Ni usb 6212

Name: Ni usb 6212
Brand: National Instruments
SKU: jDTiCZIBPBHhf-iFzySG
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Manufactured by National Instruments

29 citations

Sourced in United States, Morocco

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The NI USB-6212 is a multifunction data acquisition (DAQ) device from National Instruments. It provides 16 analog input channels, two analog output channels, and 16 digital input/output channels. The device connects to a computer via a USB interface and is suitable for a variety of measurement and control applications.

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29 protocols using «ni usb 6212»

Measuring Actuation Performance of Soft Actuators

2024

The free displacement during actuation was measured by a laser displacement sensor (LK-G85 and LK-G3001, KEYENCE). The data were collected by the data acquisition board (NI USB-6212, National Instruments). The analog output voltage signal was generated by the same data acquisition board, and the output voltage was amplified through a high voltage amplifier (AMJ-4B10, Matsusada) to provide actuation voltage of the actuator.
The blocked force during the actuation was measured by a load cell (UMI-G500, Dacell), and the signal was amplified by the signal amplifier (DN-AM100, Dacell). The data were collected by the data acquisition board (NI USB-6212, National Instruments). The analog output voltage signal was generated by the same data acquisition board to vary the frequency of the applied voltage, and the actuation voltage was amplified through a high voltage amplifier (AMJ-4B10, Matsusada).
3D shapes and the displacement profiles were measured and analyzed by an optical 3D profiler (VR-5000, KEYENCE). Before measurement, we applied spray (3D scan spray, Helling) which has an average particle size of 2.8 μm on the surface of the developed device for antireflection coating.

Jang S.Y., Cho M., Kim H., Choi M., Mun S., Youn J.H., Park J., Hwang G., Hwang I., Yun S, & Kyung K.U. (2024). Dynamically reconfigurable shape-morphing and tactile display via hydraulically coupled mergeable and splittable PVC gel actuator. Science Advances, 10(39), eadq2024.

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Cerebrovascular Response to Postural Transfer

2024

TCD was used to assess middle cerebral artery blood velocity (MCAv) during a sit-to-stand positional transfer. A 2-MHz TCD probe (RobotoC2MD, Multigon Industries) was used to record right MCAv over the temporal window. The left MCA was used if the right MCA signal was absent. Continuous beat-to-beat MAP was recorded through a cuff around the left middle finger (Finapres Medical Systems, Amsterdam, The Netherlands). A 5-lead electrocardiogram (Cardiocard; Nasiff Associates, Central Square, New York) continuously recorded heart rhythm and was used to synchronize MCAv and MAP across the cardiac cycle.[41 (link),42 (link)] A capnograph (BCI Capnocheck Sleep 9004; Smiths Medical, Dublin,OH) recorded continuous expired end tidal carbon dioxide (P_ETCO₂) through a nasal canula and participants were instructed to breathe through their nose throughout the 3-minute duration of the sit-to-stand recording. All data were recorded at 500Hz. During the first minute of the recording, the participant remained seated quietly. At the 60-second mark of the recording, the experimenter verbally cued the participant to stand and remain standing for 2 minutes. Time-synchronized raw data were acquired through an analog-to-digital unit (NI-USB-6212, National Instruments) and custom written MATLAB software (The Mathworks Inc. Natick, MA).

Palmer J.A., Kaufman C.S., Whitaker-Hilbig A.A, & Billinger S.A. (2024). APOE4 carriers display loss of anticipatory cerebral vascular regulation over AD progression. medRxiv.

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Cerebrovascular Dynamics Measurement

2024

Data was collected at 500 Hz via an analog-to-digital unit (NI-USB-6212, National Instruments) and custom-written code within MATLAB (v2014a, TheMathworks Inc, Natick, Massachusetts). 38 (link) Beat-to-beat data was processed offline using the QRS complex of the ECG. 38 (link) The left MCAv signals for CON was used for analysis. However, if left MCAv was not obtainable or had noise, the right MCAv signal was used. 38 (link) In individuals post-stroke, the ipsilesional hemisphere's MCAv signal was used to compare to CON.

Whitaker A.A., Aaron S.E., Chertoff M., Brassard P., Buchanan J., Nguyen K., Vidoni E.D., Waghmare S., Eickmeyer S.M., Montgomery R.N, & Billinger S.A. (2024). Lower dynamic cerebral autoregulation following acute bout of low-volume high-intensity interval exercise in chronic stroke compared to healthy adults. Journal of applied physiology (Bethesda, Md. : 1985), 136(4).

