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Publication numberUS3466742 A
Publication typeGrant
Publication dateSep 16, 1969
Filing dateJan 30, 1967
Priority dateJan 30, 1967
Publication numberUS 3466742 A, US 3466742A, US-A-3466742, US3466742 A, US3466742A
InventorsSinclair John C
Original AssigneeUniv Iowa Res Found
Export CitationBiBTeX, EndNote, RefMan
External Links: USPTO, USPTO Assignment, Espacenet
Process of forming an electrical cable for chronic implantation within a living body
US 3466742 A
Abstract  available in
Previous page
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Claims  available in
Description  (OCR text may contain errors)

Sept. 16, 1969 J. c. SINCLAIR 3,466,742

PROCESS OF FORMING AN ELECTRICAL CABLE FOR CHRONIC IMPLANTATION WITHIN A LIVING BODY Filed Jan. 30. 1967 METRIC Z United States Patent US. Cl. 29592 6 Claims ABSTRACT OF THE DISCLOSURE The disclosure relates to a process for forming a product particularly adapted for the chronic implantation thereof within a living body, human or animal, for the transmission thereby of electrical current in response to a temperature change of the body, the product being made innocuous to the body tissues while being flexresistant in order to endure constant movement of the body organs.

Background of the invention The invention relates to the field of flexible conduits or cables capable of transmitting electric current, said cables adapted for implantation in living tissues for measuring coronary blood flow.

Methods used to measure coronary blood fiow include fiowmeters of various kinds; the uptake and disappearance of nitrous oxide or radioactive tracers, cyclic movement of various foreign substances, and differential pressure recordings. The electromagnetic and ultrasonic flowrneters are the only ones deemed suitable at the present for chronic implantation. Both the latter flowrneters have been found to disturb the blood flow pattern; the electromagnetic flowmeter surrounding the blood vessel by insulating material, and with the pickup electrodes requiring electrostatic shielding due to stray capacitance.

The ultrasonic flowmeter is lightweight and simple but requires very complex electronic instrumentation.

Cables used for chronic implantation of these devices into living tissues were thoroughly checked with one manufactured under the Dow Corning Corp. name found to be good. However, other than being more expensive than applicants cable, the Dow cable for example was not sufiiciently resistive to the permeation thereof of moisture, nor did it completely obviate interference with body functions, both non-permeation and non-interference being requirements of applicants cables.

Summary of the invention This invention relates generally to the electrical arts and more particularly to a blood flowmeter or electric stimulating device suitable for implantation within a living body.

The recent microminiaturization of electronic components has made it possible to chronically implant fiow transducers within the animal body. Implanting a transducer inside an artery, however, requires that such a device he made so small and so compliant that it does not obstruct the blood circulation or significantly disturb laminar blood flow. It must also be made innocuous to the body tissues while being flex-resistant in order to endure the constant movement of the body organs.

Accordingly, it is an object of this invention to provide a blood flowmeter device capable of withstanding the above stated forces indefinitely.

It is another object of our invention to provide an electrical cable suitable for chronic implantation within ice a human body, said cable capable of placing a flow transducer within the blood stream for measuring coronary blood flow.

It is yet another object of this invention to provide an electrical cable capable of carrying an electrical impulse to the muscle of the heart when connected to a pacemaker.

Still another object of our invention is to develop a process for making a flowmeter device that is capable of carrying through the named objectives.

Another object of our invention is to provide a process for producing an electrical cable which will be permanently flex-resistant.

It is still another object of this invention to provide a flowmeter device which is economical to manufacture, extremely compact and functional in use, and simple but rugged in construction.

The foregoing and other objects, advantages and characterizing features of our invention will become clearly apparent from the ensuing detailed description taken in conjunction with the accompanying drawings.

Brief description of the drawings FIG. 1 is a plan view of our invention and showing the bottom of the skin connector;

FIG. 2 is a greatly enlarged view of the probe and cable of this invention in relation to a metric ruler;

FIG. 3 is an enlarged cross sectional view of the cable taken along the line 33 in FIG. 2;

FIG. 4 is also an enlarged view showing the probe in relation to the head of an ordinary straight pin; and

FIG. 5 is an exploded perspective view of the Skin connector elements.

