|Publication number||WO1992008536 A1|
|Publication date||29 May 1992|
|Filing date||12 Jul 1991|
|Priority date||16 Nov 1990|
|Also published as||CA2072888A1, EP0511331A1, EP0511331A4|
|Publication number||PCT/1991/4938, PCT/US/1991/004938, PCT/US/1991/04938, PCT/US/91/004938, PCT/US/91/04938, PCT/US1991/004938, PCT/US1991/04938, PCT/US1991004938, PCT/US199104938, PCT/US91/004938, PCT/US91/04938, PCT/US91004938, PCT/US9104938, WO 1992/008536 A1, WO 1992008536 A1, WO 1992008536A1, WO 9208536 A1, WO 9208536A1, WO-A1-1992008536, WO-A1-9208536, WO1992/008536A1, WO1992008536 A1, WO1992008536A1, WO9208536 A1, WO9208536A1|
|Inventors||Steven Kaali, Peter M. Schwolsky|
|Applicant||Steven Kaali, Schwolsky Peter M|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (7), Referenced by (1), Classifications (10), Legal Events (7)|
|External Links: Patentscope, Espacenet|
TITLE: Electrically Conductive Methods and Systems For Treatment of Blood and Other Body Fluids and/or Synthetic Fluids With Electric Forces
FIELD OF INVENTION
This is a continuation-in-part application of prior United States patent application Serial No. 07/562,721 filed August 6, 1990.
This invention relates to novel
electrically conductive methods and systems employing electrically conductive vessels provided with electrically conductive surfaces for use in subjecting blood and/or other body fluids and/or synthetic fluids such as tissue culture medium to direct treatment by electric forces.
It is now well known in the medical profession and the general public that blood collected in a blood bank from a large number of donors may be contaminated by contaminants such as bacteria, virus, parasites or fungus obtained from even a single donor. While screening of donors has done much to alleviate this problem, the screening of donors can and does miss occasional donors whose blood is unfit for use. When this occurs and the unfit blood is mixed with otherwise usable blood, the entire batch must be discarded for transfusion purposes. Because of this problem, the present invention has been devised to attenuate any
bacteria, virus, parasites and/or fungus contained, in blood contributed by a donor to the point that any such contaminant is rendered ineffective for infecting a normally healthy human cell, but does not make the blood biologically unfit for use in humans. Similar problems exist with respect to the treatment of other body fluids, such as amniotic fluids. The treatment method and system is also applicable to mammals other than humans.
In addition to the above, there is a need for methods and systems for the treatment of blood and other body fluids both in in-situ processing wherein the treated blood and/or other body fluids are withdrawn from the body, treated and then returned to the body in a closed loop,
recirculating treatment process that is located near but outside the patient's body, or the
treatment can be effected through implanted
treatment system components.
SUMMARY OF INVENTION
The present invention provides new electrically conductive methods and systems for transferring blood or other body fluids, such as amniotic fluids, and/or synthetic fluids such as tissue culture medium from a donor to a transfusion recipient or to a storage receptacle, or for recirculating a single donor's blood or other body fluids through components of a treatment system external of the body or by implant devices for purging contaminants using a novel electrically conductive vessel for direct electric treatment of blood or other body fluids, such as amniotic fluids, with electric field forces of appropriate electric field strength to attenuate such
contaminants to the extent that bacteria, virus, or fungus, or parasites contained in the blood or other body fluids are rendered ineffective to infect or affect normally healthy human cells. The treatment, however, does not render the blood or other body fluids biologically unfit for use in humans or other mammals after the treatment. The new methods and systems according to the invention achieve these ends without requiring time consuming and expensive processing procedures and equipment in addition to those normally required in the handling of blood or other body fluids or synthetic fluids. The invention achieves the electric field force treatment during the normally occurring transfer processing from a donor to a recipient or to a collection receptacle, or recirculation of a single donor's blood or other body fluids, such as amniotic fluids.