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Corresponding organizations : University of Kansas Medical Center, Medical College of Wisconsin, Université Laval, Institut Universitaire de Cardiologie et de Pneumologie de Québec, University of Kansas

Dynamic Tactile Perception Study

2024

The perception studies on human volunteers were approved by the Institutional Review Board of Korea Advanced Institute of Science and Technology (KH-2023-249). None of the 12 participants (2 females and 10 males, ages between 25 and 29) reported abnormalities in touch perception, and they were allowed to take rest freely whenever they wanted. Participants directly applied the haptic stimuli themselves and submitted their responses identifying the patterns through a keyboard with their nondominant hand. A partition was used to prevent participants from seeing the developed haptic interface. To implement dynamic tactile pattern, the electrode was controlled individually by the customized multichannel control circuit consists of a microcontroller unit (MCU) and customized multichannel HV amplifier circuit. The voltage signal was generated by the MCU and amplified through customized multichannel HV amplifier. The detailed actuation sequence for each dynamic pattern is shown in the Supplementary Materials. In the user study for shape and texture identification, an analog output voltage from a data acquisition board (NI USB-6212, National Instruments) was amplified through a high voltage amplifier (AMJ-4B10, Matsusada) to provide actuation voltage. In the user study for surface roughness discrimination, the same experimental setup with an extra high voltage amplifier was used.

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Quantifying Acoustic Environment in Experimental Arena

2023

Sound samples were produced in MATLAB (Release 2019b, The Mathworks, Inc., Natick, USA) using a laptop connected to a DAQ (NI USB-6212; National Instruments, USA), transmitting the signal through an amplifier (Prosound Power AMP 200; frequency response: 20 Hz–20 kHz), and was emitted via the UW30 underwater transducer. Acoustic stimuli were standardised such that the desired SPL was reached in the centre of the experimental arena. Use of artificial stimuli allowed for control of the specific acoustic components tested.
Prior to exposing fish to stimuli, the acoustic environment of the experimental arena was quantified. A total of 246 measurements were made using a calibrated hydrophone (Brüel & Kjær 8105) to produce a 3D representation of the SPL in the experimental arena (Supplementary Fig. S1). The measurements consisted of 82 points, 5 cm apart at depths of 5, 15, and 25 cm measured from the water surface (Table 3). The data capture and stimulus generation were synchronised to facilitate computation of the PA. Both SPL and PA were quantified to create maps of the sound field. The PA, a, was calculated as:

a = - \frac{1}{ρ} \nabla P

where ρ is the ambient density and P is the pressure⁸⁰.Table 3

The mean ± standard deviation of the 145 dB re 1 μPa, 120 ms pure tone (columns 2–5) SPL and particle acceleration (column 6) across the cylindrical tank at frequencies of 250 Hz; 400 Hz; 600 Hz; 800 Hz; 1000 Hz; 2000 Hz.

Frequency (Hz)	5 cm (dB re 1 μPa)	15 cm (dB re 1 μPa)	25 cm (dB re 1 μPa)	Centre SPL (dB re 1 μPa)	15 cm (dB re 1 mm s⁻²)
250	136.3 ± 0.7	143.5 ± 0.6	146.9 ± 0.5	143.3 ± 0.4	18.5 ± 4.8
400	137.9 ± 0.4	145.0 ± 0.5	148.3 ± 0.4	144.9 ± 0.3	19.0 ± 5.1
600	137.5 ± 0.4	144.4 ± 0.4	147.6 ± 0.3	144.5 ± 0.3	20.2 ± 5.0
800	137.2 ± 0.5	144.1 ± 0.5	147.8 ± 0.3	144.2 ± 0.3	22.8 ± 4.1
1000	136.1 ± 0.6	143.2 ± 0.8	145.8 ± 0.3	143.4 ± 0.4	24.5 ± 3.7
2000	139.9 ± 0.8	144.8 ± 0.6	141.0 ± 2.5	145.1 ± 0.1	48.6 ± 4.1

Point measurements were taken at 3 depths (5 cm; 15 cm; 25 cm measured from the water surface). Centre SPL refers to the average of the four SPLs in the middle in the 15 cm layer of the tank.

The pressure gradient was computed using the measurements of the pressure signal. The root mean square (RMS) of the pressure difference was calculated independently in three directions (x, y and z). The pressure gradient was obtained by dividing by the distance between measurements. The RMS PA Eq. (1), in each direction, was calculated by dividing the pressure gradient by the water density. The total RMS PA was determined by combining the values in all three directions, with the results expressed in decibels (dB re 1 mm s⁻²). Following this the PA was represented in maps (Supplementary Fig. S2).
The measured ambient SPL (TC4032, manufacturer-calibrated sensitivity − 170 dB re: 1 V μPa; Teledyne Reson, USA) was on average less than 96 dB re 1 µPa, which was the electrical noise floor of the measurement system being used. The SPL was relatively uniform across the horizontal plane for each frequency, with greatest variation observed at the highest frequency (shortest wavelength) at 2000 Hz (Table 3). The SPL differed by ≈ 10 dB between the top and bottom of the tank. The PA increased with frequency and varied up to 4.8 dB within the horizontal plane.