Description of the preferred embodiment The thermistor flowmeter device as shown generally in FIG. 1 is composed of three parts. The probe 11 (FIG. 2) that is inserted into the artery, the cable 12 that acts as an electrical conduit, and the skin connector 13 that permits the device to be attached to an external recorder (not shown).

The cable 12 is made by coiling a double strand of platinum alloy wire, such as platinum alloy wire #851, 2.2 mil, class H insulation, Sigmund Cohn Corp., Mount Vernon, N.Y., into a coil about 1 mm. in diameter with commercially available apparatus of any known type. Two five-foot lengths of wire are used for an eighteen inch cable 12. The coils 14 and 16 are rinsed in isopropyl alcohol and blotted. They are then dipped in 4120 primer, such as Primer #SS-4120, General Electric, Waterford, N.Y., and drained. The coils are suspended vertically in three mm. glass tubing which has been coated with silicone. A deaerated potting compound 17 (FIG. 2) is slowly injected or sucked into the tube with a syringe so as to avoid trapping bubbles. Silicone tubing, such as Vivosil, Medical grade, Becton, Dickinson and Company, Rutherford, N.J., is used with the syringe.

The plotting compound 17 is allowed to solidify overnight and is then placed in the oven for thirty minutes. This and all subsequent heat treatments are done in an oven preheated to C. If the glass tubing is previously coated inside with a thin film of potting compound 17, the cable can be cured immediately in a steam jacket or oven. One must use caution because the glass will shatter. The shattered glass is removed and the cable remaining is then rinsed in water. One end of the wires at one end of the cable 12 is straightened and dip-coated with varnish, such as Sylgard #1377, Dow Corning Corp., Midland, Mich, and the baked for two hours.

To make the probe 11, the straightened wires are cut to thirteen and twenty-two mm. lengths 18 and 19 (FIG. 4) respectively, stripped of insulation at the tips, and

3 tinned with solder with the help of flux, such as Duzall, All-State Welding Alloys Co., Inc., White Plains, N.Y. The soldering is done with a drop of solder on the tip of a magnetic soldering iron of commercial availability. The solder is kept just above its melting point by adjusting the line voltage with a voltage regulator. The surface of the solder is cleansed with a thread before each use. These and all subsequent manipulations are accomplished under a dissecting microscope.

The thermistor 21, such as Veco Micro-Bead #42A402C, Victory Engineering Corp, Springfield, N.I., has a lead Wire 15 one end of which is joined to the end of the cable Wire 18 by being wrapped several times thereabout, and with the joint 22 being tied by a suture strand. The joint 22 is then etched with flux and soldered, with the soldered joint etched with flux, cleaned with xylene, coated with varnish, and baked for one hour.

The cable wires 18 and 19 are tied together, also at joint 22, and then the thermistor lead wire 15 is wound around the longer cable wire 19, with the outer end thereof joined and tied to the outer end of wire 19 as at 23. The second joint 23 is then etched, cleaned, coated and baked as described relative to the first joint 22. Additional ties are made where necessary, with all ties made with a strand taken from a two cm. piece of Vetafil suture, a product of Dr. S. Jackson, Washington, DC.

The entire probe tip 11 is then dipped in 4004 primer, such as Primer #SS-4004, General Electric, Waterford, N.Y., and baked for fifteen minutes. The probe tip 11 is then dipped in a 50:50 mixture of dry xylene and silastic, such as Medical adhesive #891, Dow Corning Corp., Midland, Mich. The probe 11 is then air dried for one hour and baked for one additional hour. The probe 11 is then dip-coated with potting compound 24, identical to the compound 17, and baked for thirty minutes. The

probe 11 is again coated with xylene and silastic mixture, then again baked for thirty minutes.

The skin connector 13 (FIGS. 1 and is made by fitting a stainless steel flange 26 around a chassis connector 27 (FIG. 5). The cable 12 and a five cm. length of bare silver wire 28 are soldered to the connector 27. The silver wire 28 acts as a ground wire. The flange 26 and connector 27 base are then coated with a plotting compound such as 17, and silastic to waterproof and insulate the connector 13 as a unit.

The thermistor flowmeter device is then ready for testing. It can be sterilized for surgery by placing it in the oven for two hours, and can also be chemically sterilized.

