Log In Sign up
The largest database of trusted experimental protocols
> Procedures > Therapeutic or Preventive Procedure > ECHO protocol

ECHO protocol

The ECHO protocol is a powerful optimization technique that enhances the performance of the ECHO (Efficient Channel Hopping) wireless communication protocol.
PubCompare.ai's AI-driven platform helps researchers effortlessly locate and compare ECHO protocols from literature, preprints, and patents, enabling them to identify the best protocols and products for their research needs.
This cutting-edge tool provides insightful comparisons and elevates research by leveraging expertize in ECHO protocol optimization.

Most cited protocols related to «ECHO protocol»

1
Calculating Relative Efficiency in CASL
Cited 174 times
All image data were saved as raw echo intensities and reconstructed offline with custom software. Partial Fourier raw data was acquired at lines –m ≤ u ≤ N/2 (m = 6, N= 64). The low frequency phase map of each coil was estimated from the Fourier transformation of the image generated by Hanning filtering the center portion of the raw data at lines –m ≤ u ≤ m. The final image was combined from each coil image, weighted by the conjugate of the corresponding low resolution phase map. A Region of interest (ROI) for each subject was defined to contain the entire brain.
For the first study, the relative combined inversion efficiency was defined as the ratio of the PCASL average difference signal when control and label are set below the brain to the average CASL difference signal after compensating for the duty cycle difference (dividing the CASL difference signal by dcycle). dcycle is the duty cycle of continuous ASL, which is 53.33% in our study. Previous simulations of adiabatic fast passage demonstrate that the labeling efficiency may not have a linear relationship with the RF duty cycle in the pulsed-form CASL(32 (link)). Simulation was performed to calculate the mean labeling efficiency for the laminar flow across the different time when spin passes through the labeling plane. The simulation result shows that the relative efficiency is within 2% difference with the RF duty cycle. This linearity between the RF duty cycle and labeling efficiency is likely valid because of the long pulse period (375 ms) used in the CASL sequence. This improvement with longer labeling blocks (A pulse period of 100 ms was better approximated by a linear relationship than a pulse period of 20 ms) was suggested in previously reported simulations (32 (link)). The relative efficiency loss of the control pulse was defined as the ratio of the PCASL average difference signal when the control is set below the brain compared with above the brain to the average CASL difference signal after compensating for the duty cycle difference. Because of the very low SNR in the average difference signal between controls in PCASL, we used the low-resolution phase map from the average difference signal between control and label when applied below the brain to phase correct the images from each coil. The relative systematic error between control and label pulses was defined as the ratio of the average PCASL difference signal between control and label when applied above the brain to the average CASL difference signal after compensating for the duty cycle difference. The relative efficiency of labeling pulse was defined as the ratio of the PCASL average difference signal when the label is set below the brain compared with above the brain to the average CASL difference signal after compensating for the duty cycle difference. We used low-resolution phase maps to correct the phase of the image from each coil as in the relative efficiency calculation of control pulse.
For the second study the relative combined efficiency described for the first study was employed. For the third study, frequency-dependent off-resonance saturation effects were analyzed by averaging the difference images (between the control and label images) across the phase direction.
Dai W., Garcia D., de Bazelaire C, & Alsop D.C. (2008). Continuous Flow Driven Inversion for Arterial Spin Labeling Using Pulsed Radiofrequency and Gradient Fields. Magnetic resonance in medicine : official journal of the Society of Magnetic Resonance in Medicine / Society of Magnetic Resonance in Medicine, 60(6), 1488-1497.
Publication 2008
Brain ECHO protocol Inversion, Chromosome Microtubule-Associated Proteins Pulse Rate Pulses Spin Labels Vibration
2
GABA-Edited MRS in Healthy Adults
Cited 172 times
To demonstrate the utility of the Gannet software, GABA-edited spectra were acquired in 10 healthy adult volunteers, who provided written informed consent with the approval of the Cardiff University School of Psychology ethics board. In each subject, spectra (repeated four times) were acquired for each of three brain regions: occipital (OCC; including primary visual cortex); sensorimotor (SM; including primary somatosensory and motor cortex); and dorsolateral prefrontal (DLPF), as shown in Figure 3. Experimental parameters were relatively standard for the field (2 (link)), including: GE Signa HDx 3 Tesla (T) scanner using an eight-channel phased-array head coil for receive; repetition time (TR) 1.8 s; echo time (TE) 68 ms; 332 transients of 4k datapoints sampled at 5 kHz; 16 ms Gaussian editing pulse with 95 Hz bandwidth applied at 1.9 ppm in ON scans and 7.46 ppm in OFF scans in an interleaved manner; voxel size 3 × 3 × 3 cm3; acquisition time 10 min. Data were acquired on a GE Signa HDx 3T scanner; a two-step phase cycle, which was time averaged on the scanner so that each FID in the exported data represented two TRs or a period of 3.6 s. OFF/ON interleaving of editing was performed outside the phase cycle loop, so that lines of the exported data were alternately OFF, ON, etc. The unsuppressed water signals from the same volumes were also acquired for quantification.