BRIEF DESCRIPTION OF DRAWINGS
The above and many other objects, features and attendant advantages of this invention will be appreciated more readily as the invention becomes better understood from a reading of the following detailed description, when considered in connection with the accompanying drawings, wherein like parts in each of the several figures are identified by the same reference characters, and wherein:
Figure 1 is a diagrammatic, fragmentary, elevational view of a new blood transfer system using a novel electrically conductive treatment vessel in the form of conductive tubing to directly treat blood being transferred to a storage
receptacle with electric field forces according to the invention;
Figure 2 is an enlarged, horizontal cross sectional view of the novel electrically conductive tubing treatment vessel taken across lines 2-2 of Figure 1;
Figure 3 is a longitudinal, vertical sectional view of the novel electrically conductive tubing treatment vessel taken along the staggered section lines 3-3 of Figure 2;
Figure 4 is a view similar to Figure 2 showing a different construction of the novel electrically conductive tubing treatment vessel;
Figure 5 is a view similar to Figure 3, taken along the staggered section lines 5-5 of Figure 4;
Figure 6 is a diagrammatic, fragmentary, elevational view showing a different modification of a novel blood transfer system using the novel electrically conductive tubing treatment vessel, and which employs a blood pump and a blood flow regulator;
Figure 7 is an enlarged cross sectional view, similar to Figure 2 that shows an
electrically conductive tubing treatment vessel fabricated from longitudinally extending,
integrally molded strips of alternate polarity, conductive polymer interconnected by integrally molded, insulating, longitudinally extending strips made of polymer or other insulating material;
Figure 8 is a diagrammatic, fragmentary elevational view showing a different form of a blood transfer system according to the invention wherein a small electrically conductive vessel in the form of a short piece of tubing and a
miniaturized battery power source are implanted in the arm of a human being to provide a novel
electrically conductive blood and other body fluid treatment system which operates in a closed loop, recirculating manner;
Figure 9 is a partial, diagrammatic sectional view of the upper arm portion of a human being and shows in greater detail the construction of a specially designed miniaturized, electrically conductive treatment vessel with associated
miniaturized battery electric power source for use in the implant treatment system shown in Figure 8;
Figure 10 illustrates the details of construction of a somewhat different form of miniaturized electrified treatment tubing for use in an implanted treatment system of the type shown in Figure 8 and built according to the invention;
Figures 11 and 11A illustrate still a different construction for the electrified
treatment tubing for use in practicing the
invention wherein the tubing has a square or rectangular cross section with upper and lower conductive sides and intervening right and left sides separating the two conductive sides made from plastic or other suitable electrical insulating material;
Figure 12 is a perspective top and side view of a novel electrified, closed, octagonally- shaped, flat, box-like treatment vessel having an enlarged cross sectional area relative to the cross sectional diameter of the inlet and outlet tubes supplying the interior of the treatment vessel;
Figure 12A is a partial, cross sectional view of the enlarged treatment vessel shown in Figure 12;
Figure 13 is a perspective view of a second form of enlarged cross sectional area treatment vessel having an exterior shape similar to that of Figure 12, but wherein the electrically conductive electrodes of the treatment vessel comprise
interleaved conductive plates with one set of alternate ones of the plates being electrically insulated from the remaining set, and wherein different polarity electric potentials are applied to the respective sets. If desired, the electrode plates may be formed from an electrically
conductive porous material;
Figure 13A is a partial, cross sectional view taken through the electrically conductive treatment vessel shown in Figure 13;
Figure 14 is a longitudinal sectional view of still a different form of enlarged diameter electrified treatment vessel wherein the vessel is in the form of an elongated cylinder, and the sets of conductive electrodes mounted therein are concentrically arrayed within the interior of the treatment vessel and maintained at different electric potentials;
Figure 14A is a cross sectional view of Figure 14 taken through plane A-A;
Figure 15 is an enlarged longitudinal sectional view of still another form of an enlarged cross sectional area treatment vessel according to the invention wherein the electrically conductive electrodes of the treatment vessel are comprised by longitudinally extending needle-like electrodes with alternate ones of the needle-like electrodes being provided with opposite polarity electric potentials;
Figure 15A is a cross sectional view of the treatment vessel shown in Figure 15 taken through plane A-A of Figure 15;
Figure 16 is a perspective view of still another form of enlarged cross sectional area treatment vessel according to the invention wherein the treatment vessel comprises a relatively large block of insulating material having parallel, longitudinally extending, open ended tubes formed through its length. The tubes are provided with electrically separated, opposed, parallel extending conductive plate electrodes which have opposite polarity electric potentials applied thereto. The ends of the tubes open into and are supplied from, or supply, respective reservoirs formed on the respective ends of the central block of insulating material containing the tubes, with inlet and outlet conduits for body fluids to be treated connected to the free ends of the respective reservoirs;
Figure 17 is a perspective view of an enlarged cross sectional area treatment vessel similar to Figure 16 wherein the body of the treatment vessel is cylindrical in nature;
Figure 18 is a diagrammatic, fragmentary elevational view of a human blood or other body fluid treatment system according to the invention employing one of the larger cross sectional dimension fluid treatment vessels shown in any one of Figures 12-16 of the drawings, and which is suitable for use in a continuous flow through recirculating body fluid treatment system;
Figure 19 is a diagrammatic, fragmentary elevational view of still another human blood or other body fluid, closed loop, recirculating treatment system according to the invention designed for use with the enlarged diameter fluid treatment vessels illustrated in Figures 12-16, and which employs both inlet and outlet fluid pumps on each side of the treatment vessel. With this arrangement the system can be operated in an intermittent manner to allow batch treatment of the body fluids to fully take place before passage of the body fluids being treated back to the patient;
Figure 20 is a partially disassembled, perspective view of a non-flow through, single batch, body fluid treatment vessel according to the invention which is open to atmosphere on the upper side thereof to allow a clear view of the body fluids being treated during operation of the process; and
Figure 20A is a diagrammatic, fragmentary side view of an assembled, open sided, treatment vessel of the type shown in Figure 20 connected to a source of electric power. BEST MODE OF PRACTICING INVENTION
Figure 1 is a schematic illustration of one form of novel blood transfer system according to the invention. Figure 1 shows an electrically conductive blood treatment vessel constructed according to the invention which is in the form of intravenous-type tubing 11 interconnected between a hypodermic needle 12 and a blood storage receptacle 14. The needle 12 is inserted in an artery or vein of the arm 13 of a blood donor and the tubing 11 leads from the arm 13 to the receptacle 14.
