|Publication number||US3659588 A|
|Publication date||May 2, 1972|
|Filing date||Apr 8, 1970|
|Priority date||Apr 8, 1970|
|Publication number||US 3659588 A, US 3659588A, US-A-3659588, US3659588 A, US3659588A|
|Inventors||Alan R Kahn, Florence A Stroebel|
|Original Assignee||Medtronic Inc|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (5), Referenced by (33), Classifications (26)|
|External Links: USPTO, USPTO Assignment, Espacenet|
1 United States Pat ent Kahn et al. [4 1 May 2, 1972 54] CATHETER APPARATUS 3,473,087 10/1969 Slade ..317/2 R 3 166,688 1/1965 Rowand et al. ..317/2 R 72 Inventors. Alan R. Kuhn, Morrest wn, Florence A. 1 8mm. Maple Shade a of Ni 3,428,046 2/1969 Remer et al ..128/349 R  Assignee: Medtronic, Inc., Minneapolis, Minn. F REIGN PATENTS OR APPLICATIONS  Filed: Apr. 8, 1970 1,033,971 6/1966 Great Britain ..128/348 Appl' 26697 Primary Examiner-Dalton L. Truluck Attorney-Lew Schwartz and Donald R. Stone  US. Cl ..l28/2 R, l28/2.05 R, 128/348,
138/118, 317/2 R  ABSTRACT  Int. Cl ..A6lb 05/02, A61m 25/00 58 Field of Search ..128/2.05 R, 2.05 D, 2.06 R, A catheter having walls of which at least a Portion is electril28/2.06 E, 2, 348-351; 138/1 18; 317/2 R cally conductive and has an electrical resistivity approximately equal to the electrical resistivity of blood.  References Cited 7 Claims, 5 Drawing Figures UNITED STATES PATENTS Sheridan ..128/348 X Patented May 2, 1972 m m V m ALAN 2 K411,
izaezwcz' A 6720x821 CATHETER APPARATUS BACKGROUND OF THE INVENTION This invention is concerned with an improved catheter. Catheters constructed as hollow tubes are well known in the art for their use in the practice of medicine as well as in medical research. Catheters are used, for example, to measure pressures in body organs and in the circulatory system, to withdraw samples of body fluids, and to introduce drugs, intravenous fluids, X-ray contrast media, dyes for cardiac output measurements, and nasogastric feeding.
In performing functions such as those mentioned above, the catheter or tube is normally filled with solutions which are electrically conductive. In many of these applications, one end of the catheter terminates inside the body in close proximity to the heart while the other end is attached to an electrical device or electronic instrumentation. As the catheter is normally made of an electrically insulating material, the solution within the catheter acts as an isolated circuit for electrical current into the body, and close proximity to the heart causes the possibility of accidental death due to accidentally applied electrical power which will be felt near the heart and may cause ventricular fibrillation.
The above-mentioned danger is now well known to those skilled in the art, and various studies are being conducted to overcome the problem. The apparatus of the present invention does overcome the problem by providing a catheter having a conductive wall so that electrical current is disbursed through the blood and body tissues rather than being concentrated at or near the heart.
SUMMARY OF THE INVENTION Briefly described, the apparatus of this invention comprises a tube having walls at least a portion of which is electrically conductive or semiconductive material and has an electrical resistivity sufficient to prevent harmful current flow to organs within the body when the tube is used as a catheter for intracorporeal applications.
IN THE DRAWINGS FIG. 1a is a representation of the catheter apparatus of this invention;
FIG. 1b is a representation of the apparatus of this'invention as it is in the process of being assembled;
FIG. 2 is a schematicized drawing representative of the current density pattern in the body of a human being between a pair of skin electrodes;
FIG. 3 is a schematicized drawing of the current density pattern between a prior art intravascular catheter anda skin electrode; and
FIG. 4 is a schematicized diagram of the current density pattern between an intravascular catheter of this invention and a skin electrode.
BRIEF DESCRIPTION OF THE PREFERRED EMBODIMENT Resistance (ohms) Xarea (cm?) which equations is knownto those skilled in theart.