As mentioned above these GABA+-edited data contain substantial contributions from macromolecular contaminants, which can be removed by a symmetrical editing scheme (22 (link),23 (link)). To demonstrate the ability of Gannet to model MM-suppressed GABA spectra, data were acquired at a TE of 80 ms (22 (link)) in a single healthy subject with 20 ms editing pulses at 1.9 ppm (ON scans) and 1.5 ppm (OFF scans). Other experimental parameters include: TR 2 s; 2k datapoints sampled at 2 kHz; 3 × 3 × 3 cm3 voxel in a primary sensorimotor region (4 (link)).
Edden R.A., Puts N.A., Harris A.D., Barker P.B, & Evans C.J. (2013). Gannet: A Batch-Processing Tool for the Quantitative Analysis of Gamma-Aminobutyric Acid–Edited MR Spectroscopy Spectra. Journal of magnetic resonance imaging : JMRI, 40(6), 1445-1452.
Publication 2013
Adult Brain ECHO protocol gamma Aminobutyric Acid Head Healthy Volunteers Motor Cortex Pulse Rate Pulses Radionuclide Imaging Striate Cortex Transients
3
CEST Imaging of Glycogen Phantom and Calf Muscle
Cited 171 times
All images were acquired using a whole-body Philips 3T Achieva scanner (Philips Medical System, Best, The Netherlands) equipped with 80 mT/m gradients. RF was transmitted using the body coil and SENSE reception (31 (link)) was employed. A series of consecutive direct saturation and CEST scans were performed using the 8-element knee coil for both the glycogen phantom and in vivo human calf muscle. To minimize leg motion, foam padding was placed between the subject’s lower leg and the knee coil. In all cases, second order shims over the entire muscle on the imaging slice were optimized to minimize B0 field inhomogeneity. Notice that the width of Z-spectra depends on T2 and that the WASSR procedure provides an absolute field frequency map so that there is no need for higher order shimming for the CEST acquisition. Clinical imagers generally employ a prescan to center the bulk water signal of the object/subject, optimize the flip angle and shim the field. Note that no such “prescan” should be made between direct saturation and CEST scans to maintain the same field reference conditions. For both scans, saturation was accomplished using a rectangular RF pulse before the turbo spin echo (TSE) image acquisition, as previously described by Jones et al. (21 (link)).
The power level needed for each saturation experiment depended on the load and was optimized by measuring sets of Z-spectra under these different conditions. For WASSR, the power and pulse lengths were chosen as small as possible to have sufficient direct saturation, while minimizing any MT effects. For CEST, the maximum pulse length allowed for the body coil within the protected clinical software (500 ms) was used and the power was optimized for maximum effect at the phantom and muscle loads. WASSR was obtained at higher frequency resolution than CEST, but over a smaller frequency range as only the direct saturation region needs to be covered. The WASSR range was chosen sufficiently large to validate the simulated results, consequently leading to a larger number of frequencies needed in vivo than for the phantom.
Single-slice glycogen phantom imaging was performed using SENSE factor = 2, TSE factor [number of refocusing pulses] = 34 (two-shots TSE), TR = 3000 ms, TE = 11 ms, matrix = 128 × 122, FOV = 100 × 100 mm2, slice thickness = 5 mm, NSA = 1. Imaging parameters for human calf muscle experiments were identical to those in phantom experiments except for the following: FOV = 160 × 160 mm2. The saturation spectral parameters for WASSR and CEST are indicated in Table 1.
Kim M., Gillen J., Landman B.A., Zhou J, & van Zijl P.C. (2009). WAter Saturation Shift Referencing (WASSR) for chemical exchange saturation transfer experiments. Magnetic resonance in medicine : official journal of the Society of Magnetic Resonance in Medicine / Society of Magnetic Resonance in Medicine, 61(6), 1441-1450.
Publication 2009
Dietary Fiber ECHO protocol Glycogen Homo sapiens Human Body Knee Joint Leg Muscle Tissue Pulse Rate Pulses Radionuclide Imaging SHIMS
4
Robust Spatial Preprocessing for fMRI Data
Cited 148 times
