Warning: Check to make sure devices are inactive upon arrival at your facility. Do not store within 10 cm of iron tools, power transformers, computers, or external hard drives. During implantation, take note that stainless steel tools and work surfaces are often magnetic, and can activate and deactivate your transmitters.
The Subcutaneous Transmitter (A3028) is an implantable telemetry sensor for rats and mice that provides high-fidelity amplification and recording of one or two biopotential inputs. The device comes in rechargeable and non-rechargeable versions, as well as fully-implantable and head-mounting versions.
The A3028A displaces volume 1.3 ml and provides two EEG channels with bandwidth 160-Hz for fifteen days. The A3028E displaces 3.0 ml, and provides one EEG channel with 160 Hz and 512 SPS for eighteen weeks. Both the A3028A and A3028E are fully-implantable beneth the skin of an animal. The A3028MX is a head fixture with replaceable battery that provides two EEG channels with 640-Hz and 2048 SPS for four days. The A3028M may be mounted on the skull of an animal, but may not be implanted beneath the skin.
All versions of the A3028 operate within our Subcutaneous Transmitter System. The A3028 may be equipped with rechargeable or primary batteries. When the battery is rechargeable, we recharge it through the red X and the blue C leads using an especially designed Battery Charger (A3033). Primary batteries offer three times the charge density of rechargeable batteries. As a consequence, non-rechargeable transmitters offer two to three times the operating life of rechargeable transmitters. Rechargeable transmitters may be restored to full capacity after each implantation, but their electrode leads suffer the same damage and length reduction as those of a non-rechargeable transmitter. We warranty all our implantable devices against corrosion and manufacturing defect for one year after delivery. We do not warranty the devices against damage during explantation, which is traumatic to the leads and antenna. You can follow our recharging and soldering instructions to recharge batteries and replace damaged leads. Or you can send your rechargeable transmitters back to us and we will recharge their batteries, test their frequency response and gain, and repair damaged leads as needed. Our price list gives the cost of these services and of the transmitters themselves. Transmitters with battery holders are intended to be mounted in head fixtures, and we deliver them with a plastic enclosure that may be cemented to an animal's skull. Their batteries may be replaced at any time.
We turn the A3028 on and off with a magnet. We recommend a cow magnet. The A3028A comes with three helical stainless-steel leads coated with silicone. The three leads provide us with two biopotential inputs, X and Y, that share a common ground, C. The sensor measures the voltage difference X−C and Y−C. The electrodes at the end of the wires can be stainless steel screws, gold pins, or bare helical wire, as we discuss in Electrodes and The Source of EEG.
|Volume of Transmitter Body||1.3 ml|
|Mass of Transmitter Body||2.2 g|
|Lead Dimensions||diameter 0.7±0.1 mm, length up to 150 mm|
|Maximum Dimensions||14 mm × 14 mm × 8 mm|
|Operating Life||360 hours|
|Shelf Life||27 months|
|Number of Inputs||2|
|Type of Input||Differential|
|Input Impedance||10 MΩ || 2 pF|
|Sample Rate (Each Input)||512 SPS|
|Input Dynamic Range||27 mV|
|Input Bandwidth||0.3-160 Hz|
|Input Noise||≤12 μV rms|
|Input Mains Hum||<1 μV|
|Total Harmonic Distortion||<0.1%|
The A3028D is the same circuit with the same functionality as the A3028A, but with a 255 mA-hr battery instead of the A3028A's 48 mA-hr battery. The A3028D's volume is 3.0 ml and its operating life is 1900 hours.
All versions of the A3028 turn on and off with the application of a magnetic field. We like to use cow magnets. Component U2 is a micro-power hall effect switch. When it detects a magnetic field, it asserts its output. When we remove the field, the transmitter changes state. If it is inactive, it activates. If it is active, it deactivates. The state change does not occur when we bring the magnet close to the transmitter, it occurs when we move the magnet away.
We determine the version of a transmitter during assembly, programming, and encapsulation. We might change capacitors on the board to set the filter frequencies. We might change resistors to set the gain. We program the logic chip to set the sample rate for each channel. We can equip the circuit with various sizes of battery. The larger the battery, the longer the operating life.
The A3028 transmits one or two signals. Each signal has its own channel number. Each sample of each signal is transmitter by the A3028 with a radio-frequency message. Each message contains a channel number, as we describe in Message Encoding. Channel numbers lie in the range 1-222. A two-channel transmitter transmits on channels n and n+1, where n is an odd number.
We can program the A3028 to take anything from 128-4096 SPS. We can enable either or both of its inputs. The A3028PV1 circuit is a variant of the A3028 circuit that provides only input. The circuit board itself is only 10.2 mm wide and 9.6 mm high, compared to 12 mm square for the two-input circuit.
[20-FEB-21] The Subcutaneous Transmitter (A3028) can be equipped with a dozen different batteries, any lead length up to 150 mm, several lead diameters, one or two recording channels, a dozen varieties of electrode, several types of antenna, and a range of bandwidths, gains, and sample rates. You specify exactly which transmitter you want with a full SCT part number.
The part number begins with A3028 and is followed by the primary version code, which can be a single letter, as in A3028A, or a letter followed by more letters and numbers, as in A3028S2Z. We can create new versions to your specifications, in which case we will assign the new version a new primary version code.
The table below lists the A3028 primary version codes. Additional tables give codes for electrodes, leads, and antennas.