Calibration of the thermistor 21 is accomplished on a rotating drum (not shown) approximately ten cm. in diameter. The thermistor probe tip 11 was rigidly held three mm. from the edge of the drum and about twelve mm. below the surface of the fluid. The fluid used was sucrose by weight and 0.4% sodium chloride. The viscosity of this fluid at C. is approximately that of blood plasma (1.7 centipoises). Changes in voltage across the recorder, such as Grass Polygraph, Model 5, Grass Instruments, Quincy, Mass., bridge circuit with changes in DC. current at a constant flow rate were used to calculate AR/AI. The bridge circuit had 20K ohm, 1% resistors in the base of each arm. The thermistor arm was balanced with a 25K ohm potentiometer on the other arm. The current source was a 9-volt battery in parallel with a 50K ohm potentiometer used as a gain control. The changes in voltage with changes in flow rate at forty p.21. of current were used to calculate AR/AF. The voltage is a log function of the flow rate.

The insulation of the device was tested in the same fluid with a one volt square wave taken from the calibrating circuit of the oscilloscope, such as Oscilloscope #502, Tektronix, Inc., Portland, Oreg. A wire from the calibration jack was immersed in the fluid. If the square Wave was picked up by the probe, it was rejected. The time constant was calculated from the rise time of one of the fast transients seen when the rotating drum is suddenly stopped. One such spike was considered to be one-half of an idealized sine wave.

It is known that a thermistor such as 21 is a semiconductor material with a large temperature coeflicient. An increase in temperature greatly increases the density of current carriers and so lowers the resistance. Its total resistance as used here is a function of the nominal resistance, the current flowing through it, the temperature of the blood, and the velocity of blood flow. Forty a. of current will raise the temperature of the 20K ohm thermistor about 0.6 C. above body temperature. The resistance will drop about 3.9% for each 1 C. rise in temperature. A flow signal of l mv. represents an increase in resistance of about 50 ohms. The flow velocity determines how rapidly heat is removed from the surface of the thermistor, and thus how effectively the thermistor is cooled by the blood.

A flowmeter which lies inside the blood stream poses certain unique problems. It is more apt to disturb the flow it is supposed to measure, both by the heat it dissipates and by its physical size; it may be inactivated by blood clots or tissue overgrowth; and its response may be distorted by the pulsating blood flow.

It has been shown theoretically that at present, exact mathematical calculation of the forces exerted on a body immersed in a streaming fluid is impossible even in the case of steady flow. In the range of high Reynolds numbers, friction must be considered, for the force exerted on the body is due to a thin boundary layer of fluid (Prandtls theory). Within this layer, the velocity gradient perpendicular to the body surface is very high and is a function of the viscosity. The boundary layer is stable up to Reynolds numbers of about 900 (Reynolds number: velocity radius density/viscosity). In pulsatile flow the blood is nonhomogenous and Reynolds numbers vary from zero to several thousand. Under these conditions, the response of the thermistor will be unpredictable.

The thermistor flowmeter device 10 has certain advantages over other implantable flowmeters. Its response is an indication of instantaneous flow rates at the surface of the probe. There are no intervening tissue layers or averaging elfects to mask or distort the fiow signal. It uses simple circuitry and is free of ECG or magnetic field artifacts. It can also record temperature gradients and so can be used as a measure of cardiac output by thermal dilution methods.

The probe 11 of the device 10 which is placed inside the artery must be so small, strong, and flexible that the use of a platinum alloy wire is mandatory. Considering this requirement, the fabrication of the device 10 and its reuse are facilitated by using this same wire for the cable 12. The diameter of the probe wire is chosen to with stand the manipulations of implantation. The compliance of the probe 11 in turn fixes the minimum compliance that can be tolerated in the cable 12. It is necessary for the maximum flexibility of the cable 12 to choose a wire coil that matches the compliance of the cured potting compound. The coil can be made more flexible by increasing the diameter of the coil, using a smaller wire, or by including more loops per unit length. It is usually desirable to keep the overall size of the cable 12 as small as possible. A cable one mm. in diameter is quite strong and can be made very flexible by the above considerations.