Spatial image preprocessing (distortion correction and image alignment) was carried out using the HCP’s spatial minimal preprocessing pipelines5 (link). This included steps to maximize alignment across image modalities, to minimize distortions relative to the subject’s anatomical space, and to minimize spatial smoothing (blurring) of the data. The data were projected into the 2 mm standard CIFTI grayordinates space, which includes cortical grey matter surface vertices and subcortical grey matter voxels5 (link). This offers substantial improvements in spatial localization over traditional volume-based analyses, enabling more accurate cross-subject and cross-study registrations and avoiding smoothing that mixes signals across differing tissue types or between nearby cortical folds. Additionally, we did minimal smoothing within the CIFTI grayordinates space to avoid mixing across areal borders prior to parcellation.
For cross-subject registration of the cerebral cortex, we used a two-stage process based on the multimodal surface matching (MSM) algorithm14 (link) (see Supplementary Methods 2.1–2.5). An initial ‘gentle’ stage, constrained only by cortical folding patterns (FreeSurfer’s ‘sulc’ measure), was used to obtain approximate geographic alignment without overfitting the registration to folding patterns, which are not strongly correlated with cortical areas in many regions. Previously, we found that more aggressive folding-based registration (either MSM-based or FreeSurfer-based) slightly decreased cross-subject task-fMRI statistics, suggesting that aligning cortical folds too tightly actually reduces alignment of cortical areas14 (link). A second, more aggressive stage used cortical areal features to bring areas into better alignment across subjects while avoiding neurobiologically implausible distortions or overfitting to noise in the data. The areal features used were myelin maps, resting state network maps computed with weighed regression (an improvement over dual regression34 (link) described in the Supplementary Methods 2.3) and resting state visuotopic maps (see Supplementary Methods 4.4). Areal distortion was measured by taking the log base-2 of the ratio of the registered spherical surface tile areas to the original spherical surface tile areas. The mean (across space) of the absolute value of the areal distortion averaged across subjects from both registration stages was 30% less than the standard FreeSurfer folding-based registration and the maximum (across space) of this measure was 54% less. Despite less overall distortion, the areal-feature-based registration delivers substantially more accurate registration of cortical areas than does FreeSurfer folding-based registration as judged by cross-subject task fMRI statistics, an areal feature that was not used to drive the registration14 (link). Because MSM registration preserves topology and is relatively gentle (it does not tear or distort the cortical surface in neurobiologically implausible ways), it is unable to align some cortical areas in some subjects where the areal arrangement differs from the group average (see Supplementary Results and Discussion 1.3–1.4 for more details on atypical areas). Group average registration drift away from the gentle folding-based geographic alignment was removed from the surface registration35 (link) (see Supplementary Methods 2.5) to enable comparisons of this dataset with datasets registered using different areal features (for example, post-mortem cytoarchitecture). Group average registration drift is any consistent effect of the registration during template generation on the mean size, shape, or position of areas on the sphere (as opposed to the desired reductions in cross-subject variation). An obvious example is the 37% increase in average brain volume produced by registration to MNI space4 (link). Uncorrected drifts during surface template generation can cause apparent changes in cortical areal size, shape, and position when comparing across studies.
Resting state fMRI data were denoised for spatially specific temporal artefacts (for example, subject movement, cardiac pulsation, and scanner artefacts) using the ICA+FIX approach, which includes detrending the data and aggressively regressing out 24 movement parameters36 (link),37 (link). We avoided regressing out the ‘global signal’ (mean grey-matter time course) from our data because preliminary analyses showed that this step shifted putative connectivity-based areal boundaries so that they lined up less well with other modalities, likely because of the strong areal specificity of the residual global signal after ICA+FIX clean up. Task fMRI data were temporally filtered using a high pass filter. More details on resting state and task fMRI temporal preprocessing are described in the Supplementary Methods 1.6–1.8. Substantial spatial smoothing was avoided for both datasets, and all images were intensity normalized to account for the receive coil sensitivity field. Artefact maps of large vein effects, fMRI gradient echo signal loss, and surface curvature were computed as described in Supplementary Methods 1.9.
Glasser M.F., Coalson T.S., Robinson E.C., Hacker C.D., Harwell J., Yacoub E., Ugurbil K., Andersson J., Beckmann C.F., Jenkinson M., Smith S.M, & Van Essen D.C. (2016). A multi-modal parcellation of human cerebral cortex. Nature, 536(7615), 171-178.
Publication 2016
Autopsy Brain Cortex, Cerebral ECHO protocol fMRI Gray Matter Heart Histocompatibility Testing Hypersensitivity Microtubule-Associated Proteins Movement Multimodal Imaging Myelin Sheath Tears Veins
5
Multimodal Neuroimaging Protocol for Brain Analysis
Cited 134 times