Alternatively, the system could be set up to transfer blood from the storage receptacle 14 to the arm of a recipient or could be designed to recirculate the blood through electrified tubing 11 back to the donor. The electrically conductive tubing 11 may be of any desired length as indicated by the break at 15 so that it can be appropriately set up to lead from a comfortable position for the donor from whose arm 13 the blood is being taken to a proper storage location for the receptacle 14. The greater the length of the electrified portion of tubing 11, then the more extended is the
exposure of the blood (or other body fluid) to the electric field force effects and low level,
biologically compatible current flow through the body fluid being treated thereby assuring adequate electrification treatment of the fluid without impairing the biological usefulness of the blood or other body fluid being treated.
Figure 2 is a cross sectional view of the electrically conductive tubing 11 taken through plane 2-2 of Figure 1. The tubing 11 may be from 1 to about 20 millimeters in inside diameter,
although it may be larger or smaller in diameter depending upon the intended application. For example, if the blood transfer system is for the purpose shown in Figure 6, then the tubing may have a cross sectional dimension of about 5 millimeters. However, if the intended use is in an implanted blood transfer system as shown in Figure 8, then the tubing diameter must be designed to result in a flow-through rate corresponding to the natural circulatory blood flow rate of the patient in which the system is implanted, and must be long enough to assure effective electrification treatment at the flow rate selected. The tubing 11 is formed from plastic, rubber, medical grade polymer, or other suitable material which is compatible with human fluids and/or tissue. A plurality of physically separated, electrically conductive surface segments form opposed, parallel electrodes shown at 16 and 16A on the inside of tubing 11 from electrically conductive materials such as platinum, platinum alloys, silver, silver or platinum covered alloys, or other similar conductive materials such as conductive polymers, or silver or platinum covered polymers which are compatible with human fluids and tissue. The spacing between opposed electrodes 16 and 16A is of the order of 1 to 19 millimeters and perhaps may be more or less dependent upon the application and the conductivity of the body fluids being treated.
Figure 3 is a longitudinally extending sectional view along the axis of tubing 11 taken through staggered section lines 3-3 of Figure 2.
From Figure 3 of the drawings it will be seen that the electrically conductive surface segments 16 and 16A all comprise longitudinally extending, zebra-like stripe or strip electrodes which extend
longitudinally in parallel with the longitudinal axis of the tubing 11. In between each longitudinally extending conductive stripe
electrode 16 or 16A is a longitudinally extending electric insulating area 17 which electrically isolates the alternate electrically conductive, zebra-like stripe electrodes 16 and 16A one from the other.
As best shown in Figure 3, a first set of alternate electrically conductive surface stripes 16 are electrically connected in common to a first annular terminal buss 18 which circumferentially surrounds the tubing 11 and is embedded within the sidewalls of the tubing 11 at a suitable point along its length. The design is such that the first annular terminal buss 18 is electrically isolated from the remaining second set of
alternate, electrically conductive surface stripe electrodes 16A and is electrically connected through a conductor terminal 19 to a first polarity (positive) source of electric excitation potential shown in Figure 1 as a battery 20. As best depicted in Figure 2, all of the first set of positive electrically conductive stripes 16 are physically and electrically connected in common to the first annular terminal buss 18 so that all of the conductive stripes 16 are maintained at a constant, positive polarity electric excitation potential.