L × W × H
|A3028T1R||0.3-40 Hz, 128 SPS, 0.38 μV/cnt||Omitted||5 (ML621S/DN)||0.50||16 × 11 × 3.7||1.0||160||3|
|A3028P1||0.3-40 Hz, 128 SPS, 0.41 μV/cnt||Omitted||30 (CR1025)||0.65||19 × 11 × 3.7||1.4||860||17|
|A3028P2||0.3-80 Hz, 256 SPS, 0.41 μV/cnt||Omitted||30 (CR1025)||0.65||19 × 11 × 3.7||1.4||640||17|
|A3028P3||0.3-160 Hz, 512 SPS, 0.41 μV/cnt||Omitted||30 (CR1025)||0.65||19 × 11 × 3.7||1.4||390||17|
|A3028S1||0.3-40 Hz, 128 SPS, 0.41 μV/cnt||Omitted||48 (CR1225AH)||0.98||21 × 13 × 3.7||1.7||1400||27|
|A3028S2||0.3-80 Hz, 256 SPS, 0.41 μV/cnt||Omitted||48 (CR1225AH)||0.98||21 × 13 × 3.7||1.7||950||27|
|A3028S3||0.3-160 Hz, 512 SPS, 0.41 μV/cnt||Omitted||48 (CR1225AH)||0.98||21 × 13 × 3.7||1.7||620||27|
|A3028S2Z||0.0-80 Hz, 256 SPS, 4.1 μV/cnt||Omitted||48 (CR1225AH)||0.98||21 × 13 × 3.7||1.7||930||27|
|A3028A||0.3-160 Hz, 512 SPS, 0.41 μV/cnt||0.3-160 Hz, 512 SPS, 0.41 μV/cnt||48 (CR1225AH)||1.3||14 × 14 × 7||2.2||360||27|
|A3028B||0.3-160 Hz, 512 SPS, 0.41 μV/cnt||Disabled||48 (CR1225AH)||1.3||14 × 14 × 7||2.2||620||27|
|A3028C||Disabled||0.3-80 Hz, 256 SPS, 0.41 μV/cnt||48 (CR1225AH)||1.3||14 × 14 × 7||2.2||950||27|
|A3028K||Disabled||0.3-40 Hz, 128 SPS, 0.41 μV/cnt||48 (CR1225AH)||1.3||14 × 14 × 7||2.2||1400||27|
|A3028F||0.3-320 Hz, 1024 SPS, 0.41 μV/cnt||0.3-320 Hz, 1024 SPS, 0.41 μV/cnt||48 (CR1225AH)||1.3||14 × 14 × 7||2.2||180||27|
|A3028H||0.3-80 Hz, 256 SPS, 0.41 μV/cnt||0.3-80 Hz, 256 SPS, 0.41 μV/cnt||48 (CR1225AH)||1.3||14 × 14 × 7||2.2||620||27|
|A3028J||0.3-160 Hz, 512 SPS, 0.41 μV/cnt||3-200 Hz, 512 SPS, 1.4 μV/cnt||48 (CR1225AH)||1.3||14 × 14 × 7||2.2||360||27|
|A3028M||0.3-640 Hz, 2048 SPS, 0.41 μV/cnt||0.3-640 Hz, 2048 SPS, 0.41 μV/cnt||48 (CR1225AH)||1.3||14 × 14 × 7||2.2||100||27|
|A3028U||0.0-160 Hz, 512 SPS, 4.1 μV/cnt||0.0-160 Hz, 512 SPS, 4.1 μV/cnt||48 (CR1225AH)||1.3||14 × 14 × 7||2.2||340||27|
|A3028V||0.3-160 Hz, 512 SPS, 0.41 μV/cnt||30-640 Hz, 16 SPS, 0.41 μV/cnt||48 (CR1225AH)||1.3||14 × 14 × 7||2.2||620||27|
|A3028MX||0.3-640 Hz, 2048 SPS, 0.41 μV/cnt||0.3-640 Hz, 2048 SPS, 0.41 μV/cnt||48 (CR1225)||2.6||16 × 16 × 10||3.2||100||27|
|A3028NX||0.3-160 Hz, 512 SPS, 0.41 μV/cnt||Disabled||48 (CR1225)||2.6||16 × 16 × 10||3.2||620||27|
|A3028D||0.3-160 Hz, 512 SPS, 0.41 μV/cnt||0.3-160 Hz, 512 SPS, 0.41 μV/cnt||255 (BR2330A/HDN)||3.0||24 × 24 × 8||5.9||1900||140|
|A3028G||0.3-320 Hz, 1024 SPS, 0.41 μV/cnt||0.3-320 Hz, 1024 SPS, 0.41 μV/cnt||255 (BR2330A/HDN)||3.0||24 × 24 × 8||5.9||1000||140|
|A3028E||0.3-160 Hz, 512 SPS, 0.41 μV/cnt||Disabled||255 (BR2330A/HDN)||3.0||24 × 24 × 8||5.8||3200||140|
|A3028Q||0.3-320 Hz, 1024 SPS, 0.41 μV/cnt||0.3-320 Hz, 1024 SPS, 0.41 μV/cnt||560 (CR2354/HFN)||4.5||24 × 24 × 11||8.5||2200||300|
|A3028L||0.3-320 Hz, 1024 SPS, 0.41 μV/cnt||0.3-320 Hz, 1024 SPS, 0.41 μV/cnt||1000 (BR2477A/HBN)||6.0||27 × 27 × 14||13.0||4000||550|
The shelf life for a non-rechargeable transmitter is how long it takes to exhaust the battery permanently when we leave it inactive on the shelf. The shelf life of a rechargeable transmitter is how often we must re-charge it to keep its battery in good condition. See below for details of current consumption and how to calculate battery life of new versions of the A3028. Transmitters with battery holders are intended for use in head fixtures. We can replace the battery, but we cannot implant the device because the battery holder is not water-proof. The transmitter comes with a head fixture enclosure that is cemented to the animal skull.
By default, we set the top of the frequency range at one third the sample rate. When its cut-off frequency is one third the sample rate, the A3028's low-pass filter provides 20 dB of attenuition at one half the sample rate. Frequencies above one half the sample rate will be distorted by sampling, and so compromise the fidelity of the recording. Because the EEG signal contains less and less power as frequency increases, this attenuition is sufficient to ensure that distorted frequencies are insignificant.
After the primary version number, the A3028 part number continues with a specification of the electrodes at the end of the leads. The leads are color-coded with colors that do not blend with the natural color of animal tissue. The X lead is red, Y is yellow, and C is blue. A dual-channel transmitter produces two radio-frequency message sequences with two separate channel numbers. The lower of the two is X and the higher is Y. A single-channel transmitter may be equipped with only X or only Y. If the single channel is X, the leads will be red and blue. If the single channel is Y, the leads will be yellow and blue. We specify the electrodes with electrode letters, as defined in our electrodes table. We give the letter of the X-lead electrode first, the Y-electrode second, and the C-lead last. If the transmitter is single-channel, it will have only an X-lead or a Y-lead, not both, and we specify its electrode first. Thus A3028C-DA is a gold pin on the Y-lead and a bare wire on the C-lead, and A3028H-DDK is gold pins on X and Y, small screw on C.
We specify the leads with a letter that gives the type of lead, and the length of the lead in millimeters. We present the lead letter codes in our leads table. Thus A3028C-DA-B45 is equipped with two 45-mm long leads each 0.7 mm in diameter. The final section of the part number specifies the antenna with a single letter, as specified in our antenna table. Thus A3028C-DA-B45-B uses a 30-mm loop antenna made out of stranded stainless steel.
Each lead of the transmitter has its own terminating electrode. We specify the electrode of each lead with its own letter code. We specify these electrodes with two letters for a single-channel transmitter (X or Y, and C), three letters for a dual-channel transmitter with common reference potential (X, Y, and C), and four letters for a dual-channel transmitter with separate reference potentials (X or Y, C, and Y−). The letters "DDA" specify D-pin on X and Y and bare wire on C, while the letters "AAAA" specify bare wire on X or Y, C, and Y−.
|A||Bare wire, length 2 mm, stainless steel helix.|
|B||Screw, thread 0-80, diameter 1.6 mm, length 3.2 mm.|
|C||Screw, thread M0.5, diameter 0.5 mm, length 0.6 mm.|
|D||Pin, diameter 0.30 mm, length 2.1 mm, Mill-Max 4353-0-00-15-00-00-33-0|
|E||Socket, for pin diameters 0.20-0.33 mm, Mill-Max 4428-0-43-15-04-14-10-0|
|F||Pin, diameter 0.64 mm, length 4.1 mm, Mill-Max 5035-0-00-15-00-00-33-0.