Referring to FIG. la, it should 'be' understood that the catheter-apparatusof this invention comprises ahollow tube Rho (ohm-em.)
or catheter with electrically conductive or'semiconductive walls l4-which have electrical resistivity. The catheter apparatus must be durable and preferably flexible. In FIG. lb,
there is shown in the stage of construction a catheter of this invention 10 which is being made by winding a base material 11, such as a Dacron mesh, around a rod 12, preferably a stainless steel rod.
The apparatus of this invention has been made by first coating rod 12 with wax and then cutting a base material 11, such as Dacron or nylon mesh, into 3-foot long strips, 1 centimeter wide. Mesh 11 is then wound on rod 12 in a helical pattern with overlapping windings. A solution is then applied to the base material 11 in sufficient quantities to flow through the base material, the solution being one which will harden into a durable, flexible, electrically conductive or semiconductive coating when cured. The solution is then cured, and when dry, further coatings are applied and dried as necessary to form walls 14. A solution which has been used in the preferred embodiment of the apparatus of this invention is a flexible carbon impregnated elastomer, known as Eccocoat No. 258, which has a measured volume resistivity of about 133.5 ohm-cm. This material wasthinned out with a solvent and painted on the base material 11, using enough solvent to cause the material to flow through mesh 11. It was than dried in a 150 F. oven for 15 minutes. A second coat was then painted on using a thicker solution of the material than in the previous step, and it was again dried in the oven. Two further coats of the material were added as in the latter step. The completed catheter was then removed from rod 12. This catheter, comprising the apparatus of this invention, was tested in a manner to be more fully described below. Other materials which could be used to fabricate the apparatus of this invention include carbon-filled polyethylene, carbon-filled polyvinylchloride, carbon-filled rubber, and carbon-filled silicones. Catheters can also be fabricated from such materials alone without the need for the mesh base as described previously.
To best understand the operation of the apparatus of this invention, reference should be made to FIGS. 2, 3, and 4 of the drawings.
As stated above, electrical shock hazards resulting from defective medical electrical equipment are well known in the art. It is common knowledge that cycle alternating current greater than 100 milliamperes can be dangerous when flowing through the human body between two points on the body surface. The heart tissue is most susceptible'to such current, and electrocution deaths are most commonly the result of ventricular fibrillation of the heart.
Over the past decade, an increased awareness of the susceptibility of the heart to 60 cycle alternating electrical currents has been developed. When a current flows between two points on the surface of the body, it is distributed more or less unifomtly throughout the tissues, and the density of current at any single point deep inside the body is comparatively small. This may be seen by reference to FIG. 2, where a body 15 has placed thereon a pair of electrodes 16 and 17 between which is flowing a current indicated by current density lines 20. A review of the current density lines will indicate that when electrical current flows through the body from two points on or near the body surface, the current becomes distributed more or less uniformly in the body blood and tissues, and the current density at anyone point inside the body, such as th heart, is relatively small.
The heart is highly sensitive to 60 cycle alternating current, and currents as low as 10 to 20 microamperes can cause fibrillation when injected over 1 square millimeter of heart muscle. However, to. generate 10 microamperes per square millimeter of current density at the heart surface from electrical contact on either arm, such as electrodes 16 and 17 on body 15 of FIG. 2, it is necessary to provide a current flow of milliamvperes. This is because the current is effectively disbursed through-the volume of the blood and tissues in the body.
However, when a catheter containing electrically conductive liquid is introduced near the heart, the current density situation issignificantly altered. In 'FIG. 3, there is again shown body 15 and electrode 16, but the current density lines 21 nowiindicate theflow of current between electrode 16 and an intravascular catheter 18 here shown to be a prior art hollow catheter having a nonconductive wall.
As can be seen in FIG. 3, catheter 18 terminates within the heart, and because of the conductive effect of the solution or liquid within catheter l8, virtually all of the current passing through catheter 18 exits at a small area near the heart muscle. That is, the current density at the end of the catheter is sufficiently great so that as little as 20 microamperes of current can be lethal. Such small currents can result from many accidental causes. For example, if the catheter is connected to a grounded pressure transducer or fluid injector, as is often the case, a small electrical potential introduced at any point on the body can be dangerous. As a specific example, a nurse who may adjust a properly functioning bedlamp having an exposed metal part which is not grounded can kill the patient by simply touching him.