A second annular terminal buss 21, which circumferentially surrounds the tubing 11, is embedded within the tubing 11 at a point along its length displaced from the position of the first annular terminal buss 18 and is spaced inwardly towards the inside diameter of the tubing relative to the first annular buss 18. By this arrangement it is possible to electrically connect the
remaining second set of alternate electrically conductive surface stripes 16A in common to the second annular terminal buss 21 in a manner such that the second annular terminal buss is
electrically isolated from the first annular terminal buss 18 as well as the first set of alternate electrically conductive surface stripes 16. As shown in Figure 3, the second annular terminal buss 21 is provided with an outside terminal conductor connection 22 for connecting the annular buss 21 to a negative polarity source of electric potential on the battery 20 as shown in the system drawing of Figure 1. The second set of alternate electrically conductive surface stripes 16A are all provided with internal connector studs which physically and electrically connect all of the 16A stripes in common to the second annular terminal buss 21 so that all of these conductive stripes will be maintained at a negative polarity potential opposite to that from the positive polarity potential applied to the first set of electrically conductive stripes 16 by annular buss 18.
As best shown in Figure 1, the source of electric potential may constitute a direct current voltage battery 20 connected to the conductor terminals 19 and 22 through electric supply
conductors 23 and 24 preferably by a double pole, double throw, on-off control switch 25. In
preferred embodiments of the invention, voltage controlling variable resistors 26 and 27 also are included in the electric supply conductors 23 and 24 in order to control the value of the excitation voltage developed between the alternate sets of conductive surface stripes 16, 16A. While a
battery has been illustrated as a source of direct current excitation potential in the system of Figure 1, it is believed obvious to those skilled in the art that any known direct current source of excitation potential could be used in place of the battery 20.
In operation, the donor whose blood is to be taken, or the recipient who is to be given blood, or is to have his or her blood recycled, is placed on a cot with his or her arm 13 extended and the interconnecting electrically conductive tubing 11 having the hypodermic needle 12 for withdrawal, or supplying, or recycling of blood set up as shown in Figure 1. When both the donor/recipient and the system is in readiness, the control switch 25 is closed so that an electric field is built up across the oppositely disposed electrically conductive zebra-like stripes 16, 16A, etc. Voltages of the order of from 0.2 to 12 volts are applied to the conductive surfaces 16, 16A. It is important to note that the hypodermic needle should be
electrically isolated via conventional electrically insulating IV tubing from any of the zebra stripe electrodes 16, 16A so that the donor/recipient does not receive a shock. By this precaution, he or she will not even be aware of the existence of the electric field within the electrically conductive tubing 11. With the transfer system thus
conditioned, the hypodermic needle is inserted into a vein in the donor's/recipient's arm and blood is withdrawn, given, or recycled through tubing 11.
As the blood passes through the electric fields produced within the electric conductive tubing 11 it will be subjected to and treated by biologically compatible electric current flow through the blood or other body fluid with a current density that ranges from from one
microampere per square millimeter (lμA/mm2) of electrode cross sectional area exposed to the fluid to abou t one mi lliampere per square millimeter ( 1 mA/mm2) dependent upon field strength of the electric field gradient existing between electrodes 16 and 16A, the distance between the electric electrodes 16 , 16A and the conductivity
( resistivity) of the body fluid being treated.
Recent experiments have proven that exposure to electric fields induced by supply voltages of 2-4 volts produces electric current flow through blood of the order of 1 to 100 microamperes .
Effectiveness is dependent primarily upon length of time of treatment ( which may range from about one to twelve minutes) and the magnitude of the
biologically compatible current flow at current densities within the range noted above. For example, treatment of AIDS virus in media at 100 microamperes for 3 minutes has been observed to substantially attenuate ( render ineffective) the AIDS virus. Treatment at other current densities and lengths of time will have a similar attenuating effect. By controlling the length of time and field strength values that blood and/or other body fluids is subjected to the electric field forces, undesirable contaminants such as virus, bacteria, fungus and/or parasites will be adequately
attenuated. The contaminants are rendered
ineffective by the sustained action of the electric current as the blood travels from the needle 12 to the storage bag 14 , or vice versa, or in a
recycling mode. The length of travel of the blood through the sustained electric field induced
current flow also can be adjusted so that the blood is subjected to the electric field force for time periods of the order of from about 1 to 12 minutes at least . At the current noted above this is believed adequate to attenuate (render ineffective) bacteria, virus (including the AIDS virus),
parasites and/or fungus entrained in blood or other body fluids, but does not render the fluids unfit for human use or impair their biological
The species of the invention shown in
Figures 2 and 3 is advantageous since it is
possible to fabricate the treatment tubing by preforming the conductive segments 16 and 16A on the tubing walls while it is in a flat planar
condition, and then rolling the walls into tubular form using a suitable mandrel. The adjoining longitudinal edges of the planar member after rolling are thereafter heat sealed along a
longitudinally extending seam located within one of the electrically insulating sections 17.