Mates with Plastics One socket E363/0.
|G||Pin, diameter 0.51 mm, length 4.4 mm, Mill-Max 5063-0-00-15-00-00-33-0.
Mates with Plastics One socket MS303/6.
|H||Depth electrode, wire 125-μm dia Pt-Ir, insulation 200-μm dia teflon.
Locate with guide cannula, mates with D-Electrode pin using E-Electrode socket.
|J||Depth electrode, 125-μm dia 316SS wire, insulation 200-μm dia teflon.
Locate with guide cannula, mates with D-Electrode pin using E-Electrode socket.
|K||Screw, thread 00-90, diameter 1.2 mm, length 1.6 mm.|
|L||Screw, thread 000-120, diameter 0.86 mm, length 1.6 mm.|
|M||Bare silver wire, diameter 125 μ, length 50 mm.|
|N||Pin, diameter 0.38 mm, length 3.2 mm, Mill-Max 4689-0-00-15-00-00-33-0|
|W||Depth electrode, straight wire 125-μm dia 316SS, insulation 200-μm dia teflon.
Locate with hypodermic tube, mates with D-Electrode pin using E-Electrode socket.
|X||Depth electrode, wire 125-μm dia 316SS, insulation 200-μm dia teflon.
Locate with hypodermic tube, mates with A-Electrode bare wire using crimp ferrule.
By default, we solder screws, pins, and sockets perpendicular to leads and wires. But if we preceed the electrode letter code with a lower-case "s", the pin, screw, or socket is parallel to the lead or wire, as shown below.
We do not attach depth electrodes to transmitter leads. Instead, we connect the depth electrode to one of the transmitter leads during implantation, which allows us to tunnel the leads up under the skin of the neck to the head. We connect the depth electrode with a pin-and-socket or a crimp contact. The pin and socket is always a D-Electrode or S-Electrode pin on the transmitter lead and an E-Electrode socket on the depth electrode wire. The D and S-Electrodes are the same pin, but soldered at right angles and parallel to the axis of the transmitter lead respectively. The crimp contact is between a 2-mm length of bare wire on the electrode and a 2-mm length of helical steel wire at the end of the transmitter lead, which we enclose in a steel ferrule and compress to make a crimp contact. See SCT Implantation for an introduction to the implantation procedure. Join the OSI-Neuroscience mailing list to ask our customers about details of implantation.
[26-FEB-19] Our electrode leads are a flexible helix of stainless steel wire insulated in silicone. We describe how we arrived at this design in Flexible Wires. We make the following varieties of lead. You may specify which lead you want when you order transmitters, or you can leave it to us to choose the best diameter for your target animal.
|Outer Diameter (mm)||Spring Diameter (μm)||Wire Diameter (μm)||Resistance (Ω/cm)||Names||Common Application|
|B||0.7±0.1||450||100||6.3||Thin Lead||45-mm leads for mice,
100-mm leads for rat pups,
150-mm leads for adult rats
|C||0.5±0.1||250||50||25||Very Thin Lead||35-mm leads for mouse pups,
45-mm leads for mice 50-mm leads for rat pups
|D||0.8±0.1||500||150||1.6||Stimulator Lead||150-mm lamp leads for adult rats|
We order our springs in 150-mm sections, which makes it easy to manufacture leads up to 150 mm long. We make longer leads by joining two 150-mm leads together and insulating the join with silicone (see video). We use the C-Leads (0.5-mm diameter) with our smallest transmitters, those with volume less than 1.0 ml such as the T, P, and S series devices. We use the B-Leads (0.7-mm diameter) with transmitters larger than 1.0 ml. The wire in the A-Lead (1.0-mm diameter) is the same as the wire in the 0.7-mm lead, but the A-Lead, being larger is more likely to irritate the animal. When we reduced the diameter of our leads from 1.0 mm to 0.7 mm, we noticed a sharp drop in the number of reports we received of skin irritation around the implanted wires. The 0.5-mm lead is half the volume of the 0.7-mm lead, which is important in the smallest animals. But the wire in the 0.5-mm lead is one half the diameter of the wire in the 0.7-mm lead, so the spring itself is one quarter as strong. The 0.5-mm leads must be handled with care. They will survive the fatigue of animal movement, but they are easy to damage with a scalpel during implantation or extraction.
[31-JAN-21] We make three type of antenna: 50-mm loop, 30-mm loop, and 13-mm helix. We use the 50-mm loop in rat transmitters, the 30-mm loop in mouse transmitters, and the 13-mm helix in pup transmitters. The loop antennas are made of stranded steel wire. The loop antennas are tough and efficient. The helical antenna is made of a steel spring. It is small and flexible, but less efficient. We specify the Antenna with a letter code in the transmitter part number.
|A||50||Stranded steel loop antenna, for rats.|
|B||30||Stranded steel loop antenna, for mice.|
|C||13||Straight antenna of helical wire, for pups.|
[02-MAR-18] The antenna connection is marked OUT on the schematic. The antenna transmits the values of X and Y with 7-μs bursts of 902-928 MHz radio waves. The power transmitted during these bursts is roughly 300 μW (−5 dBm). The receiving antenna, which is usually a Loop Antenna (A3015C) connected to an Octal Data Receiver (A3027), must pick up at least 25 pW (−76 dBm) to overcome noise in the receiving antenna amplifiers, and at least four times (12 dB) more than the 902-928 MHz interference power picked up by the receive antenna. In our office, interference power ranges from 100 pW to 100 nW. In order to guarantee reception outside a faraday enclosure, we must receive 1 μW (−30 dBm). Inside an FE2F faraday enclosure, which offers at least ×1000 (30 dB) isolation from interference, we must receive 1 nW (−60 dBm).
We compared (see here and here) the 50-mm and 30-mm antennas moving in air and water with a self-propelled sphere. We found that the 30-mm antenna performed just as well as the 50-mm in water, and almost as well in air. Given that an animal body is more closely approximated by water than air, we conclude that, when implanted, the 30-mm loop will perform almost as well as the 50-mm loop. When we immerse an A3028E with 50-mm antenna in water, the radio-frequency power it emits remains constant to within a factor of two as we half-immerse it in water, completely immerse it in water, or press it up agains the wall of a water-filled beaker. The center-frequency of its transmission increases by 1 MHz from air to total immersion in water. The dielectric constant of water is ninety times greater than that of air. Water affects the propagation of radio waves along the antenna, slowing them down, so that the effective length of the antenna is greater. The water also affects the oscillator within the transmitter circuit, changing its resonant frequency. When we immerse an A3028A with 30-mm antenna in water, the power it emits rises by a factor of ten (10 dB) and the center-frequency rises by 2 MHz. The figure below is the power spectrum we measure when we hang an A3028A by its leads in air, then surround it with a beaker of water.
We make our helical antenna out of the same MDC13867A helical spring insulated with silicone that we use for EEG leads. We measured transmitted power versus antenna length in water and in air for these helical antennas by cutting back the antenna in stages. The graph below shows three plots: one for air, one for water with the tip of the antenna insulated from the water, and another in water with the tip of the antenna in contact with the water.
