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Model 2200

Manufactured by A-M Systems
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Sourced in United States

The Model 2200 is a high-precision electrical stimulator designed for a variety of laboratory applications. It features adjustable current and voltage outputs, and supports both constant current and constant voltage modes of operation.

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Lab products found in correlation

Dam80, by World Precision Instruments (1 mentions) Powerlab 8 35, by ADInstruments (1 mentions) Pci 6071e, by National Instruments (1 mentions) Labview, by National Instruments (1 mentions) Model 1700, by A-M Systems (1 mentions) Rhd2132, by Intan Technologies (1 mentions) Pcie 6353, by National Instruments (1 mentions) Rc 22c, by Warner Instruments (1 mentions) Bnc 2120, by National Instruments (1 mentions) Multiclamp 700a, by Molecular Devices (1 mentions) Fastrak, by Polhemus (1 mentions) Mr compatible system, by SA Instruments (1 mentions)

Close spelling variants of this product

Model 2200 stimulus isolator Analog stimulus isolator Model 2200 Model 2200 isolator

23 protocols using model 2200

1

Infrared Stimulation of Cochlear Nerve

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Electric current pulses were delivered to the surface of the left CN using a pair of stainless steel wires insulated except at the tip (200 μm diam.; impedance 0.1–0.5 MΩ). Bipolar, biphasic pulses (100 μs duration) were presented through a stimulus isolator (Model 2200, A-M Systems, Carlsborg, WA) at 27 pulses/s. Infrared pulses for INS were generated using a diode laser (Capella R-1850, Lockheed-Martin Aculight Corp., Bothell, WA). The laser unit was kept outside the sound-attenuating chamber and the optical fiber (400 μm diam.) was led into the chamber via a penetration hole. The distal fiber was mounted to a three-axis micromanipulator and its tip was placed on the surface of the left CN. Unless explicitly stated otherwise, laser parameters were: pulse duration of 0.25 ms, stimulation rate of 23 Hz, and wavelength of 1849 nm. This wavelength is expected to penetrate into the tissue about 700 μm (Hale and Querry, 1973 (link)). Radiant energy of the laser was measured with a high-sensitivity thermopile sensor (PS19Q, Coherent, Santa Clara, CA).
Verma R., Guex A.A., Hancock K.E., Durakovic N., McKay C.M., Slama M.C., Brown M.C, & Lee D.J. (2014). Auditory Responses to Electric and Infrared Neural Stimulation of the Rat Cochlear Nucleus. Hearing research, 310, 69-75.
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2

Electrical Stimulation of Reward Pathway

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All training and testing was conducted in the dark in a video-monitored acrylic arena, with a white noise source to mask environmental distractors. Sessions lasted a minimum of 60 minutes, but could extend up to 150 minutes if the animal was sustaining task performance.
Prior to implantation, all animals were trained to press two levers to deliver chocolate-flavored food pellets (BioServ). Beginning one week after surgery, animals were offered the same two levers, but one lever now triggered electrical stimulation of MFB via a stimulus isolator (A-M Systems Model 2200). Stimulus parameters were titrated until the animal reliably pressed the MFB-stimulation lever to the exclusion of food reward. Pulse trains could be monophasic or biphasic (cathodal leading). Stimulus parameters were adjusted at most weekly, if needed, to sustain behavior. Electrodes in both hemispheres were tested to determine the maximally reinforcing site, but stimuli were only delivered unilaterally in a given session.
Widge A.S, & Moritz C.T. (2014). Pre-frontal control of closed-loop limbic neurostimulation by rodents using a brain-computer interface. Journal of neural engineering, 11(2), 024001.
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3

Nerve Conduction Velocity Measurement in Mice Tails

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NCV from mice tails were measured in a lab-built instrument inside a grounded Faraday cage. Mice were anesthetized using a constant flow of isoflurane. The external body temperature was maintained at 37 °C with a chargeable warm heating pad (Kent Scientific Inc). The body temperature was continuously monitored with a thermal camera (Micro-Epsilon). Tail skin and stainless steel recording electrodes (~29 ga, World Precision Instruments) were sanitized with 70% isopropanol. The recording electrodes were inserted 1 cm distal to the base of the tail. The nerve compound action potential was measured using an extracellular amplifier (DAM80, World Precision Instruments). Stimulating electrodes were inserted approximately 30 mm distal to the recording electrodes. Voltage pulses (2–5 msec duration, 0.6–4 V) were delivered to the stimulating electrodes from a battery powered stimulus isolator (Model 2200, A-M Systems). Recorded data from the extracellular amplifier and from the stimulator were collected and analyzed with PowerLab 8/35 (ADInstruments Inc.) and used to calculate nerve conduction velocity of the compound action potential after completion of the experiment. Mice were returned to their home cages for recovery.
Dannen S.D., Cornelison L., Durham P., Morley J.E., Shahverdi K., Du J., Zhou H., Sudlow L.C., Hunter D., Wood M.D., Berezin M.Y, & Gerasimchuk N. (2020). New in vitro highly cytotoxic platinum and palladium cyanoximates with minimal side effects in vivo. Journal of inorganic biochemistry, 208, 111082.
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4