Particular attention must be paid to the juncture of the ends of the annular terminal busses 18 and 21 during the rolling and heat sealing steps to assure that good electrical interconnection and continuity at these junctures of the annular terminal busses is provided in the completed treatment tubing. The conductive electrode
segments 16, 16A may be electro-deposited,
chemically formed, separately formed conductive polymer surfaces, or conductive foil or wires adhesively secured to the side walls of the tubing 11 in advance of the rolling and sealing using techniques well known in the printed circuit and integrated circuit manufacturing technologies.
Figure 6 is a diagrammatic, fragmentary, elevational view of a modified blood transfer system using the novel electrically conductive treatment tubing in accordance with the invention. In the Figure 6 embodiment of the invention, a blood pump 28 of conventional, commercially
available construction is inserted in the tubing 11 at some point along its length. The blood pump 28 is electrically isolated from the zebra striped conductive surfaces 16, 16A by suitable insulators 29 formed on the blood input-output connections of pump 28. Provision for electrically bypassing the blood pump 28 (if need be) is made through the shunt conductors 30, 30A which maintain electrical continuity of the direct current excitation
potential applied to the conductive stripes 16, 16A on each side of pump 281 For convenience, the direct current excitation source 20 and its
connection to the electrically conductive tubing 11 has not been shown in Figure 6 but would have to be provided. A separate source of excitation current for running the blood pump 28 is provided from a conventional 110 volt alternating current source through the input terminals 31, 31A.
In systems employing a blood pump, it may be desirable in some applications to provide a blood flow regulating valve 37 inserted in the system at the output of blood pump 28 and within the by-pass loop 30, 30A for the conductive stripes 16, 16A. By thus controlling blood flow, the
electrified transfer system safely can be employed in a closed loop recycling system for withdrawing blood from a patient, electrically treating the blood as described above and then returning the electrically treated blood to the patient. This procedure is referred to herein as recycling. The system of Figure 6 also can be used in those
situations where the blood flow of a donor's blood is not sufficient to assure supply of an adequate amount of blood to or from the collection
receptacle 14 or other recipient. It may also be desirable to have a blood flow regulating valve such as 37 in non-pump systems.
Figures 4 and 5 of the drawings show another embodiment of the invention wherein the electrically conductive treatment tubing 11 includes electrically conductive electrode segments 32 and 32A which are in the form of zebra stripes that extend radially around the inside diameter of tubing 11 in spaced-apart, alternating polarity, conductive annular bands 32 and 32A separated by insulating surface bands 11I which serve to
electrically isolate the respective first set of conductive zebra stripes 32 from the second set of conductive zebra stripes 32A. The first set of alternate ones of the electrically conductive annular stripes 32 are electrically connected in common to a first longitudinally extending terminal buss bar 33 that is embedded within tubing 11 in parallel with the longitudinal axis of the tubing and electrically isolated from the remaining second set of alternate electrically conductive annular stripes 32A. The first longitudinally extending terminal buss bar 33 is designed for connection to a first polarity (positive) source of electric excitation potential through a supply conductor connection 35 on the exterior surface of the tubing 11.
A second longitudinally extending terminal buss bar 34 is. embedded within the body of tubing 11 and is electrically connected to the remaining second set of alternate electrically conductive annular stripes 32A. The second longitudinally extending terminal buss bar 34 is electrically isolated from the first longitudinally extending terminal buss 33 and the first set of alternate electrically annular stripes 32. Terminal buss bar 33 is designed for connection to a second polarity (negative) source of electric excitation potential of opposite polarity from that of the first polarity source of excitation potential. For this purpose an input supply conductor connection 36 is directly connected through the exterior surface of tubing 11 and to the second longitudinally
treatment extending terminal buss bar 34.
In operation, the embodiment of the invention shown in Figures 4 and 5 is physically arranged in a blood transfer system in the manner illustrated in Figure 1 of the drawings with the positive polarity and negative polarity zebra annular stripes being connected to the respective positive polarity and negative polarity terminals of an excitation battery 20 via control switch 25. If required, a blood pump such as 28 and blood flow regulating valve 37 shown in Figure 6 can be included in the blood transfer system employing electrified tubing shown in Figures 4 and 5.
Similar to the system shown in Figure 1, a blood transfer system employing the embodiment of the invention shown in Figures 4 and 5 would be electrically excited in advance of injection of the hypodermic needle 12 into the arm of a blood donor so that all blood passing through the tubing 11 will be subjected to electric forces produced between the alternate polarity annularly formed conductive bands 32 and 32A. Experience with the invention will establish what length is required for the electrification field. However, for initial installations the length of the electrified field as related to the flow of blood through electrified tubing 11 should correspond to at least the 1-6 minute treatment time mentioned earlier.