With the tip un-insulated, we are using the entire 50-ml beaker as an antenna. Even with a 0-mm antenna we get enough power. But if we drop the entire transmitter into the water, we get no power transmitted. We cannot use the entire animal body as an antenna because the body encloses our implanted transmitter. We must insulate the tip of the antenna. We perform similar experiments with the A3028P equipped with a helical antenna, cutting back the antenna and insulating its tip as we go. We obtain the best performance at the edge of a beaker of water with a 5-mm antenna. This 5-mm antenna contains 30-mm of wire. But the performance of the 5-mm antenna in air is so poor as to be impractical. We must be able to tell if the transmitter is on or off before we put it on the shelf. We settle upon 13 mm as the best compromise between air, water, and implanted.
[05-JAN-19] The following plot shows reception from seven A3028P2 devices with 13-mm helical antennas implanted in mice living in an IVC rack with isolation chamber.
Average reception is 97%. Short drops to 80% or below are shared by all seven devices, suggesting that the curtains of the chamber were open for cage cleaning and animal feeding.
[29-MAR-16] We calibrate the A3028 center frequency to lie in the range 913-918 MHz at room temperature, which is around 22°C. The MAX2624 oscillator that provides the radio-frequency signal has a temperature coefficient of −0.2 MHz/°C. In an animal body at 37°C, the center frequency will drop to 910-915 MHz. Our Octal Data Receivers (A3027) and the older Data Receiver (A3018) are designed to provide reliable message reception in for center frequencies in the range 908-918 MHz. The spectrum of the entire signal spans a ±5 MHz range about the center.
The following files define the A3028 design. Note that we distribute all these files under the GNU Public License.S3028A_1.gif: 2×0.3-160 Hz, A3028AV1 and A3028AV2.
The A3028 provides two amplifiers for recording two channels of EEG, or simultaneous EEG/EMG recording. The photographs below shows the A3028HV1, the latest in a series of similar circuits, each of which provides a slight improvement upon the last in terms of reliability, noise, or current consumption.
The A3028HV1's circuit board is black. Previous versions of the A3028 circuit were red, blue, and green. The A3028PV1 is the most recent and only pup transmitter assembly, as shown below.
Thew A3028PV1's circuit board is red, and a notch to accommodate side-mounting of a coin cell. The A3028T, A3028P and A3028S transmitters made with this circuit board are long and thin rather than short and fat.
We purchase boards fully-loaded with parts from our assembly house. We change various capacitors and resistors to create new versions of the assembly. The table below shows how we can modify the A3028HV1 assembly to create all versions of the A3028 other than the J, P and T versions. We modify only those components that are necessary for the new version to function correctly.
|Version||C7||C8||C9, C10, C11||C12||C13||C14, C15, C16|
|A3028F||same||same||510 pF||same||same||510 pF|
|A3028L||same||same||510 pF||same||same||510 pF|
|A3028M||same||same||240 pF||same||same||240 pF|
|A3028Q||same||same||510 pF||same||same||510 pF|
|A3028U||1.0 kΩ||620 kΩ||same||1.0 kΩ||620 kΩ||1.0 nF|
|A3028V||same||same||same||same||100 nF||240 pF|
The following table gives modifications to the A3028PV1 assembly to create the A3028P and A3028T series of devices.
|Version||C7||C8||C9, C10, C11|
|A3028S1Z||1.0 kΩ||620 kΩ||same|
|A3028S2Z||1.0 kΩ||620 kΩ||2.0 nF|
|A3028S3Z||1.0 kΩ||620 kΩ||1.0 nF|
The most complex modification of all is that required by the A3028J, which is a combined EEG/EMG transmitter that has four input leads. We start with the two-channel A3028HV1 circuit. We leave the X amplifier intact, but modify the Y amplifier on the see top side of the board. We remove C13, C14, and C16. We replace C12, R12, R13, and C15 with 2.0 MΩ. We replace R15 with 100 nF. We replace R16 and R18 with 50 kΩ. We load 510 pF in parallel with R17. We solder the a green Y− lead to the pad of the C13 footprint that is nearest to C12. The result is the S3028J differential amplifier, in which output Y is equal to 31 × (Y+ − Y−) with bandwidth 3-200 Hz.
[05-FEB-20] Dual-channel versions of the A3028 have three input leads named X, Y, and C. They are red, yellow, and blue respectively. All three inputs are marked on the S3028F schematic. Single-channel versions of the A3028 we obtain by omitting either the red or the yellow lead. The A3028P provides one input channel only. Its inputs are X and C, as shown in the A3028P schematic.
|X||X positive input||Connected to VC by 100 nF in series with 10 MΩ.|
|Y||Y positive input||Connected to VC by 100 nF in series with 10 MΩ.|
|C||shared negative input||Connected directly to VC|
|OUT||radio-frequency antenna||flexible steel antenna|
Rechargeable version of the A3038 provide access to their batteries through the X and C leads. Diodes permit current to enter X and leave through C. The input impedance of the X input remains 10 MΩ.
|X||X positive input||Connected to VC by 100 nF in series with 10 MΩ, connected to VBAT by diode.|
|Y||Y positive input||Connected to VC by 100 nF in series with 10 MΩ.|
|C||shared negative input||Connected directly to VC, connected to 0V by diode.|
|OUT||radio-frequency antenna||flexible steel antenna|
The A3028's on-board amplifiers and filters take the X and Y inputs and produce the XA and YA signals. The gain of the A3028A amplifiers is ×100, while Its high-pass filter provides a cut-off frequency of 0.3 Hz, and its low-pass filter provides a cut-off frequency of 160-Hz. The gain of the A3028U amplifiers, on the other hand, is ×10, with no high-pass filter, and a 160-Hz low-pass filter. In all versions of the A3028, XA and YA are applied to a sixteen-bit analog-to-digital converter (16-Bit ADC). In the A3028A and A3028U, the ADC samples XA and YA alternately at 512 SPS per channel, for a combined sample rate of 1024 SPS. In the A3028B, sampling from YA is disabled, and XA is sampled at 512 SPS. In the A3028C, sampling from XA is disabled, while YA is produced by a 0.3-40 Hz filter sampled at 128 SPS.
The 16-bit ADC produces numerical values 0-65535, and these values are what we see plotted in the Recorder Instrument and Neuroarchiver Tool. A value of 0 for means XA = 0V, and 65535 means XA = VBAT. A fresh lithium battery, such as the BR1225 in the A3028A, provides VBAT = 2.8 V during the first day of operation. With amplifier gain ×100, each sixteen-bit count represents 435 nV at the amplifier input. In the last few hours of a transmitter's life, VBAT drops to 2.2 V, at which point one ADC count is 350 nV. For most of the life of the transmitter, however, the battery voltage will be just below 2.7 V. When working with the A3028A, we assume a conversion factor of 400 nV/cnt. When we set the range of our signal plot to 5000 counts, this will be close to 2.0 mV. A fresh lithium-polymer battery, such as the PP031012 in the A3028B-R, provides VBAT = 4.2 V when fully charged, and 3.0 V when almost exhausted. But for most of the battery's life, its voltage is close to 3.7 V. When working with the A3028B-R signal, we assume a conversion factor of 560 nV/cnt. Consult the version table for the conversion factors other versions.