If one wishes to avoid the necessity of aligning the coils 14 and 16 inside the glass tubing, the inside of the tubing can be coated with a thin film of potting com pound and cured before the wire coils are inserted. Alternatively, the cable 12 can be dip-coated with silastic or potting compound after it is removed from the glass tubing. Any low viscosity silicone resin that is waterproof and is a good insulator can be used as a potting compound. A suture can be tied close to each end of the coils 14 and 16 to prevent the wire from pulling out of the cable 12 during the fabrication of the device. A few millimeters of braiding would serve the same purpose, but would hinder the reuse of the cable 12.

The most difficult part of the fabrication is the coating of the tip 11. Various materials (varnish, primers, silastic, and potting compound) were tried in all conceivable combinations. It was learned that the potting compound 17 and the silastic would bond to themselves and to one another, if the undercoat was properly primed and cured. The combination of materials finally adopted gives a probe 11 which is flexible and waterproof.

Four dogs and thirteen pigs were implanted to learn what sort of probe design and technique of implantation were best. The connectors were attached to the skull with screws at first, but the neck flexing pulled the probes out of the artery. It was also diflicult to maintain aseptic conditions when the cables were threaded under the skin to the skull. Septic conditions could rapidly destroy the silicone elastic cable. Insulated stainless steel wire Was used in the beginning, but the cable lasted only a few days before breaks occurred in it. The coils of fine, insulated, platinum alloy wire embedded in silicone rubber were entirely satisfactory. Cables made in this way could be removed intact after several months in the animal. Several of the connector and cable assemblies were used over again after the thermistor probe was repaired.

The longest survival of a functional probe was three weeks. The device itself was intact but the intraarterial probe was partially walled off with endothelium. This walling-off process can be well along after only one day, if the probe is digging or rubbing against the endothelium. Hence, the probe inside the artery needs to be relatively long and flexible, though this kind is very difiicult to implant without damaging it. Suturing the probe base firmly to the wall of the artery helps to keep the probe from rubbing against the endothelium.

Several of the implanted tips 11 were found to have perforated the coronary artery twice. If the thermistor could be centered with .a diagonal double perforation, so that the tip 11 protrudes from the underside of the artery, this could be one way of staying in the center of the lumen. The motion of the heart during surgery, however, makes it impossible to achieve this. The field of view is also obstructed by the loss of blood during the time that the channeled needle is in place. Another way of centering the device is by placing flexible bristles on the tip of the probe 11 like the spokes of a Wheel. These bristles would also tend to anchor the tip in place and help prevent it from pulling out during surgery. Centering would minimize any mechanical artifacts due to the motion of the heart and the arterial pulse. It would also retard an endothelial overgrowth of the tip 11 and would thus prolong its useful life. An electric zero fiow could be determined by using a reference thermistor implanted near the spine where is would be shielded from mechanical motion and thermal gradients due to muscle contraction, respiration, or blood flow. Occluding the artery would not give a true zero flow.

The fabrication of a chronically implantable thermistor flowmeter device has been described hereinbefore. It has an effective time constant of 0.02 second. It is suitable for the measurement of intra-arterial coronary blood flow transients in the quiet, unanesthetized pig. It consists of a probe 11 that projects into the lumen of the artery, a skin connector 13 for external recording, and a flexible silicone elastic cable 12 that acts as an electrical conduit. This device can remain intact in the animal body for several weeks but the probe 11 may become ensheathed with endothelium. The operative procedures are also very difiicult. There are uncertainties relative to vasomotor changes at the site of implantation and to the position of the thermistor 21 within the velocity profile across the diameter of the vessel. Thus no knowledge of absolute flow rate is possible, but it should be proportional to the flow as it has been measured here. Hence,

6 any conclusion drawn from these relative changes in blood flow should be valid.

Although a specific embodiment and process for making the thermistor flowmeter device of this invention have been described hereinbefore, the invention is not to be so limited as various alterations and modifications can be made to both the product and the process without departing from the true and intended spirit and scope of the invention, as defined in the appended claims.

I claim:

1. The process of forming an electrical cable for the chronic animal implantation of an electronic device, comprising the steps:

coiling a double strand of insulated platinum alloy wire;

suspending the coiled wire vertically in a glass tube coated internally with silicone;

filling the tube with a potting compound until the coiled wire is completely surrounded with said compound; solidifying said potting compound by curing same while said tube is in a vertical position;

heating the tube for a predetermined time until the glass shatters;

removing the glass from the cured compound;

straightening the ends of the coiled wire at one end thereof;

sealing the straightened ends of said coil; and

heating the sealed ends of said coil for a predetermined time.