It is, therefore, desirable that the walls of the catheter or at least a portion thereof be of a conductive material so that electrical currents impressed on the catheter may pass through the catheter walls into the body and be disbursed to avoid density at the heart. If the walls of the catheter are substantially better electrical conductors than the surrounding blood and tissue, then the electrical current will pass out uniformly into the blood and tissue along the length of the catheter. However, if the catheter walls are highly conductive along its length as well as through its walls, it will provide a low impedance between the source of power and the heart and be even more dangerous than the above-mentioned prior art catheter because very low voltages can generate high currents. Obviously then, a highly conductive catheter is even more dangerous than a highly insulated catheter.
The catheter of the apparatus of this invention is selected to have a conductive or semiconductive surface with an electrical resistivity approximately in the range from 12 to 1,200 ohm-centimeters, preferably approximately equal to the electrical resistivity of blood, 120 ohm-centimeters. That is, the catheter apparatus of this invention has a wall with at least a portion having an electrical resistivity of one-tenth to times the electrical resistivity of blood.
Referring now to FIG. 4, there is again shown the body 15 and electrode 16 and a plurality of current density lines 22 flowing between electrode 16 and an intravascular catheter 10 comprised of the apparatus of this invention. In FIG. 4, it is apparent that the current begins to disburse at the site at which catheter 10 penetrates the skin of body 15. Thus, the pattern of dispersion is similar to that which would be present if the catheter 10 were not used and the current were injected from a surface electrode such as 17 in FIG. 2. It has been proven by experimentation that greatly increased currents can be applied without causing ventricular fibrillation of the heart when the apparatus of this invention, as shown in FIGS. 1a, 1b, and 4, is used in place of prior art catheters.
From the above, and with reference to FIG. 4, it will be apparent that catheter 10 need not be electrically conductive or semiconductive along its entire length, but that it must include a part of its wall which is conductive or semiconductive at the point adapted to be in contact with the skin after intracorporeal application of the improved catheter.
The improved catheter apparatus of this invention was built and tested in a live, intact dog under conditions normally present in human cardiac catheterization. Similar tests were performed on a conventional catheter normally used in human diagnostic cardiac studies, in this case a standard No. 7 Lehman cardiac catheter.
A catheter of the apparatus of this invention was passed to the right ventricle of the heart through the femoral vein and wedged between muscular trabeculations. The prior art catheter of identical length and intemal diameter was passed to the right ventricle through another femoral vein and also wedged between muscular trabeculations. Sixty cycle AC current was applied to the catheter of this invention beginning with 6 microamperes and increasing in 15 steps to 10,000 microamperes. Each current step was applied for 5 seconds.
Electrocardiogram and intraventricular pressures were monitored continuously. No effect on the heart was observed. At the 10,000 microamperes level, the animal's leg was seen to twitch where the catheter entered the skin. Results of this test are shown in Table I below.
The prior art catheter was then tested in a similar manner. However, when the current reached 70 microamperes, ventricular fibrillation of the heart occurred. The dog was restored immediately to normal sinus rhythm using DC cardioversion at 50 watt-seconds, in a manner known to those skilled in the art. It is also interesting to note that at 50 microamperes the dog began to have occasional ventricular premature beats. The results of this test are shown in Table II below. 1
TABLE II Prior Art Catheter Current-ua Time applied-sec. Response 6 5 none l2 5 none 17.5 5 none 22 5 none 34 5 none 50 5 Doc. VPBS" 70 5 Ventricular fibrillation (ventricular premature beats) The prior art catheter was withdrawn to the vena cava, and the catheter of this invention was repositioned in the right ventricle. The above-described test was repeated, and again, no cardiac disturbances were observed. Again, the 10,000 microamperes current produced leg twitching. Reference is made to Table III for the results of this test.
TABLE III Improved Catheter Apparatus Current-ua Time applied-sec. Response 6 5 none 23 5 none 5 none 240 5 none 740 5 none 1450 5 none 3000 5 none 5 none 5 none 7 8000 5 none 10,000 5 leg muscle twitch The catheter of this invention was then withdrawn to the vena cava, and the prior art catheter was repositioned in the right ventricle. The above test was again repeated, and again, the dog had ventricular fibrillation of the heart at 70 microamperes of input current. Cardioversion again restored normal sinus rhythm. The results of this test are shown in Table IV.
fibrillation The two sets of the last above two paragraphs were repeated in sequence, with the same results. However, when using the prior art catheter, the animal fibrillated at 50 microamperes but stopped after the current was turned ofi. When 70 microamperes was again reached, ventricular fibrillation occurred but was irreversible. The results of these further tests can be seen in Tables V and VI below.