This is achieved by using an extended array of the alternate annular zebra bands 32 and 32A of adequate length to assure thorough subjection of blood to electric current flow produced by the alternate polarity zebra stripes 32 and 32A. The electric field force intensity applied to the blood by means of the electrified tubing is anticipated to be of the order of 2 to 4 volts similar to the embodiment of the invention shown in Figures 1-3.
In place of supplying continuous direct current excitation to the conductive stripes 16,
16A of Figures 2 and 3 or 32, 32A of Figures 4 and 5, it also is possible to excite these electrically conductive segments of tubing 11 with pulsed waveform direct current excitation potentials. For use in this manner, the pulse rate of the pulsed waveform excitation potentials must be sufficiently high to maintain continuous current flow through blood being treated. In addition, it may be desirable to couple a bank of storage capacitors in parallel across respective pairs of opposite polarity electrically conductive segments 16, 16A and 32, 32A where operation in a pulsed DC mode is desired.
Figure 7 of the drawings is a cross sectional view of another embodiment of the
invention which is substantially different from those previously described. In Figure 7, the material used for fabrication of the tubing 11 is one of the new space-age polymer materials which can be either highly electrically conductive, insulating, or semiconducting and may have values of conductivity ranging from essentially fully conductive to insulating. In the embodiment of the invention of Figure 7, the conductive surface areas on the inside diameter of the tubing 11 are
actually formed into segments, such as 11C, of the cross sectional area of the tubing 11 fabricated from the highly conductive polymer material. The intervening segments of the tubing 11I which separate the conductive segments 11C are integrally formed from the highly insulating polymer material. Suitable positive polarity and negative polarity potentials are applied to the exterior surface areas of alternate ones of the sets of conductive polymer segments 11C from a source of electric potential via the conductors 23 and 24 as
illustrated schematically in Figure 7.
It will be appreciated that the embodiment of the invention shown in Figure 7 is much simpler and hence less expensive to make in that it
requires fewer processing steps than the
embodiments of the invention shown in Figures 1-6. In other respects, the embodiment of the invention shown in Figure 7 would be used in a blood transfer system similar to that shown in Figure 1 or 6 with or without a blood pump 28 and blood flow
regulating valve 37 to effect transfer of blood from a donor to a receptacle or recipient in the event of a transfusion or recycling. During the blood transfer process, again it would be necessary to provide alternate polarity, DC electric
excitation potentials to the spaced-apart,
alternate sets of positive polarity and negative electrically conductive polymer segments 11C prior to passing blood through the tubing 11. This will assure that all of the blood being transferred is subjected to the electric field forces produced between the alternate conductive surfaces 11C. As a variation of the Figure 7 embodiment, which visualizes that the segments 11C and 11I all extend longitudinally and parallel to the longitudinal axis of tubing 11, it would be possible, but more elaborate to design, to employ alternate radially surrounding annular conductive segments 11C and interlacing insulating segments 11I similar to Figure 5, but such fabrication would require somewhat more complex terminal buss bar DC electric supply connections 23 and 24 than those shown in Figure 7.
Figure 8 is a fragmentary, diagrammatic, elevational view showing a form of blood treatment system according to the invention wherein a small electrically conductive vessel 41 in the form of a short piece of electrified tubing and a
miniaturized battery power source 42 are implanted in the arm of a human being. The electrified tubing 41 may be in the form of any of the prior disclosed electrified tubing structures described with relation to Figures 1-7, but which are
fabricated in miniaturized form so that the tubing 41 can be inserted in a section of or surrounding a vein 44 of the arm 13 of a patient whose blood is being treated. The implantation is such that the blood of the patient 44 naturally is pumped through the short piece of electrified tubing 41 while circulating blood to the hand of the patient and thereby form a closed loop, recirculating,
implanted treatment system that comprises an integral part of the circulatory system of the patient being treated. Because the parameters of such an implanted system are necessarily small, a single passage through the implanted electrified tube 14 may accomplish a relatively small
attenuation of contaminants in the blood.
Therefore, it is the repeated passage of small portions of the patient's blood continuously twenty-four hours a day and for as many days as are needed which will gradually attenuate the contaminants to the point where they are rendered ineffective as described earlier.