2. The process of forming an electrical cable as defined in claim 1, and further wherein the coiled wire is rinsed in isopropyl alcohol, blotted, and dipped in a primer, drained, and air dried before being suspended in said tube.

3. The process of forming an electrical cable as defined in claim 2, and further wherein the potting compound is slowly injected into said tube in a manner obviating the trapping of air bubbles therein.

4. The process of forming an electrical cable as defined in claim 1, and further wherein a miniature electronic device having at least two leads is secured in an intertwined manner to said sealed ends of said coil as by soldering;

the intertwined ends are dipped in a primer and heated for a predetermined time;

the intertwined ends are dipped in a mixture of dry xylene and silastic, air dried and again being heated; the intertwined ends are dipped in a potting compound and heated; and

the intertwined ends are again coated in an xylene and silastic mixture, and again heated.

5. The process of forming an electrical cable as defined in claim 4, and further wherein the free ends of the coiled wire opposite the sealed ends to which the electronic device is secured are soldered to a skin connector;

a ground wire is soldered to said connector;

a stainless steel flange is fitted around the connector;


said connector and flange are waterproofed and insulated.

6. The process of forming an electrical cable as defined in claim 5, and further wherein all heating is performed in an oven pre-heated to approximately C.;

said tube is heated for approximately 30 minutes;

the juncture of said device to the said one sealed end and the juncture of said intertwined free ends are both tied by a suture, etched with flux, cleaned with xylene, coated with varnish, and baked for one hour;

the intertwined ends, dipped in said primer are heated for 15 minutes;

the intertwined ends dipped in said xylene and silastic mixture are air dried for one hour and heated for one hour;

the intertwined ends dipped in the potting compound 3,224,436 12/1965 Le Massena 128-21 are heated for 30 minutes; and 3,249,103 5/1966 Woodhouse 128-2.1 the intertwined ends dipped for a second time in said mixture are heated for 30 minutes. JOHN F. CAMPBELL, Primary Exammer References Cited 5 ROBERT W. CHURCH, Asslstant Exammer UNITED STATES PATENTS US. Cl. X.R.

2,217,734 10/1940 Dreyfus. 29-610, 624, 629; 128-2.1, 418; 264-272 2,280,074 4/ 1942 Halsall.

Patent Citations
Cited PatentFiling datePublication dateApplicantTitle
US2217734 *Jan 21, 1936Oct 15, 1940Dreyfus CamilleMethod of making shaped articles containing organic derivatives of cellulose
US2280074 *Feb 17, 1941Apr 21, 1942Toyad CorpManufacture of hollow articles
US3224436 *Apr 10, 1961Dec 21, 1965Honeywell Regulator CoHypodermic apparatus for measuring hydrogen ion concentration of blood within a living body
US3249103 *Jan 21, 1963May 3, 1966Charles F WoodhouseMethod and apparatus for measuring bioelectronic parameters
Referenced by
Citing PatentFiling datePublication dateApplicantTitle
US3596662 *Sep 4, 1968Aug 3, 1971Medtronic IncElectrode for cardiac stimulator
US3731376 *Jan 22, 1971May 8, 1973Electro Catheter CorpMethod of making a catheter
US4369795 *Jun 17, 1980Jan 25, 1983Bicher James IImplantable microthermocouple member
US5120313 *Mar 20, 1990Jun 9, 1992Nancy W. ElftmanMethod for measuring blood pressure in an animal or human using a percutaneous access port
US5174299 *Aug 12, 1991Dec 29, 1992Cardiac Pacemakers, Inc.Thermocouple-based blood flow sensor
EP0004667A1 *Apr 5, 1979Oct 17, 1979Precimed S.A.Cardiac probe
EP0091577A1 *Mar 22, 1983Oct 19, 1983Kunke, Stefan, for the determination of the position of a probe
WO1981003607A1 *Jun 17, 1981Dec 24, 1981J BicherImplantable microthermocouple member
U.S. Classification29/592.1, 600/505, 29/610.1
International ClassificationH01B7/04, A61N1/375, H01B13/06, A61B5/07
Cooperative ClassificationA61B5/07, H01B13/06, A61N1/375
European ClassificationA61B5/07, A61N1/375