Protocol full text hidden due to copyright restrictions

Open the protocol to access the free full text link

Publication 2011
Biological Evolution Blood Oxygen Levels Brain ECHO protocol HAVCR2 protein, human Head Neoplasm Metastasis TRIO protein, human Vision

Most recents protocols related to «ECHO protocol»

1
Cardiac Magnetic Resonance Imaging for LV Function
All participants were scheduled to have CMR-LGE examination just before each CPET. CMR-LGE examination involved a 3.0-Tesla Skyra scanner (Siemens Medical Systems, Erlangen, Germany) operating on the VD13 platform with a 32-channel phased-array receiver body coil. Short-axis (contiguous 8-mm-thick slices) and standard long-axis view (2-, 3- and 4-chamber views) cine images were obtained by steady-state free precession (SSFP) cine imaging with the following parameters: repetition time, 45 ms; echo time, 1.4 ms; matrix, 256 × 256; and field of view, 34 to 40 cm. LV geometry as well as functions, including LV end-diastolic volume (LVEDV), LV end-systolic volume (LVESV), resting CO (COrest), LVEF, LV mass, and left ventricle wall motion (LVWMS) were determined using SSFP cine imaging. The lower the LVWMS is, the better the LV contractility [28 (link)].
Quantitative parametric images of myocardial extracellular volume (ECV) fractions were acquired from longitudinal relaxation time (T1) mapping in short-axis slices before (pre) and after (post) contrast medium enhancement. The ECV was estimated by the following equation: ECV=(1-hematocrit)(1T1myopost-1T1myopre)(1T1bloodpost-1(T1bloodpre)
The CMR-LGE system determines the T1 in each myocardial segment. Myocardial fibrosis was estimated with a modified Look-Locker inversion-recovery (MOLLI) sequence [15 (link)] acquired during the end-expiratory phase in the basal, middle and apical LV myocardial segments at short-axes before (T1myo pre) and approximately 15 to 20 min after (T1myo post) a 0.1 mmol/kg intravenous dose of gadolinium-DOTA (gadoterate meglumine, Dotarem, Guerbet S.A., France). The ECV value was further normalized by the blood T1 mapping image before (T1blood pre) and after (T1blood post) enhancement in the corresponding short-axis slices. The basal slice (Base), mid-cavity slice (Middle), and apical slice (Apex) of LV myocardial segments [29 (link)] were drawn along the epicardial and endocardial surfaces on matched pre- and post-contrast MOLLI images to identify the myocardium for ECV analysis.
Hsu C.C., Wang J.S., Shyu Y.C., Fu T.C., Juan Y.H., Yuan S.S., Wang C.H., Yeh C.H., Liao P.C., Wu H.Y, & Hsu P.H. (2023). Hypermethylation of ACADVL is involved in the high-intensity interval training-associated reduction of cardiac fibrosis in heart failure patients. Journal of Translational Medicine, 21, 187.
Full text: Click here
Publication 2023
BLOOD Cardiovascular System Clostridium perfringens epsilon-toxin Dental Caries Diastole Dotarem ECHO protocol Endocardium Epistropheus Exhaling Fibrosis Gadolinium gadolinium 1,4,7,10-tetraazacyclododecane-N,N',N'',N'''-tetraacetate gadoterate meglumine Human Body Inversion, Chromosome Left Ventricles Muscle Contraction Myocardium Sequence Inversion Systole Volumes, Packed Erythrocyte
2
Multiparametric MRI Protocol for Brain Imaging
All MRI examinations were performed using a 3-Tesla MRI system (Discovery MR 750W, GE Medical Systems, Inc. Chicago, IL, USA). DWI was performed in axial planes by using six b values (0, 50, 100, 250, 500, and 1000 s/mm2). The DWI sequence parameters were as follows: repetition time, 6666 ms; echo time, 78 ms; flip angle, 90°; bandwidth, 1305 Hz/Px; slice thickness, 3.0 mm; field of view, 220 mm; acquisition matrix size, 128 × 192; pixel size, 1.7 × 1.1 mm; acquisition time, around 2 min for total acquisition; motion-probing gradient, bipolar type. The isotropic images were created from 3 orthogonal diffuse gradient pulse images. The sequence parameters for 3D T2-weighted fast spin-echo Cube sequence were as follows: TR, 2,000 ms; TE, 85.3 ms; matrix 288 × 288; voxel size, 0.8 × 0.8 × 0.8 mm; and acquisition time, approximately 4 min.
Yamada S., Hiratsuka S., Otani T., Ii S., Wada S., Oshima M., Nozaki K, & Watanabe Y. (2023). Usefulness of intravoxel incoherent motion MRI for visualizing slow cerebrospinal fluid motion. Fluids and Barriers of the CNS, 20, 16.
Full text: Click here
Publication 2023
ECHO protocol Physical Examination Pulse Rate
3
Functional Ultrasound Imaging of Visual Cortex