Electrophysiology Data Acquisition

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We controlled the delivery of current or voltage and data acquisition with a National Instruments card (DAQ, PCI-6071E). We provided the current to our circuit with the DAQ connected to an Analog Stimulus Isolator (A-M Systems, model 2200). The membrane potential was acquired with an analog input of the same DAC, and the information was processed using LabVIEW (National Instruments, TX).
Vazquez-Guerrero P., Tuladhar R., Psychalinos C., Elwakil A., Chacron M.J, & Santamaria F. (2024). Fractional order memcapacitive neuromorphic elements reproduce and predict neuronal function. Scientific Reports, 14, 5817.
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5

Selective Neuromodulation via Directional E-fields

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To generate E-fields directed along specific axes, a stimulation electrode platform was built using four 125 μm thick Ag/AgCl wires that were affixed on a 4 × 4×1mm silicon (Polydimethylsiloxane; PDMS) board in a rectangular configuration (Fig. 1A). The distance between opposite contact pairs was 3.5 mm and the length of each contact was slightly shorter (~3.2 mm). Another Ag/AgCl wire was wrapped 3 times around a 1 mm diameter drill bit to make a helical electrode. After opening a 1.2 mm circular hole at the center of the substrate, the helical electrode was positioned into this hole. Opposing wire electrode pairs (shown in blue and red) were used to generate E-fields in the mediolateral (ML) or rostrocaudal (RC) directions. The helical electrode was used to create E-fields in the dorsoventral (DV) direction by pairing it with a Ag/AgCl wire inserted into the right hind limb. The electrode pairs were connected to the output of a voltage/current isolator unit (Model 2200, A-M Systems) through a commutator that facilitated switching between the electrode sets quickly. The PDMS substrate was placed over the cerebellum with its center positioned over vermis lobule 7 and secured with silk sutures tied to the frame. The hole in the center was filled with normal saline to ensure a stable interface with the helical electrode.
Asan A.S., Lang E.J, & Sahin M. (2020). Entrainment of cerebellar purkinje cells with directional AC electric fields in anesthetized rats. Brain stimulation, 13(6), 1548-1558.
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6

Somatosensory Evoked Responses to Direct Current Stimulation

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We measured the somatosensory-evoked potentials (SEP) and somatosensory-evoked cerebral blood flow (SECBF) response to different direct current stimuli of the forepaw and determined the peripheral nerve stimulation parameters that evoked the maximum response (n = 10).
We used an analog stimulus isolator (Model 2200, A-M Systems, Sequim, WA, USA) with high affinity for the AD converter in the direct current stimulation and connected the 2 needle electrodes puncturing the right forepaw to the output lead of the stimulus isolator. For the stimulus waveform, we designed monophasic rectangular pulses with the 3 parameters of frequency, pulse width, and current value. Based on the results of previous research 2 (link) and preliminary experiments (data not shown), we fixed the pulse width at 10 ms and the current value at 4 mA. Frequency was varied at 3, 5, 7, 9, and 12 Hz. SEP and SECBF were measured simultaneously in each case. Stimulus duration was 10 s in all conditions. Each of the direct current stimulation parameters was used one time only with each animal. The parameters were applied randomly for the measurements.
Yamada M., Takano K., Kawai Y, & Kato R. (2015). Hemodynamic-based Mapping of Neural Activity in Medetomidine-sedated Rats using a 1.5T Compact Magnetic Resonance Imaging System: A Preliminary Study. Magnetic resonance in medical sciences : MRMS : an official journal of Japan Society of Magnetic Resonance in Medicine, 14(3).
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7