Figure 9 is a partial, fragmentary, sectional view of the upper arm portion 13 of a vein or artery of a patient in which a treatment system according to the invention has been
implanted, and shows in greater detail the
construction of a specialized, miniaturized, electrically conductive treatment vessel with associated miniaturized battery electric power source for use in an implanted treatment system as shown in Figure 8. In Figure 9, the electrified vessel 41 is in the form of an outer housing 45 that is in the shape of a football which is implanted within the interior walls 44 of an artery or a vein 44. The outer housing 45 is comprised by a central, cylindrically-shaped portion 45M of solid conductor such as platinum which is
biocompatible with human blood and tissue and has integrally formed, conically-shaped porous ends 45C which are attached to and form an electrically conductive screen grid (at the same potential) as the mid portion 45M. The conical end portions 45C both are perforated and may be in the nature of a screen or mesh wire and of the same material composition as the mid portion 45M. Disposed within the outer housing 45 is a inner housing 46 which is tear-drop shaped and secured within the central portion 45M of the outer housing by
suitable insulating support spider legs 47. The inner housing 46 likewise is formed from platinum or other suitable biocompatible conductive material and has supported within its interior a
miniaturized battery 42 secured to the conductive walls of inner housing 46 by conductive support legs 48. The support legs 48 serve as terminal connectors from one terminal of battery 42 to the inner housing 46 so that it is maintained at one polarity excitation potential. The remaining opposite polarity terminal of miniaturized battery 42 is connected through an insulated conductor 49 to the central portion 45M of outer housing 45 whereby the entire outer housing including the meshed conical end portions 45C are maintained at the opposite polarity potential.
Prior to implantation in a patient, the electrified vessel shown in Figure 9 is activated by connection to battery 42 so that a difference of potential exists between the inner and outer housings 45 and 46. Following implantation of the activated, electrified treatment vessel 41, its presence in a vein or artery will cause all blood flowing through the vein or artery to pass between the side walls of the inner and outer housings 45 and 46 so as to be subjected to the electric field forces existing in these spaces. The presence of the electric field forces will induce a current flow through the blood passing between the interior and outer housings as explained above which will result in attenuating bacteria, virus, parasites and/or fungus which are present in the blood as contaminants. Here again, because of the
relatively small portion of the total blood flowing in a patient that will be treated by the device within a given time period, it is the repeated, recycling process of treatment of the blood over a prolonged period of time that will result in attenuation of the contaminants in the blood to the point where such contaminants are rendered
ineffective as described earlier.
In order to further assure adequate treatment of the blood of a patient receiving the implant device, it is recommended that the blood be treated in an external treatment processing
facility such as described earlier in Figures 1 and 6 or to be described hereinafter with relation to Figures 18 and 19 in which the total capacity of the treatment system is greater whereby substantial attenuation effect can be achieved in a
comparatively shorter time period yet to be
determined, and then the in vitro implant treatment system such as shown in Figures 8, 9 and 10 can be used to maintain the attenuated condition and to prevent any subsequent; build up of contaminants after the initial treatment.
Figure 10 is a fragmentary, diagrammatic view of a partial vein or artery 44 showing in greater detail the cylindrical or tubular
electrified treatment vessel 41 originally
described with relation to Figure 8. This implant treatment vessel 41 is miniaturized so that it is in effect an open-ended cylinder in shape and has a diameter comparable to that of a large vein or artery and so that it can be grafted or implanted into the vein or artery as illustrated in Figure 10. The tubular treatment vessel 41 may be
designed pursuant to Figures 2 and 3 of the
drawings, for example. For this application, the battery source of power 42 is annular in shape and is slipped over the tubular treatment vessel 41 in the manner shown. In Figure 10 only a cross
sectional view of the annular collar-shaped battery 42 is illustrated. At the point where the battery 42 fits over the tubular treatment vessel 41, the respective positive and negative terminals of the battery are exposed to engage the corresponding positive and negative supply terminals 19 and 22 of the tube 41 so that the resulting battery powered structure has a minimum exterior profile to facilitate implantation. From a comparison of Figure 10 to Figure 9 of the drawings, it will be appreciated that the Figure 10 treatment vessel introduces some flow restriction in the vein or artery in which it is implanted and for this reason the construction shown in Figure 10 is preferred.
Figures 11 and 11A of the drawings illustrate a construction for the electrified treatment vessel 51 wherein the treatment vessel is in the form of square or rectangular cross
sectionally-shaped open-ended tubing. The
treatment tubing 51 provided with a square or rectangular shape so that provision of opposed, parallel conductive electrode surfaces 51U and 51L is greatly simplified as best seen in Figure 11A of the drawings which is a cross sectional view taken through plane 11A-11A of Figure 11. By fabricating the upper and lower surfaces of the tubing 11 from electrically conductive material such as platinum, etc., and separating the upper and lower surfaces 51U and 51L by electrically insulating side walls 52R and 52L, provision of the electrically
isolated, opposed, parallel electrode surfaces is simplified and the resulting treatment vessel introduces minimum restriction to flow of blood. By connecting the upper surface 51U to one polarity of electric potential (for example the positive terminal) and connecting the lower surface 51L to the negative polarity terminal of a. battery (not shown), electrification of the interior area of the tubing wherein the fluids to be treated flow is readily achieved with a greatly simplified
electrode structure. Variations of this structural feature wherein the side insulating surfaces 52R and 52L are curved with their concave surfaces facing each other and the cross sectional area of the upper and lower conductive surfaces 51U and 51L tailored to provide a desired current density, tubular treatment vessels such as shown in Figures 11 and 11A could be readily provided for use in implantation devices such as those illustrated in Figures 8 and 9 above.