Protocol full text hidden due to copyright restrictions

Open the protocol to access the free full text link

Publication 2023
Agar Cortex, Cerebral Darkness ECHO protocol Ferrets Pulse Rate Radionuclide Imaging Reading Frames Sinusoidal Beds Transducers Transmission, Communicable Disease Ultrasonics
4
Ultrasound-Mediated Imaging and Delivery of Nanomedicines
A Sonovitro ultrasonic irradiator instrument (ShengXiang, China) was used for US treatment. Ultrasound scanning system (SonoKang, China) and High-resolution small animal ultrasound imaging system (S-Sharp, United States) for US imaging in vitro or in vivo, respectively. The ultrasound signals were recorded before and after the ultrasound treatment.
For in vitro US imaging, the effect of ultrasound intensity on ultrasound imaging of SonoBacteriaBot has been studied, DOX-PFP-PLGA@EcM (1 mL, 1.25 mg/mL) placed in a gel model, were exposed to US irradiation with different intensities (1–3 W/cm2, 1 min, 1 MHz), and then captured US imaging (MI = 0.7, 7.5 MHz). To evaluate the effect of ultrasound treatment time on the imaging effect of SonoBacteriaBot in vitro. DOX-PFP-PLGA@EcM was subjected to ultrasonic irradiation of different durations (0–10 min, 1 W/cm2, 1 MHz), and captured US imaging. Then, Imaging of DOX-PFP-PLGA@EcM after phase transformation by ultrasound treatment under an ultrasound intensity of 1 W/cm2 for 2 min, was observed continuously (0–10 min). Ultrasound images were acquired at different times to evaluate the duration of the imaging signal.
For in vivo US imaging, mice were intravenously injected with DOX-PFP-PLGA @EcM in PBS (100 μL, 2.5 mg/mL). At 1 h after injection, the liver was irradiated using US (1 W/cm2, 10 min, 1 MHz). Subsequently, US imaging (40 MHz) of the liver imaging was performed. The corresponding echo intensity values of the ROI were quantitatively analyzed using ImageJ software.
Du M., Wang T., Feng R., Zeng P, & Chen Z. (2023). Establishment of ultrasound-responsive SonoBacteriaBot for targeted drug delivery and controlled release. Frontiers in Bioengineering and Biotechnology, 11, 1144963.
Full text: Click here
Publication 2023
Aftercare Animals ECHO protocol Liver Mus Polylactic Acid-Polyglycolic Acid Copolymer Ultrasonics
5
Analyzing Mouse Body Composition using Echo MRI
The body composition of mice was analysed using an Echo MRI 3-in-1 scanner (Echo MRI, Houston, TX, USA).
Thompson D., Mahmood S., Morrice N., Kamli-Salino S., Dekeryte R., Hoffmann P.A., Doherty M.K., Whitfield P.D., Delibegović M, & Mody N. (2023). Fenretinide inhibits obesity and fatty liver disease but induces Smpd3 to increase serum ceramides and worsen atherosclerosis in LDLR−/− mice. Scientific Reports, 13, 3937.
Full text: Click here
Publication 2023
Body Composition ECHO protocol Mice, House

Top products related to «ECHO protocol»