Holgate A., White P.R., Leighton T.G, & Kemp P.S. (2023). Applying appropriate frequency criteria to advance acoustic behavioural guidance systems for fish. Scientific Reports, 13, 8075.

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Corresponding organizations : University of Southampton

Top 5 most cited protocols using «ni usb 6212»

Acoustic Monitoring of Ultrasonic Vocalizations

Cited 3 times

Animals were continuously acoustically monitored by a condenser ultrasound microphone (Avisoft-Bioacoustics CM16/CMPA-5V, Berlin, Germany; 15–180 kHz, with a flat frequency response (±6 dB) between 25 and 140 kHz) placed 20 cm above the cage floor keeping the alignment errors between sound and physiological parameters to less than 1 msec. Signals were acquired through a multi-channel data acquisition device (NI USB-6212; National Instruments, Austin, TX), sampled at 150 or 200 kHz and saved as uncompressed files on a computer using Avisoft Recorder software (Avisoft-Bioacoustics).
USV were spontaneously uttered after the presentation of female odor or a female. All males had previous experience with females.
All measurements were performed using sound analysis software PRAAT (version 5.0.41; www.praat.org). Analysis was done in 130 Hz bandwidth spectrograms. USV were divided into 22 kHz calls (near-constant frequency calls between 20 and 29 kHz) and 50 kHz calls categories, following the categorization by Wright et al. (2010) (link). The 50-kHz calls contained 50 kHz trills (rapid frequency oscillations with a period of approximately 10 msec; either sinusoidal or appearing as repeated “inverted-Us”), 50 kHz flat calls (near-constant frequency greater than 30 kHz with a mean slope between −0.2 and 0.2 kHz/msec), 50 kHz complex calls (contain two or more directional changes in frequency of at least 3 kHz each), 50 kHz upward calls (monotonically increasing in frequency, with a mean slope not less than 0.2 kHz/msec), 50 kHz composite calls (calls other than flat/trill combinations, that comprise two or more categories).

, & RIEDE T. (2013). Stereotypic Laryngeal and Respiratory Motor Patterns Generate Different Call Types in Rat Ultrasound Vocalization. Journal of experimental zoology. Part A, Ecological genetics and physiology, 319(4), 213-224.

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Corresponding organizations : University of Utah

Cerebrovascular Responses to Exercise

Cited 2 times

With respect to the exercise response we have previously demonstrated that there is no significant difference in the right versus left MCAv response to exercise (Billinger, Craig, et al. 2017 (link)). Herein, the left MCA was the primary vessel of interest. If the signal was not obtainable, then the right side was used. (Billinger, Craig, et al. 2017 (link)) Briefly, participants were instrumented with the following equipment in the seated position: transcranial Doppler ultrasound (TCD) (Multigon Industries Inc. Yonkers, NY), beat-to-beat mean arterial blood pressure (MAP) (Finometer, Finapres Medical Systems, Amsterdam, The Netherlands) on the left middle finger, end-tidal carbon dioxide (P_ETCO₂ in mmHg) via nasal cannula (BCI Capnocheck Sleep 9004 Smiths Medical, Dublin, OH) and HR via electrocardiogram (Cardiocard, Nasiff Associates, Central Square, NY). Data was acquired through an analog-to-digital data acquisition unit (NI-USB-6212, National Instruments) and custom written software operating in MATLAB (v2014a, The Mathworks Inc. Natick, MA).

Witte E., Liu Y., Ward J.L., Kempf K.S., Whitaker A., Vidoni E.D., Craig J.C., Poole D.C, & Billinger S.A. (2019). Exercise Intensity and Middle Cerebral Artery Dynamics in Humans. Respiratory physiology & neurobiology, 262, 32-39.