In theory, the dynamic range of the A3028A is 2.7 V ÷ 100 = 27 mV. But in practice, the amplifier is not able to drive XA all the way up to VBAT nor all the way down to 0 V. The actual dynamic range is closer to 24 mV. We specify a dynamic range that is 90% of the range we get when we multiply the sixteen-bit count conversion factor by 65536. Thus for the A3028U, with conversion factor 4.1 μV/cnt, the dynamic range is 90% of 270 mV = 240 mV.
Most versions of the A3028 provide a DC-blocking capacitor at each input. These are C7 and C12 in the schematic. Together with input resistors R5 and R12, they each form a high-pass filters with time constant 1.0 s. There is another high-pass filter in each amplifier, consisting of R6/C8 for X and R13/C13 for Y. In most versions of the A3028, these provide a time constant 0.5 s. The figure below shows the theoretical step response of the A3028A inputs, and compares it to that of other devices we have manufactured.
The common-mode reference voltage in the amplifier is VC, and VC is derived from the battery voltage by a 1.8-V regulator. Thus VC is 1.8 V, and the average value of both XA and YA are also 1.8 V. Thus the average digital value of X and Y correspond to 1.8 V. This allows us to calculate the battery voltage from the average value of either channel. We have VBAT = 65535 / Xave × 1.8 V, where Xave is the average value of X. This relation applies to all versions of the A3028, and both inputs, regardless of the gain and frequency response of its amplifiers, and regardless of what battery we have installed.
The figure below shows the X signal from an un-encapsulated A3028E as we reduce VBAT from 4.2 V to 1.2 V over 300 s. Our formula for VBAT from the average value of X works down to VBAT = 1.9 V. After that, the X decreases, suggesting an increase in VBAT, when in fact the actual VBAT drops to 1.8 V and the transmitter turns off.
The analog input impedance of X and Y is 10 MΩ in the pass-band of the amplifier. Most versions of the A3028 provide a high-pass filter at 0.3 Hz to remove slowly-varying electrochemical potentials so that the gain of the amplifier can be ×100 and the dynamic range is the battery voltage divided by 100. For non-rechargeable devices, the battery voltage is 2.7 V for most of the operating life of the device, so the dynamic range is 27 mA. The A3028U amplifier, however operates all the way down to 0.0 Hz and accommodates electrochemical potentials by reducing the amplifier gain to ×10 so that the input dynamic range is 270 mV.
We set the cut-off frequency of the A3028 three-pole, 3-dB ripple, Chebyshev, low-pass filters by our choice of filter capacitance, CF. Most often, we set the cut-off frequency at one third the sample rate. There are three capacitors in each filter that must have the same value for the filter to function properly. They are C9, C10, and C11 for the X filter and C14, C15, and C16 for the Y filter. With CF = 1.0 nF, the cut-off frequency is 160 Hz. The following graph shows how the gain of the two inputs of an A3028A varies with frequency.
The frequency response in the pass-band shows a slight decrease in gain from 10 Hz to 80 Hz, followed by a bump up at 130 Hz. These two features are the 3-dB ripple of the three-pole Chebyshev filter. By tolerating this non-uniformity of gain in the pass-band, we obtain a far sharper cut-off at the top of the pass-band. Amplitude drops by a factor of ten, or 20 dB from 160 Hz to 256 Hz. Frequencies above 256 Hz when sampled at 512 SPS will produce artificial sin-waves of lower frequency, in a process called aliasing. The purpose of our low-pass filter is to prevent aliasing. Even with the sharp cut-off of our Chebyshev filter, we might still see aliasing of high frequency components in EEG.
The plot above shows how 10-mVpp of 500 Hz applied to the X input of an A3028A would appear after low-pass filtering and sampling. The signal has an apparant frequency of 12 Hz, which is 512 − 500. The EEG signal power decreases with frequency, so we can place our cut-off frequency at one third the sample rate and be confident we will see no significant distortion due to aliasing. The same is not true of EMG, in which the signal power density reaches a maximum somewhere between 100-300 Hz. When we record EMG at 512 SPS, we recommend placing the cut-off frequency at one sixth the sample rate, so that all EMG components above half the sample rate will be eliminated by the low-pass filter. The A3028J provides a 0.3-160 Hz EEG input and a separate differential 3-200 Hz EMG input, both sampled at 512 SPS.
We expect some variation between amplifiers, because the three-pole filter is sensitive to the exact component values. The plot below shows the frequency response of a batch of fourteen A3028E transmitters stimulated with a 30-mV sinusoid through a 20 MΩ resistor.
At 10 Hz, the fourteen channels agree to within ±0.5 dB. At 130 Hz, where we have the bump in the Chebyshev response, they agree to within ±1 dB. These variations are well within the range we expect with 5% capacitors and 1% resistors.
An A3028 with two inputs, such as the A3028A or A3028D, provides two separated amplifiers for the X and Y signals. Both these signals use the same reference electrode C, which we call the common input. When we apply a signal to X, we would like Y to be unaffected. That is to say: when Y is connected to C, we would like the recorded value of Y to be zero regardless of the voltage we apply to X. We define the crosstalk from X to Y as the amplitude of Y divided by the amplitude of X when Y is connected to C. The crosstalk from Y to X we define in a similar manner. The crosstalk in the A3028 circuit is less than 2% and varies with frequency.
The crosstalk reaches a maximum of 2% at 140 Hz, just below the cut-off frequency of the amplifiers. For 1-100 Hz, the crosstalk is 1%.
Aside: We have defined crosstalk in terms of a ratio of amplitudes, but it is more traditional to define it as a ratio of signal powers, or the ratio of the square of amplitudes, and then take the log to base ten and multiply by twenty to obtain the crosstalk in decibels. In these units, the A3028D crosstalk is −68 dB.
When we apply a pure sinusoidal waveform to the A3028, the sinusoid is amplified, filtered, digitized, transmitted, received, and recorded by the data receiver. The purpose of the A3028 is to provide high-fidelity EEG recordings, so we hope to see only a pure sinusoidal waveform emerge in the frequency spectrum of the recorded signal. We apply a 14-mVpp sinusoid of increasing frequency to the input of an A3028E-R transmitter. We measure the power of the recorded signal after subtracting its fundamental harmonic. This non-fundamental power is a combination of imperfection in the applied sinusoid, noise in the amplifier, and distortion in amplification and transmission of the signal. We divide the non-fundamental power by the total signal power to obtain a measure of the distortion of the sinusoid by the recording process.