Optimizing Deep Brain Stimulation Current

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A cathodic leading square wave current was generated by Digidata digitizer output (Model 1322a, Molecular Devices, CA) and a linear voltage-current conversion isolator (Model 2200, A-M systems, WA). This current signal mimics deep brain stimulation (DBS) parameters. The stimulation began with a 200 μs cathodic current, immediately followed by a 400 μs charge balanced current with half amplitude and reversed polarity. Various current amplitudes were delivered through the microelectrode surface and voltage profiles were recorded with the digitizer at a sample rate of 500 kHz. Linear regression was applied to voltage-current relationship and a voltage threshold of -0.6 V was set as safe charge injection window for stimulation 19 -21 . The CIL was calculated based on the amount of charge at -0.6 V per GSA.
Du Z.J., Luo X., Weaver C, & Cui X.T. (2015). Poly (3, 4-ethylenedioxythiophene)-ionic liquid coating improves neural recording and stimulation functionality of MEAs. Journal of materials chemistry. C, Materials for optical and electronic devices, 3(25), 6515-6524.
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8

Extracellular Electrophysiology with Micropipette Electrode

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A micropipette electrode (573050 suction electrodes, AM systems) was placed near a cell and connected through an electrode holder to a neuroamplifier (Model 1700, AM systems) and an analog stimulus isolator (Model 2200, AM systems). The electrode was connected to the ‘stimulus’ channel of the amplifier and the current was imparted using a manually-triggered digital button, that injected 5 mA at 5 kHz for 10 ms. A part of the current output was also connected to an input of the DAQ card to synchronously record the instance of electrical stimulation. The extracellular field potentials were measured using the same setup used for electrical stimulation to generate the results in Figures 4 and 5, where the Model 1700 amplifier was operated in recording mode. The electrical signals were captured using a DAQ device (NI 6353, National Instruments). The amplifier was set to pass frequencies between 10 and 10,000 Hz with an additional notch filter at 60 Hz to reject electrical noise. The sample arm of the system was placed inside a custom Faraday cage.
Iyer R.R., Liu Y.Z., Renteria C.A., Tibble B.E., Choi H., Žurauskas M, & Boppart S.A. (2022). Ultra-parallel label-free optophysiology of neural activity. iScience, 25(5), 104307.
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9

Vagus Nerve Stimulation Induces Anti-Inflammatory Response

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Example 4

A cortisol-specific signal was extracted from a neurogram obtained from one mouse (mouse A in FIG. 11). The nerve recordings were high-pass filtered (w/160 Hz edge) and converted to .wav format. For a control signal, the cortisol-specific signal from mouse A was transformed to a scrambled signal using a Matlab code that generates a randomized signal with the same amplitudes, but random frequencies while maintaining the total power of the signal. The cervical vagus nerve was isolated from another naïve receiver mouse (mouse B in FIG. 11) and placed on hook stimulating electrodes. The cortisol-specific or scrambled signal was transferred to receiver mouse B using an analog stimulator isolator (Model 2200, A-M Systems). Serum IL-10 levels were monitored in mouse B at regular time intervals. Stimulation of the cervical vagus nerve of the naïve mouse with the cortisol-specific signal induced an increase in serum levels of the anti-inflammatory cytokine IL-10 (FIG. 12). Stimulation of the vagus nerve using the control scrambled signal did not induce an increase in serum IL-10 levels (FIG. 12).

US11541239B2. Nerve stimulation for treatment of diseases and disorders (2023-01-03). THE FEINSTEIN INSTITUTES FOR MEDICAL RESEARCH [US]. Inventors: Kevin J. Tracey [US], Sangeeta S. Chavan [US].
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10

Cortisol-Specific Vagus Nerve Stimulation Enhances IL-10

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Example 4

A cortisol-specific signal was extracted from a neurogram obtained from one mouse (mouse A in FIG. 11). The nerve recordings were high-pass filtered (w/160 Hz edge) and converted to .wav format. For a control signal, the cortisol-specific signal from mouse A was transformed to a scrambled signal using a Matlab code that generates a randomized signal with the same amplitudes, but random frequencies while maintaining the total power of the signal. The cervical vagus nerve was isolated from another naïve receiver mouse (mouse B in FIG. 11) and placed on hook stimulating electrodes. The cortisol-specific or scrambled signal was transferred to receiver mouse B using an analog stimulator isolator (Model 2200, A-M Systems). Serum IL-10 levels were monitored in mouse B at regular time intervals. Stimulation of the cervical vagus nerve of the naïve mouse with the cortisol-specific signal induced an increase in serum levels of the anti-inflammatory cytokine IL-10 (FIG. 12). Stimulation of the vagus nerve using the control scrambled signal did not induce an increase in serum IL-10 levels (FIG. 12).

US10507327B2. Nerve stimulation for treatment of diseases and disorders (2019-12-17). THE FEINSTEIN INSTITUTES FOR MEDICAL RESEARCH [US]. Inventors: Kevin J. Tracey [US], Sangeeta S. Chavan [US].
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