1
Tim trio by Siemens
Sourced in Germany, United States, United Kingdom, China
The Tim Trio is a versatile laboratory equipment that serves as a temperature-controlled magnetic stirrer. It features three independent stirring positions, allowing simultaneous operation of multiple samples. The device maintains a consistent temperature range to ensure accurate and reliable results during experimental procedures.
2
32 channel head coil by Siemens
Sourced in Germany, United States, Australia, United Kingdom, Canada
The 32-channel head coil is a key component in magnetic resonance imaging (MRI) systems. It is designed to acquire high-quality images of the human head, enabling detailed visualization and analysis of brain structure and function.
3
Discovery mr750 by GE Healthcare
Sourced in United States, Germany, United Kingdom, Netherlands
The Discovery MR750 is a magnetic resonance imaging (MRI) system developed by GE Healthcare. It is designed to provide high-quality imaging for a variety of clinical applications.
4
Ingenia by Philips
Sourced in Netherlands, Germany, United States, Switzerland, Japan
The Philips Ingenia is a magnetic resonance imaging (MRI) system designed for diagnostic imaging. It provides high-quality images of the body's internal structures to aid in the detection and diagnosis of various medical conditions.
5
Magnetom skyra by Siemens
Sourced in Germany, United States
The MAGNETOM Skyra is a magnetic resonance imaging (MRI) system developed by Siemens. It is designed to provide high-quality imaging for various medical applications. The MAGNETOM Skyra utilizes advanced technology to generate detailed images of the body's internal structures without the use of ionizing radiation.
6
Magnetom trio by Siemens
Sourced in Germany, United States, United Kingdom
The Magnetom Trio is a magnetic resonance imaging (MRI) system manufactured by Siemens. It is designed to produce high-quality images of the body's internal structures. The Magnetom Trio uses a powerful superconducting magnet to generate a strong magnetic field, which, in combination with radio waves, allows for the detailed visualization of the body's anatomy and physiology.
7
12 channel head coil by Siemens
Sourced in Germany, United States, Canada, China, Australia
The 12-channel head coil is a medical imaging device designed for use with MRI (Magnetic Resonance Imaging) systems. It is an essential component that enables the acquisition of high-quality images of the human head. The coil is constructed with 12 individual receiver channels, allowing for efficient signal detection and enhanced image quality.
8
Magnetom prisma by Siemens
Sourced in Germany, United States, Switzerland
The MAGNETOM Prisma is a magnetic resonance imaging (MRI) system designed and manufactured by Siemens. It is a powerful diagnostic imaging device that uses strong magnetic fields and radio waves to generate detailed images of the human body. The MAGNETOM Prisma is capable of providing high-quality, high-resolution imaging data to support clinical decision-making and patient care.
9
Achieva by Philips
Sourced in Netherlands, Germany, United States, United Kingdom, Japan
The Philips Achieva is a versatile laboratory equipment designed for a range of analytical and research applications. It offers advanced capabilities for tasks such as sample preparation, separation, and detection. The Achieva is engineered to provide reliable and consistent performance, making it a valuable tool for various scientific disciplines.
10
Magnetom tim trio by Siemens
Sourced in Germany, United States, United Kingdom
The Magnetom Tim Trio is a magnetic resonance imaging (MRI) system developed by Siemens. It is designed to provide high-quality imaging for medical applications. The Magnetom Tim Trio utilizes advanced technology to capture detailed images of the human body.

More about "ECHO protocol"

Discover the power of the ECHO (Efficient Channel Hopping) wireless communication protocol and its optimization techniques.
The ECHO protocol is a powerful optimization method that enhances the performance of wireless communication systems.
PubCompare.ai's cutting-edge AI-driven platform helps researchers effortlessly locate and compare ECHO protocols from literature, preprints, and patents, enabling them to identify the best protocols and products for their research needs.
This tool provides insightful comparisons and elevates research by leveraging expertise in ECHO protocol optimization.
Explore the latest advancements in ECHO protocol optimization, including techniques like Channel Hopping, Wireless Communication, and Protocol Comparisons.
Discover how PubCompare.ai's platform can help you access a wide range of ECHO-related resources, such as research papers, preprints, and patents, to identify the most suitable protocols for your project.
Whether you're working with MRI systems like the Tim Trio, 32-channel head coil, Discovery MR750, Ingenia, MAGNETOM Skyra, Magnetom Trio, 12-channel head coil, MAGNETOM Prisma, or Achieva, understanding ECHO protocol optimization can be crucial for enhancing wireless communication performance and efficiency.
Leverage PubCompare.ai's expertise to streamline your research and make informed decisions about the best ECHO protocols for your needs.