For the scattered-sampling devices, distortion remains less than 1% in the 0.3-160 Hz pass-band of the A3028 amplifier. At 10 Hz and below, distortion is less than 0.01%. The distortion power for scattered-sampling devices has a white noise spectrum: it is not distortion of the original sinusoid, but noise added to the sinusoid by the power of the sinusoid. This noise is due to random variation in the sampling instants, which is a feature of the process by which A3028 transmitters avoid systematic collisions with other transmitters. We call it scattering noise. If we sample uniformly, we obtain the second plot shown above, in which distortion is less than 0.003%. With uniform sampling, the non-fundamental power is dominated by periodic signals that may be the result of distortion in the amplifier, or they may be imperfections in the signal produced by our function generator. The figures below show the spectrum of the non-fundamental power with uniform sampling.
Uniform sampling increases current consumption by 10% (for example, the A3028D with regular sampling consumes 152 μA, while the A3028D with scattered sampling consumes 135 μA). Given that scattering noise does not distort the shape of the fundamental sinusoid, and given the chaotic nature of most biopotential signals, there is no practical benefit in reducing the scatter noise below 1%, while there is a practical benefit to increasing operating life by 10%.
The A3028U provides a 200-mV dynamic range and 0.0-160 Hz bandwidth on both inputs. Its EEG amplifier gain is only ×10, compared to our usual ×100. The A3028S2Z provides a single 0.0-160Hz input. Despite their low gain, the sixteen-bit resolution of the samples permits high-fidelity recording of seizures.
The least significant bit of the 16-bit digitized samples is 4.1 μV for battery voltage 2.7 V. We enable uniform sampling for all A3028U devices. Total harmonic distortion remains less than 25 ppm (0.0025%) from 0.03 Hz to 160 Hz.
The A3028V provides two channels: one running at 496 SPS and 0.3-160 Hz, and one at 16 SPS and 30-640 Hz. The first is for normal EEG recording, the second is for EMG amplitude measurement. The Neuroarchiver will reconstruct the 496 SPS signal into a 512 SPS signal by filling in the missing samples using the previous sample values, and the result will be an EEG signal almost identical to the one we would obtain with 512 SPS. The Neuroarchiver will leave the 16 SPS signal as it is, provided you enter "16 512" for the default frequency in the Neuroarchiver configuration. The figure below shows the gain versus frequency of the EEG and EMG inputs. Our measurement of the EMG gain between 200-500 Hz is erratic because of aliasing noise produced by under-sampling a non-random periodic sinusoid. With a random EMG input, we expect no such error in our measurement of amplitude.
The figure below shows how the A3028E's 160-Hz low-pass filter responds to pulses applied to the X input.
The low-pass filter introduces the ringing after the pulse, which consists of three maxima and minima in damped harmonic oscillation after the pulse has ended. The figure below shows the response of the A3028E to perforant pathway discharge spikes of amplitude roughly 10 mV.
The ringing we see after the discharge spikes is not generated by the brain itself, but rather by our low-pass filter. The slow, positive pulse following the negative spike is, however, produced by the brain, and the ringing is overlaid on top of this pulse.
[22-MAR-21] By input noise we mean the signal recorded by the transmitter when it is sitting stationary in water. The A3028 has three significant sources of input noise: soldered electrodes, its magnetic sensor, and its amplifier input. If we use bare wire electrodes, we eliminate the first source. If we choose the correct battery, we eliminate the second source. The figure below shows the noise spectrum of twelve A3028B-AA-B45-B transmitters sitting in 37°C water. Total noise in the band 0.3-160 Hz for these devices is 4-6 μV rms.
If we make the same device with an inferior choice of battery, we see noise generated by the circuit's magnetic switch. The figure below shows the noise spectrum of ten A3028B-AA-B45-B transmitters manufactured in FEB-18 with our original mouse-transmitter battery.
Currently, we make our P and S version transmitters with the A3028PV1 circuit and all others with the A3028HV1. Both are equipped with a magnetic sensor that turns itself on and off at 5 Hz. Switching noise, if preswent, will appear as a fundamental at 5 Hz accompanied by strong harmonics all the way up to 100 Hz. Provided we use the correct battery with either circuit
Maximum total noise in 0.5-40 Hz for these A3028P1 devices is 3.5 μV rms. We see no sign of switching noise either, althoug we certainly do see switching noise when we equip this same circuit with the BR1225 battery.
[21-AUG-18] The total noise on each input in the plot above is 5±1 μV rms. The peaks near 20 Hz, along with their harmonics at 40 Hz and 60 Hz, are generated by the magnetic sensor on the A3028GV1 circuit board. This sensor turns itself on and off at roughly 20 Hz. We call these peaks switching noise. The switching noise amplitude is the amplitude of the largest harmonic of the switching frequency. In the above signal, the largest harmonic is the fundamental harmonic, and its amplitude is 3.2 μV. When we present measurements of input noise, we specify the version of the A3028 electronic circuit, the battery loaded on the circuit, and the type of electrode at the end of the leads. The electronic circuit has evolved over the years, and the noise it generates has slowly reduced. The lower the source resistance of the battery, the lower the noise. Electrodes with solder joints generate low-frequency noise.
Switching noise is proportional to the battery's source resistance. The magnetic sensor switches itself on and off to reduce its current consumption. It draws current when it is on, and this current causes a potential drop across the source resistance of the battery. The battery voltage on the board contains bursts of noise at the magnetic sensor switching frequency, and this noise makes its way into the amplifiers. Of all the batteries we use with our transmitters, the BR1225 has the highest source resistance and produces the highest switching noise amplitude. The figure below compares the source resistance of various batteries. We find that lithium primary cells have higher resistance when they are fresh, so we discharge them by 0.1% before measuring their source resistance.
Earlier versions of the A3028B-AA circuit suffered from switching noise up to 12 μV, which was visible in the Fourier transform of 32-second intervals of baseline mouse EEG. The A3028GV1 circuit reduced switching noise by increasing the decoupling capacitance in parallel with the battery by a factor of four. Now we reject any
[28-MAY-19] When we equip the A3028 with gold-plated pin electrodes, we solder these pins to the ends of the stainless steel electrical leads. When we immerse these soler joints in water, they generate electrical potentials that we call chemical artifact, as we discuss in Chemical Artifact. Most of the power in chemical artifact is below 0.3 Hz, but the amplitude of the artifact above 0.3 Hz can be hundreds of microvolts. Our quality control procedure for each batch of transmitters is to soak them in water at room temperature for three days, remove them, measure their frequency response, and put them into water at 37°C to measure input noise. When we put transmitters with soldered electrodes into water, we first scrub their solder joints with a brush, which greatly reduces the chemical artifact. When they are first immersed, we see input noise of 10-50 μV rms in the range 2.0-160 Hz. After a few minutes, the noise drops to below 12 μV rms. When we immerse a batch of transmitters with bare wire electrodes, the input noise is immediately less than 12 μV rms, and after a few minutes is less than 8 μV rms.
[11-MAR-14] The A3028 leads pick up radio-frequency power from the antenna. If the C lead is left open-circuit and the X and Y leads are connected to some solid body, the C lead acts like an antenna. The radio-frequency power it picks up is demodulated by parasitic diodes in the EEG amplifier. The result is noise visible on the EEG, as shown below. Its amplitude is roughly 100 μV rms. If you see such noise in an implanted transmitter, your C lead has a broken conductor.