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Corresponding organizations : University of Kansas Medical Center, Shawnee Mission Medical Center, University of Kansas, Kansas State University

Optical Trap Indentation of Cells

Cited 1 time

The optical trap that was used to indent the cells at low force was built around a commercial upright microscope body (Eclipse 50i, Nikon, Japan) and set up for trapping and detection vertical to the coverslip (Fig. 1B). The 980 nm laser light emitted from a 300 mW single mode fibre was collimated and combined with the optical path using a dichroic mirror (unless specified all optical components were purchased at Thorlabs GmbH, Germany). The laser beam was focused in the sample by a water immersion objective (60×1.27NA Plan Apo IR objective, Nikon, Japan). A closed-loop objective-piezo element (P-721, Physik Instrumente GmbH, Karlsruhe, Germany) was used to move the objective up and down. To measure the position of the trapped bead with respect to the trap centre, the trapping laser light was collected through an air condenser and projected onto a quadrant photo detector placed in a conjugate plane of the back focal plane. The detector was overfilled to achieve an effective numerical aperture of 0.4 for the collection of the laser light [36] (link). The sum signal of the quadrant photo detector that contains the z-position information of the trapped bead was digitized by an analogue to digital converter at a sampling frequency of 12 kHz (NI USB-6212, National Instruments, Austin, TX, US). The imaging part of the microscope consisted of a blue LED that was imaged on the back focal plane of the condenser and a CCD camera placed at 200 mm from the tube lens.
A coverslip containing the cells was mounted in a closed sample chamber, consisting of a microscope slide, a 100 µm thick spacer and the coverslip. Before the sample chamber was closed, polystyrene beads of 0.76 µm diameter (Bangs laboratories, Fishers, IN, USA) were added to the buffer.
Although the trapping laser is focused onto the bead and outside of the cell, most of the laser light will pass through the cell for the duration of the experiment (Fig. 1B). To minimize the potential cell damage we used near-infrared light. The used wavelength of 980 nm was specifically chosen to minimize the induced cell damage [37] (link). To confirm this we positioned the laser focus just outside of the cell periphery for 10 minutes (about 10 times the duration of the indentation experiment) and monitored the cell for signs of stress using optical microscopy. One hour after the exposure to the laser light, all cells (n = 6) were completely indistinguishable from the non-radiated cells, with no signs of bleb formation or other changes in cell appearance.

Nawaz S., Sánchez P., Bodensiek K., Li S., Simons M, & Schaap I.A. (2012). Cell Visco-Elasticity Measured with AFM and Optical Trapping at Sub-Micrometer Deformations. PLoS ONE, 7(9), e45297.

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Corresponding organizations : University of Göttingen, Nanoscale Microscopy and Molecular Physiology of the Brain Cluster of Excellence 171 — DFG Research Center 103, Max Planck Institute of Experimental Medicine

Cerebrovascular Responses to Exercise in Stroke

Cited 1 time

With respect to the exercise response, our previous work demonstrated that there was no significant difference in the right versus left MCAv response to exercise in healthy adults.⁹ Herein, the left MCA was the primary vessel of interest for the older adults. For the participants with stroke, both MCA signals were acquired in one visit. In the seated position on the stepper, individuals were set up with the following equipment: 1) transcranial Doppler ultrasound (TCD) (Multigon Industries Inc. Yonkers, NY). An adjustable headband and 2-MHz TCD probes with ultrasonic gel were placed on the temporal window (temple region of the head) for acquisition of MCA blood flow velocity cm*sec⁻¹.^{16 (link)} The MCA was accurately identified using practice standards for probe positioning and orientation, MCA depth selection and velocity flow direction.^{16 (link)} The TCD sonographer, who was blinded to the side of stroke, entered the room only after the participant was set up; 2) A 5- lead electrocardiogram (ECG; Cardiocard, Nasiff Associates, Central Square, NY) recorded HR; 3) A nasal cannula and capnography (BCI Capnocheck Sleep 9004 Smiths Medical, Dublin, OH) was used to assess end tidal carbon dioxide (P_ETCO₂); and 4) we recorded beat to beat mean arterial pressure (MAP; Finometer, Finapres Medical Systems, Amsterdam, The Netherlands) from the left middle finger. Data acquisition of raw data occurred through an analog-to-digital unit (NI-USB-6212, National Instruments) and custom written software operating in MATLAB (v2014a, The Mathworks Inc. Natick, MA); (see Video, Supplemental Digital Content 1, which demonstrates the experimental procedure set up).
Moderate intensity exercise was defined as 45% to 55% of the participant’s heart rate reserve. We determined the HR range by using either: 1) age-predicted (220- age) HR maximum (HR_max) or 2) for participants using beta-blocker medication, we used 164-0.72 × age^{17 (link)} to calculate HR_max. We determined the HR range for the moderate intensity bout using the Karvonen formula,^{9 ,10} HR range = [% exercise intensity (age-predicted HR max-resting HR)] + resting HR.¹² After the setup, the BL recording lasted 90 seconds followed by 6 minutes of moderate intensity exercise at the targeted HR range. The participants were instructed to maintain a step rate of approximately 90 steps per minute throughout the entire exercise bout and resistance was adjusted to obtain the targeted workloads and HR range.⁹ Work rate increased during the first 30 seconds of exercise until the target work rate was reached. At the end of exercise, recording stopped and the participant engaged in an active cool down for 2 minutes and then rested until HR returned to baseline. Participants then repeated the 90 seconds BL assessment and 6 minutes of moderate intensity exercise. Our previous work revealed improved signal-to-noise ratio when the data acquired from multiple bouts of exercise are averaged.⁹Variables were sampled at 500 Hz and then interpolated to 2.0 Hz. Three-second averages were calculated and then smoothed using a 9-second sliding window average.¹⁰ We used commercial statistical software(R version 3.2.4, R Core team, Vienna, Austria¹⁸ with the ‘nls’ function package) to model the response. Data with R-to-R intervals greater than 5 Hz or changes in peak blood flow velocity greater than 10 cm/s in a single cardiac cycle were considered artifact and censored. Acquisitions with more than 15% of data points censored were discarded.

