises, strengthening exercises, motor control exercises, manual therapy, thermotherapy, electrotherapy), physiotherapists had to indicate the priority of the intervention on a 6-point scale, 0 representing an intervention not to use and 5 representing an intervention that is extremely important to use.
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Publication 2023
Electric Stimulation Therapy Induced Hyperthermia Physical Therapist Physicians, Family Range of Motion, Articular Rehabilitation Therapy, Physical
By centralizing an enduring data archive, we allow the broader neuroscience research community to access and thereby analyze the data from various BRAIN Initiative projects. All information pertaining to data acquisition, quality control, pre-processing, and analyses are captured and retained, providing a comprehensive history and provenance to the data. Data provenance includes timestamped raw data with timeline noting data upload revisions and versions, preprocessed data (provided by data collectors or produced by users within associated analytic tools), saved cohorts, and analysis workflows saved by users. We have pioneered innovative standardization/co-registration references, fully supported by novel image and electrophysiology processing methods, to extract candidate biomarkers from the diverse data to address the specific projects’ goals. Spatial descriptions and co-registrations of regions of interest are made according to detailed coordinate/imaging maps of the brain, co-registered to sensors, such as implanted or scalp electrodes, when possible. With the aid of the LONI Pipeline22 (link),23 that is integrated into DABI, much of this work is automated. Not only is a well-curated and standardized multi-modal data set facilitating the development of models of various diseases, but it is also ensuring that such models are statistically significant and validated.
Data trends and correlations can then be calculated in DABI, without downloading raw data. Integrated software and analytics include image visualization, quality control24 (link), LONI Pipeline22 (link),23 , Jupyter25 , R Analysis and Visualization of intracranial EEG Data (RAVE)26 , and a variety of statistical tests. RAVE allows users to visualize intracranial EEG (iEEG) recordings and apply various dimensionality reduction and statistical methods to analyze these large iEEG datasets27 ,28 (link). Investigators maintain complete ownership and control of their data. Unaffiliated users must be granted access from PIs to download raw data or conduct analysis using DABI’s built-in analytics.
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Publication 2023
Biological Markers Brain Brain Mapping DABI Developmental Disabilities Electric Stimulation Therapy Electrocorticography Scalp TimeLine
The TBI group also received an integrative pediatric rehabilitation program. However, unlike the FNSD group, treatment was highly influenced by the child’s cognitive function.
Psychological therapy sessions with adolescents and with their parents focused on: (1) the medical traumatic event; (2) the expected outcomes following the injury and; (3) psychoeducation and emotional support for the parents. Psychological therapy was provided once to twice a week.
Physical therapy: children with TBI present numerous physical impairments, such as altered muscle tone, proprioception, and balance. Such impairments commonly limit the ability to independently perform age-appropriate activities and instrumental activities of daily living [36 (link)], as well as participation. Therefore, physical therapy should commence as soon as possible, once the child is clinically stable [36 (link),37 (link)]. Physical therapy commonly involves the following types of therapy: preventing secondary complications (e.g., contractures and weakness), sensory stimulation, fitness, and functional training (e.g., sit-to-stand training and gait training [38 (link)]. Physical therapy was conducted at least twice a day, six days a week. Each physical therapy session lasted 45 minutes. Both individual and group therapy were provided. Physiotherapists commonly conducted functional treatments, such as gait education and bed mobility. Physical agents and other modalities (e.g., hydrotherapy, electrotherapy, and cryotherapy) were also used.
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Publication 2023
Adolescent Asthenia Child Cognition Contracture Cryotherapy Electric Stimulation Therapy Emotions Group Therapy Hydrotherapy Injuries Muscle Tonus Parent Physical Examination Physical Therapist Proprioception Range of Motion, Articular Rehabilitation Therapy, Physical

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