[07-JUN-19] Here's how we can check if a wire is broken inside the silicone insulation of one of the leads. We put the ends of the leads in water, on top of an antenna, turn the transmitter on and examine its signal in the Neuroarchiver Tool or Recorder Instrument. If the leads are intact, the amplitude of the noise on the signal should be less than 20 μV rms.
[01-DEC-16] We take a two-channel A3028D made with the A3028RV1 circuit and BR2330 battery and put it in water at 40°C. We use 8-s recording intervals to measure the amplitude and frequency of the switching noise in each of the two input channels No3 and No4 as the water cooled to 19°C.
The frequency of the switching noise increases with temperature. We perform the same experiment with four transmitters at once, using this processor to calculate the rms amplitude of the fundamental harmonic of the switching noise. Each transmitter is made with the A3028RV1 circuit, but we have two different types of battery.
In No13/14 the noise is far greater in X than in Y. But in No10 the noise is as large as any we have seen, and appears on the Y input. The noise in the transmitter equipped with the larger, lower-resistance BR2330 battery is an order of magnitude smaller. We touch the tip of a ×1 probe to the package of the Hall Effect Switch on a battery-powered, un-encapsulated transmitter. We see no sign of 20 Hz, certainly less than 200 μV.
[21-MAR-21] Loading the CR1225AH onto the A3028HV1 circuit results in no observable switching noise in the encapsulated transmitters. Total noise is never greater than 6 μV in 1-160 Hz with bare wire electrodes.
Suppose we want to know the root mean square amplitude of a biometric signal, or the mean square amplitude, but we do not need to know its exact shape. When we monitor electromyography (EMG), our chief interest may be the power of the signal, to determine if an animal is awake or asleep, rather than examining the fluctuations in the signal itself.
As we mention above, when we try to represent a continuous, time-varying signal as a sequence of discrete samples, we must make sure that the variation in the time-varying signal between the sample points approximates a straight line. When we plot the sampled signal, we are going to display it by drawing straight lines between the samples, so these straight lines are supposed to represent what the signal actually did between the samples. If the signal varies greatly between samples, we will not see this variation. Failing to see rapid variations between samples may not concern us, but rapid variations can, through sampling, look like much slower variations when we join the samples with lines. If we sample a 100-Hz signal at 48 SPS, for example, our straight-line reconstruction of the signal will be a 2-Hz sinusoid. This generation of slow variation from rapid variation is aliasing. To avoid aliasing, we must filter the signal we want to sample so that it contains no changes of direction between sample points. With a perfect low-pass filter, which has gain 1.0 up to frequency fc and 0.0 above fc, we can sample at 2fc and avoid aliasing. In practice, low-pass filters are not perfect, and avoiding aliasing is not quite sufficient to provide adequate representation. In the A3028, we sample at 3.2fc. Our low-pass filter gain drops by a factor of 10 from fc to 1.6fc. For example, in our 512 SPS transmitter for EEG, we filter at 160 Hz. The filter gain drops by a factor of ten from 160 Hz to 256 Hz.
But aliasing does not change the power of a signal, not unless we somehow miss all the powerful moments of a signal by a spectacularly unfortunate choice of sample instants. For an irregular signal like EMG, sampling at 16 SPS and taking the standard deviation of the samples, will give us a good measure of the EMG signal amplitude. Most EMG power is in the range 40-300 Hz, so we can high-pass filter at 30 Hz and low-pass filter at 320 Hz to separate the EMG from any artifacts that may be generated by our EMG pick-up electrodes, sample at 16 SPS and obtain EMG power at a cost of only 1.8 μA in current consumption. Thus the A3028V monitors EMG on Y and EEG on X and has the same battery life as the single-channel A3028B EEG monitor.
For a discusion of body capacitance, see Body Capacitance in the A3019 manual.
[24-JAN-21] The A3028 can run down its battery sitting on the shelf in its inactive state, sampling and transmitting signals in its active state, or some combination of both. The inactive current of the A3028 consists of the current consumption its magnetic sensor (U2) and its logic switch (U3). The shelf life of the transmitter is the time it takes the maximum inactive current to drain the battery. The maximum inactive current for −20°C to +80°C is 2.5 μA. The minimum shelf life of any A3028 equipped with a BR1225, 48 mA-hr non-rechargeable battery is 800 days. If we leave such a device inactive on the shelf for 400 days, at least half of its battery capacity will remain. At room temperature, in dry air, the inactive current consumption of A3028 devices is a fraction of the maximum.
|Used in These Versions||Use Period|
|A3028GV1||1.4||All except P, T, S||NOV-17 to JAN-21|
|A3028PV1||0.8||P, T, S||FEB-18 to present|
|A3028HV1||0.8||All except P, T, S||JAN-21 to present|
Average current consumption of the A3028P1 transmitter, for example, is 0.8 μA, while its battery is a 30-mAhr lithium primary cell, so its shelf life is 37500 hr = 1560 days = 52 months. Transmitters equipped with larger batteries have shelf lives of ten years or more, so we can leave them inactive for six months, and lose less than five percent of their operating life.
Rechargeable versions of the A3028 may be recharged to full capacity whenever they are not implanted. We connect the X and C leads to a recharging circuit and wait until the recharge is complete. We describe how we recharge transmitter batteries in our Battery Recharger (A3033) manual. Or we invite you to send your devices back to us for recharging, testing, and lead repair. You will find the cost of such services on our price list.
The active current of the A3028 is its current consumption in the active state. This current depends upon the number of samples the transmitter takes per second. The A3028B provides one channel with 512 SPS. The active current consists of the quiescent current of the logic chip, which is independent of sample rate, and the consumption of the sample and transmit process, which increases linearly with sample rate. The figure below shows active current versus the total sample rate. To obtain the total sample rate, we add the sample rates of both channels.
The linear trend fitted to the data provides us with the following empirical formula for typical active current, Ia, as a function of the total sample rate, R for our latest circuits.
The active current increases with battery voltage, so the current consumption of the A3028E-R, equipped with a 3.7-V LiPo battery, is 10% greater than that of the A3028E, equipped with a 2.7-V Li primary cell.
The capacity of lithium primary cells decreases with operating current and increases with temperature, as shown in the following plot taken from the BR1225 data sheet.
The above plot suggests that a BR1225 battery delivering 250 μA at 15°C will provide 44 mAhr, or 176 hrs operation. Under these conditions, however, we observe closer to 190 mAhr, which implies the full 48 mAhr capacity. All coin cell battery data sheets strongly discourage soldering directly to the battery. With care, however, we are able to solder directly to lithium primary coin cells without reducing their capacity, as we discuss here.
The operating life of the transmitter is the time it takes the active current to exhaust a fresh battery. As the battery is exhausted, the average value of the analog inputs increases, like this. The A3028B single-channel, mouse-sized transmitter has nominal battery capacity 48 mA-hr. According to the above formula, its typical active current is 77 μA. Its typical operating life is 620 hrs. We guarantee an operating life of 90% of its typical operating life, which for the A3028B is 560 hrs.
