The Cooper cable: an implantable multiconductor cable for neurological prostheses

Donaldson, P. E. K.

doi:10.1007/bf02478508

Cited by 40 publications

(22 citation statements)

References 1 publication

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“…6). DONALDSON (1983) found that Cooper cable failed by wire fracture if the pulleys were 5 mm radius, as here, or by rubber failure, if the radius was 3 ram. The failure of cable 2 does not confound that result because this cable was subjected to dry running, which causes chafing where the cable rubs against itself at the top of the pulley.…”

Section: Noise Due To the Cablementioning

confidence: 90%

“…A cable testing machine was built, similar to that used originally (DONALDSON, 1983). Five cables were clamped at both ends in a tank of isotonic saline at room temperature.…”

Section: Methodsmentioning

confidence: 99%

“…The cables can tolerate flexion and stretching because of the helical form of the wires. The construction and the results of the original tests were described by DONALDSON (1983): in the flexion tests, the cable withstood 65 million flexions round a 5 mm radius pulley under saline and 40 million round a 3 mm pulley. The cable is often used with connectors (DONALDSON, 1985), and these can be used for connection once at operation or be 're-connectable' as part of a repair procedure (RUSHTON et al, 2002).…”

Section: Introductionmentioning

confidence: 99%

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Noise from implantable Cooper cable

Carrington

Zhang

Donaldson

2005

Med. Biol. Eng. Comput.

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Cooper cable is made for implanted devices, usually for connection to stimulating electrodes. An experiment has been performed to see whether these cables would be satisfactory for recording electroneurogram (ENG) signals from cuffs. Four cables were subjected to continuous flexion at 2 Hz while submerged in saline. The cables were connected to a low-noise amplifier, and the noise was measured using a spectrum analyser. These cables had not fractured after 184 million flexions, and the noise in the neural band (500-5000 Hz) had not increased owing to age. Noise in the ENG band increased by less than 3 dB owing to the motion. A fifth, worn cable did fail during the experiment, the conductors becoming exposed to the saline, but this was only apparent by extra noise when the cable was in motion. After 184 million flexions, the four cables were given a more severe test: instead of being connected to the amplifier reference node, two of the four cores of each cable were connected to 18V batteries. Two of the cables were then noisier, but only when in motion, presumably because of leakage between cores. Cooper cables are excellent for transmitting neural signals alone; transmission in one cable of neural signals and power supplies should be avoided if possible.

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Section: Noise Due To the Cablementioning

confidence: 90%

“…A cable testing machine was built, similar to that used originally (DONALDSON, 1983). Five cables were clamped at both ends in a tank of isotonic saline at room temperature.…”

Section: Methodsmentioning

confidence: 99%

Section: Introductionmentioning

confidence: 99%

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Noise from implantable Cooper cable

Carrington

Zhang

Donaldson

2005

Med. Biol. Eng. Comput.

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“…To implant IMDs in human body without complications, it has several critical requirements such as autoclavability, nontoxicity, biocompatibility and flexibility to shape freely to the change of patient's posture [1]. Furthermore, the IMDs should be safe, robust, and long-term operable without failure.…”

Section: Introductionmentioning

confidence: 99%

Flexible, stretchable and implantable PDMS encapsulated cable for implantable medical device

et al. 2011

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Purpose Diverse commercial implantable medical devices were developed for the convenience and life-quality of patients, and tether-free diagnostics and therapeutics. Those devices need implantable cable, which connects each part of their devices for transcutaneous energy or signal transfer. For prolonged implantation into human body, it should be safe, robust, and be long-term operable without failure. In this paper, we introduce an implantable PDMS-coated cable. Methods By using PDMS as an encapsulation material, we developed a biocompatible, flexible and durable cable. Several tests were carried out for the evaluation of cable performance. Leakage test confirmed that coating using PDMS was sufficient to prevent the invasion of body fluid to conducting wire. Tensile test, torsion-durability test and bending-durability test demonstrated its mechanical durability and robustness to motion. The resistance variation recorded in the durability test was monitored to verify the electrical stability during movement of cable. Experiments of subcutaneous tissue implantation for 8 weeks were performed to observe the degree of biocompatibility as an implantable cable.Results & conclusions Our cable was mechanically stable and biocompatible enough to be used for long term implantable medical devices.

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“…This is because available implantable multi-core cables were not intended to carry signals of this bandwidth and in this band they have significant resistance, inductance and capacitance. In this project a five core Cooper cable [19] was used, having a diameter of 2 mm and consisting of five helically wound cores of single strand platinum-iridium wire: this type of cable were designed to be small in diameter, very flexible and immune to fatigue (see photograph in Fig. 5).…”

Section: Introductionmentioning

confidence: 99%

An implanted system for multi-site nerve cuff-based ENG recording using velocity selectivity

Clarke

Rieger

et al. 2008

Analog Integr Circ Sig Process

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This paper describes the design of an implantable system for velocity-selective electroneurogram (ENG) recording. The system, which relies on the availability of multielectrode nerve cuffs (MECs) consists of two CMOS ASICs. One ASIC called the electrode unit (EU) is a mixed analogue/digital signal acquisition system which is mounted directly on an MEC in order to optimize the interface between the two. It is linked to the other ASIC by means of a 5-core cable through which it receives power and commands in addition to transmitting data. The second ASIC, called the monitoring unit (MU) manages the interface between the EUs (each MU can control up to three EUs) and an RF transcutaneous link to the external signal processor. The ASICs are fabricated in 0.8 lm CMOS technology. The EUs measure 3 mm 9 4 mm each and consume 105 mW (35 mW each), while the MU measures 1.5 mm 9 2 mm and consumes 4 mW. The power consumption on the communication channels (including cable losses) between the MU and EUs is 129 mW. A digital communication strategy between the two parts of the implanted system and the external controller is described.

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The Cooper cable: an implantable multiconductor cable for neurological prostheses

Cited by 40 publications

References 1 publication

Noise from implantable Cooper cable

Noise from implantable Cooper cable

Flexible, stretchable and implantable PDMS encapsulated cable for implantable medical device

An implanted system for multi-site nerve cuff-based ENG recording using velocity selectivity

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