TABLE V Improved Catheter Apparatus none I7 5 none 22 5 none 34 5 none 50 5 Ventricular fibrillation (Stopped after current turned 06) 70. 5 Ventricular fibrillation (Irreversible) From the above, it will be apparent that there is a great advantage in the use of a catheter having at least a portion of its walls electrically conductive or semiconductive and having an electrical resistivity which is comparable to that of the surrounding blood and tissues during an intracorporeal application to allow current flow throilfigh the walls into the blood and tissue, but to provide a sign [cant impedance between the source of current and the end of the inserted catheter. As explained above, this electrical resistivity lies approximately in the range of 12 to 1,200 ohm-centimeters, and is preferably approximately at the electrical resistivity of the surrounding blood and tissue.
It will be apparent that construction of the catheter of this invention can be other than that described above with respect to the preferred embodiment. For example, rings or strips of conductive material may be embedded in an insulative materi- 7 al, a portion rather than all of the catheter wall may be conductive, and in some cases only the portion of the catheter adapted to be adjacent to the skin during an intracorporeal application may be conductive.
What is claimed is:
1. Catheter apparatus comprising tubular means having walls, at least a portion of said walls being electrically conductive and having an electrical resistivity of approximately from 12 ohm-centimeters to 1,200 ohm-centimeters.
2. The apparatus of claim 1 in which all of said walls are electrically conductive and have an electrical resistivity of approximately from 12 ohm-centimeters to 1,200 ohm-centimeters.
3. The apparatus of claim 1 in which the electrical resistivity of said portion of said walls is approximately equal to the electrical resistivity of blood.
4. The apparatus of claim 3 in which the electrical resistivity of said portion of said walls is approximately from one-tenth to 10 times the electrical resistivity of blood.
5. The apparatus of claim 1 in which said portion of said walls comprises a part of said walls adapted to be adjacent to the skin of an animal during intracorporeal application of said catheter apparatus.
6. The apparatus of claim 1 in which said portion of said walls is electrically semiconductive.
7. Improved catheter apparatus comprising: tubular means defining a lumen for the passage of fluids into an animals body; and said means being electrically semiconductive and having a substantially uniform electrical resistivity selected in the range from approximately 12 ohm-centimeters to 1,200 ohm-centimeters.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3070132 *||Apr 6, 1960||Dec 25, 1962||Sheridan David S||Non-sparking medico-surgical tubes|
|US3166688 *||Nov 14, 1962||Jan 19, 1965||Ronald P Rowand||Polytetrafluoroethylene tubing having electrically conductive properties|
|US3428046 *||Apr 6, 1965||Feb 18, 1969||Vagenius Harold N||Catheter|
|US3473087 *||May 22, 1962||Oct 14, 1969||Raybestos Manhattan Inc||Electrically conductive polytetrafluoroethylene tubing|
|GB1033971A *||Title not available|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US3807391 *||Mar 23, 1973||Apr 30, 1974||Medical Plastics Inc||Cardiac catheter and shunt electrode|
|US4280507 *||Jun 27, 1979||Jul 28, 1981||Hewlett-Packard Company||Patient cable with distributed resistance protection in conductors|
|US4675780 *||Aug 26, 1985||Jun 23, 1987||The Gates Rubber Company||Conductive fiber hose|
|US4905698 *||Sep 13, 1988||Mar 6, 1990||Pharmacia Deltec Inc.||Method and apparatus for catheter location determination|
|US5498248 *||Mar 14, 1994||Mar 12, 1996||Implemed, Inc.||Iontophoretic structure for medical devices|