Kempf K.S., Whitaker A.A., Lui Y., Witte E., Perdomo S.J., Ward J.L., Eickmeyer S., Ledbetter L., Abraham M, & Billinger S.A. (2016). The Effect of Stroke on Middle Cerebral Artery Blood Flow Velocity Dynamics During Exercise. Journal of Neurologic Physical Therapy, 43(4), 212-219.

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Corresponding organizations : Eunice Kennedy Shriver National Institute of Child Health and Human Development, National Center for Advancing Translational Sciences, University of Kansas Medical Center

Magneto-Electro-Mechanical Cantilever Sensing

Cited 1 time

To realize a cantilever, a fabricated structure was clamped at one end (on the side of electrical connectors) in a specifically designed 3D printed holder from the polylactic acid (PLA) material. The resulting dimensions of the cantilever are shown in Figure 2a. The MAE material was always bonded to the “negative” side of the PE element. The side “polarity” is defined by the PE element manufacturer. On this side, the manufacturer’s logotype is imprinted, see Figure 1. The cantilever was always clamped in such a way that the MAE was on its top side.
The cantilever in the holder was placed between the poles of a large electromagnet (EM2 model, MAGMESS Magnetmesstechnik Jürgen Ballanyi e.K., Bochum, Germany), cf. Figure 2b. The pole diameter was 9.2 cm and the vertical distance between the poles was 3.4 cm. The vertical magnetic field of the electromagnet was highly uniform over the entire space where the cantilever could move. We verified that the uniformity of a magnetic field was better than 99.9% over the right circular cylinder with a radius of 2 cm and a height of 3.4 cm, which symmetry axis coincided with the symmetry axes of the magnetic poles. The electromagnet was powered by a bipolar power supply (FAST-PS 1k5, CAEN ELS s.r.l., Basovizza, Italy). The deflection of a cantilever was recorded using a CMOS-based camera (Alvium 1800 U-319 m, Allied Vision Technologies GmbH, Stadtroda, Germany) with a suitable lens (Edmund Optic Double Gauss Focusable, 25 mm C-mount F4.0 1.3”, Barrington, New Jersey, NJ, USA) and a backlight LED illumination (LED Illuminant G4 Pen). The generated voltage by a PE element was measured using a data acquisition board (NI USB-6212, National Instruments, Austin, TX, USA). The generated electrical charge was obtained by electrical current integration using a charge amplifier (Kistler 5018A, Winterthur, Switzerland). The entire experimental process was automated using the LabVIEW software.
The “negative” side of the PE element was connected electrically to the conducting shield (“ground”) of the coaxial cable, while the “positive” side was connected to the core electrode (“signal”). With such a choice of the signal polarity, the first voltage peak was positive, when the composite cantilever was deflected down upon application of an external magnetic field. When an external magnetic field was switched off then, the second voltage peak was negative, see Section 3.1 for details. If the cantilever was deflected up when a magnetic field was switched on and off, the polarity of two voltage peaks was changed to the opposite.

Glavan G., Belyaeva I.A., Ruwisch K., Wollschläger J, & Shamonin M. (2021). Magnetoelectric Response of Laminated Cantilevers Comprising a Magnetoactive Elastomer and a Piezoelectric Polymer, in Pulsed Uniform Magnetic Fields. Sensors (Basel, Switzerland), 21(19), 6390.

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Corresponding organizations : Regensburg University of Applied Sciences, Osnabrück University

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USB-6212 - 38 citations NI USB-6212 BNC - 8 citations NI-6212 - 3 citations NI USB-6212 DAQ - 3 citations

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