Some transmitters implement a uniform sampling interval to reduce total harmonic distortion. These transmitters consume more current. The A3028U, for example, provides uniform sampling at 1024 SPS and consumes 144 μA, while the A3028D provides scattered sampling at 1024 SPS and consumes 134 μA. To determine the current consumption of a transmitter with uniform sampling, we use:
The capacity of rechargeable batteries decreases with repeated drain and re-charge cycles. A lithium-polymer (LiPo) battery drained to 5% of capacity and recharged to 95% will endure a hundred charge cycles before its capacity has dropped to 90% of its initial value. A LiPo battery drained even once to 0% will immediately lose 50% of its initial capacity. We drained several manganese-lithium (ML) batteries to 0% and were unable to observe any loss of capacity afterwards.
Charging a magnesium-lithium battery is simple: connect it to a fixed voltage through a series resistor. We charged ours with voltages 2.9-3.3 V with a series resistor of 400 Ω. We recorded battery voltage as the battery discharged through a transmitter. The batteries take 24 hours to charge to 90% capacity and 48 hours to charge to 100%. Charging to 2.9 V gives 90% the capacity of charging to 3.3 V. We see no significant degredation of capacity over ten discharge cycles. Because of accumulated damage to their leads and encapsulation, we do not expect a transmitter to survive more than a ten implantations.
We discharge LiPo batteries through transmitters over several months. The plots above show how the battery voltage, as reported by the average value of the X input, declines with time. We have one 190-mHr battery with a connector, one new 190-mAhr battery with a connector, and one 190-mAhr battery encapsulated with a transmitter circuit. The encapsulated battery had been poached at 60°C for several months. The 190-mAhr battery with connector delivered 150 mAhr when discharged at 150 μA and 156 mAhr when discharged at 520 μA. The encapsulated 190-mAhr battery delivered 190 mAhr when discahrged at 90 μA. The 19-mAhr battery delivered between 19-21 mAhr when drained at 40-280 μA. We conclude that poaching an encapsulated battery does not reduce its capacity below nominal. We note that some batteries can deliver only 80% of their nominal capacity, while others can deliver 110%.
Batteries are vulnerable to heat. Lithium polymer batteries operate well at 60°C, but we find their capacity reduced by 50% at 80°C. Lithium primary cells operate well at 80°C, but they can suffer damge if we heat them with a soldering iron. Whenever possible, we use batteries with tabs, and we solder the tabs to our circuit board, rather than heating up the battery directly with a soldering iron and attaching a wire to the battery housing. In some devices, however, we solder directly to the battery housing, and in that case we must be careful which battery we use. Panasonic CR-series batteries delivered full capacity after soldering with an iron at 350°C (650F). We do not have to be quick when soldering Panasonic CR-series batteries: five seconds of heating causes no degradation in battery capacity. When we try CR-series batteries from two other manufacturers, we find that soldering with a 350°C (650F) iron for five seconds reduces their capacity by more than 50%. Rechargeable ML-series batteries suffer damage with a one-second application of 350°C (650F). With a 260°C (500F) iron we are able to solder directly to ML-series batteries, provided we are quick about it. If we take more than a three seconds, the battery is likely to fail. The same goes for the BR-series: a 350°C iron damages a BR-series battery, but 260°C it can tolerate for short periods. If we are not quick enough with the soldering, we will see the plastic seal bulging out between the terminals, which is a sure sign of damage and reduced capacity. We never to solder directly to ML or BR-series batteries, but use them only with tabs or a battery holder. When we solder CR-series batteries to a circuit baord, we make sure we get them Panasonic, and we do so quickly with acid flux and our iron at 350°C (650F).
[29-JUN-18] When an A3028 is equipped with a rechargeable battery, we recharge the battery after explantation. We deliver the charging current through the X and C leads. Re-implanting requires that we either clean cement off the ends of our leads, or cut back the leads to release them from the cement of the head fixture. In either case we are going to have to expose fresh wire for the next implant. We use this fresh wire to make contact with the charging circuit. We provide recharging instructions in our Battery Recharger (A3033) manual. We provide battery charger circuits for some of our rechargeable transmitters, which will make it easier for you to recharge your own devices. You may also send your exhausted transmitters back to us and we will recharge them for you, as well astest the leads for damage to the silicone insulation, and check the gain and frequency response. We can repair or replaced damaged leads. Our recharging and repair services are included in our price list.
[07-DEC-18] We run down the batteries of three A3028T1 rechargeable transmitters four times. These devices are equipped with the ML621 Manganese-Lithium Batteries, with nominal capacity 5 mA-hr. The current consumption of the A3028T1 128 SPS transmitter is 33±2 μA, so we expect the lifetime of the battery to be at least 140 hours.
The first discharge of each battery provides the longest life. Charging with 4.3 V gives greater capacity than charging with 4.1 V. But all discharges give us more than our expected 140-hr life.
[30-JAN-18] We encapsulate the A3028 in black epoxy and silicone. The outer layer of silicone is MED-6607, an unrestricted medical-grade silicone. The sensor leads are stainless steel springs coated with dyed silicone. The antenna is either a stranded stainless-steel wire coated with silicone, or a short sensor lead in the case of the smallest transmitter versions. We remove one in ten transmitters from our production line for accelerated aging. These transmitters run until they exhaust their batteries while fully immersed in water at 60°C or 80°C.
Corrosion causes the failures of electronic circuits in warm, humid environments. Both silicone and epoxy are permeable to water vapor. An implanted transmitter encapsulation becomes saturated with water vapor. Occasional drops in temperature cause condensation in any cavities that may exist within the transmitter, such as within a cracked ceramic capacitor or beneath a surface-mount component. Condensed water, the warmth of the animal body, flux residue, and electrical voltages combine to promote corrosion that leads initially to loss of performance in the EEG amplifier and ultimately to premature draining of the battery. At 60°C, corrosion occurs over ten times faster than at 37°C in an animal body.
We guarantee our transmitters against failure from corrosion while implanted. Our encapsulation procedure seeks to remove flux residue by repeated washing and scrubbing in hot water, and to eliminate cavities in the epoxy by use of vacuum and atmospheric pressure. The minimum operating life of an encapsulated A3028RV3 circuit in 100% humidity at 60°C is 100 days, with the first artifacts of corrosion appearing in the EEG signal after 50 days. Implanted in an animal, we expect no sign of corrosion in the EEG for 500 days, and no failure through corrosion for 1000 days. None of the popular versions of the A3028A run for 500 days. The A3028GV1 circuit we have just introduced for use in mouse transmitters. We poached ten devices at 80°C. Two stopped transmitting after 6 days, which is equivalent to 360 days implanted, and the remaining 8 lasted 13-14 days, which is their full operating life, and equivalent to 780 days implanted. Looking at our notes we find that we did not clean these circuits a second time before encapsulating, so we suspect the two early failures were caused by flux residue and moisture. But in any case, none of our mouse transmitters run for more than 100 days implanted, so we have no fear that these will fail prematurely by corrosion.
We have moved our development to a separate page, Subcutaneous Transmitter Development.