|US5584838 *||Feb 28, 1994||Dec 17, 1996||Stryker Corporation||Distal targeting system|
|US5584872 *||Mar 11, 1994||Dec 17, 1996||Scimed Life Systems, Inc.||Electrophysiology energy treatment devices and methods of use|
|US5645065 *||Apr 11, 1995||Jul 8, 1997||Navion Biomedical Corporation||Catheter depth, position and orientation location system|
|US5727553 *||Apr 3, 1996||Mar 17, 1998||Saad; Saad A.||Catheter with integral electromagnetic location identification device|
|US5741224 *||Apr 16, 1996||Apr 21, 1998||Implemed, Inc.||Iontophoretic material|
|US5759564 *||Apr 16, 1996||Jun 2, 1998||Implemed, Inc.||Iontophoretic material|
|US5902328 *||Nov 14, 1996||May 11, 1999||Scimed Life Systems, Inc.||Electrophysiology energy treatment device and method of use|
|US5944023 *||Oct 7, 1997||Aug 31, 1999||Sims Deltec, Inc.||Systems and methods for determining the location of an implanted device including a magnet|
|US6060000 *||Mar 9, 1998||May 9, 2000||Implemed, Inc.||Iontophoretic material containing carbon and metal granules|
|US6168594||Feb 9, 1999||Jan 2, 2001||Scimed Life Systems, Inc.||Electrophysiology RF energy treatment device|
|US6238340 *||May 19, 1998||May 29, 2001||Eckhard Alt||Composite materials for avoidance of unwanted radiation amplification|
|US6287484||Apr 8, 1999||Sep 11, 2001||Robert Hausslein||Iontophoretic material|
|US6450972 *||Jun 5, 1998||Sep 17, 2002||Meinhard Knoll||Sensor system for measuring pressure profiles|
|US6923805||Nov 14, 2000||Aug 2, 2005||Scimed Life Systems, Inc.||Electrophysiology energy treatment devices and methods of use|
|US7976518||Jan 13, 2005||Jul 12, 2011||Corpak Medsystems, Inc.||Tubing assembly and signal generator placement control device and method for use with catheter guidance systems|
|US8061307 *||Jan 22, 2009||Nov 22, 2011||Mark Anderson||Lick deterrent tubing|
|US8088078||Feb 17, 2003||Jan 3, 2012||Pp-Technologies Ag||Methods and apparatus for measuring pressure profiles|
|US8197494||Sep 8, 2006||Jun 12, 2012||Corpak Medsystems, Inc.||Medical device position guidance system with wireless connectivity between a noninvasive device and an invasive device|
|US9028441||Sep 7, 2012||May 12, 2015||Corpak Medsystems, Inc.||Apparatus and method used with guidance system for feeding and suctioning|
|US9131956||Jun 2, 2011||Sep 15, 2015||Corpak Medsystems, Inc.||Tubing assembly and signal generator placement control device and method for use with catheter guidance systems|
|US9579488||Sep 14, 2015||Feb 28, 2017||Corpak Medsystems, Inc.||Tubing assembly and signal generator placement control device and method for use with catheter guidance systems|
|US9687174||May 16, 2012||Jun 27, 2017||Corpak Medsystems, Inc.||Medical device position guidance system with wireless connectivity between a noninvasive and an invasive device|
|US20060116601 *||Feb 17, 2003||Jun 1, 2006||Raymond Glocker||Methods and apparatus for measuring pressure profiles|
|US20080097475 *||Sep 8, 2006||Apr 24, 2008||Viasys Holdings, Inc.||Medical device position guidance system with wireless connectivity between a noninvasive device and an invasive device|
|US20090188440 *||Jan 22, 2009||Jul 30, 2009||Mark Anderson||Lick deterrent tubing|
|US20090188443 *||Jan 28, 2009||Jul 30, 2009||Minick Chris A||Veterinary medical tubing removal deterrent technology|
|EP0134845A1 *||Sep 21, 1983||Mar 27, 1985||Walter Spaa||Safety catheter|
|WO2004071293A1 *||Feb 17, 2003||Aug 26, 2004||Pp-Technologies Ag||Methods and apparatus for measuring pressure profiles|
|U.S. Classification||600/301, 361/215, 128/908, 604/523, 600/433, 138/118, 174/47|
|International Classification||A61B5/042, A61N1/05, A61B5/0215, A61B5/0424, A61M25/00|
|Cooperative Classification||A61N1/056, Y10S128/908, A61B5/0424, A61M25/00, A61B5/0215, A61M25/005, A61B5/042, A61M25/0009|
|European Classification||A61N1/05N, A61B5/0215, A61B5/0424, A61M25/00G, A61M25/00, A61B5/042|