Figure 12 is a perspective view of a novel, electrified, closed, octagonally-shaped, flat, box- like treatment vessel 60 according to the invention which provides an enlarged cross-sectional area relative to the cross sectional diameter of the inlet and outlet tubing supplying the interior of the treatment vessel whereby increased through-put of a fluid being treated can be achieved in a given time period. The treatment vessel 60 shown in Figure 12 is comprised essentially of upper and lower, octagonally-shaped, flat insulating plates 61 and 62, respectively, of an insulating material which is compatible with human blood and/or other body fluids. Disposed immediately below and above the upper and lower plates 61 and 62 are
octagonally-shaped, conductive electrode members 63 and 64, respectively, which are separated and electrically isolated one from the other by a surrounding electric insulating gasket member 65. The entire structure is sandwiched together and held in assembled relation by threaded thru-pins 66 as best seen in Figure 12A of the drawings. The insulating gasket 65 which may be of teflon defines an open space 67 between the two conductive
electrode members 63 and 64 into which the blood or other body fluid to be treated is introduced via inlet and outlet conduits 68 and 69. Opposite polarity electric potentials are applied to
respective conductive plates 63 and 64 to produce an electric field force across the intermediate space 67 through which the fluids being treated flow between electrode plates 63 and 64. By thus structuring the treatment vessel, increased treatment surface area is provided to the blood or other body fluid flowing through the space 67 whereby in a given time period an increased quantity of fluids can be treated.
Figure 13 is a perspective view of another form of enlarged cross sectional area treatment vessel 70 having an exterior shape similar to that of the treatment vessel shown in Figure 12. The electrified treatment vessel shown in Figure 13 differs from that in Figure 12, however, in the construction of its electrically conductive electrodes which comprise a plurality of
interleaved, conductive, flat, electrode plates 71 and 71A. The electrode plates 71 are secured in and project inwardly from a right hand (RH) conductive end plate 72R as shown in Figure 13A.
The alternate set of flat electrode plates 71A are secured to and project inwardly from a
corresponding conductive end plate 72L on the left hand end of the treatment vessel 70. The
conductive end plates 72R and 72L and coacting insulating side plates 73 which insulate the conducting end plates from one another, form an octagonally-shaped box frame which is closed by upper and lower insulating top and bottom
insulating plates 74 and 75. The conductive end plates 72R and 72L have a central opening formed therein into which inlet and outlet tubes 76 and 77 are secured as best seen in Figure 13 for providing inlet and outlet flow through connection to the treatment vessel 70.
The alternate sets of flat electrode plates 71 and 71A extend parallel to one another and are provided with different polarity electric
potentials supplied to the respective sets of interleaved electrode plates via the respective conductive end members 72R and 72L. If desired, the respective flat conductive electrode plates 71 and 71A may be fabricated from a perforated material as shown in Figure 13B of the drawings. Also, it may be desirable that some form of thermal insulation, or a thermally controlled chamber be provided around the exterior of the treatment vessel 70 as indicated by the thermal insulation 78 shown in Figure 13A.
In operation, electrified treatment vessel 70 shown in Figures 13, 13A and 13B functions in essentially the same manner as was described earlier with respect to Figures 1-7 to effect attenuation of contaminants such as bacteria, virus and fungus contained in blood and/or other body fluids being treated in the flow through treatment vessel of Figure 13.
Figure 14 is a longitudinal sectional view of still another form of enlarged cross sectional area, electrified treatment vessel 80. The
treatment vessel 80 shown in Figure 14 is in the form of an open-ended, elongated cylinder 81 whose cylindrical walls are fabricated from an insulating material which is biocompatible with human blood and/or other body fluids and whose open ends are closed by circular-shaped conductive end pieces 82 and 83. Inlet and outlet tubular openings 84 and 85 are provided to the interior of cylindrical housing 81 through centrally formed apertures in the circular end plates 82 and 83. Within the interior of the cylindrical, insulating housing 81 at least two, separate, concentric, perforated. cylindrically-shaped electrode members 86 and 87 are provided which extend longitudinally through the interior of the outer cylindrical housing 81. The first set of concentric, perforated,
electrically conductive electrodes 86 is embedded in and supported by the conductive end plate 82 which serves as an electrical terminal for applying electric potentials to all of the concentric electrode member 86. Similarly, the concentric, perforated, conductive electrode member 87 is physically supported by and electrically connected to the conductive end plate 83 for the supply of an opposite polarity potential thereto. Additionally, if desired, one or more additional perforated concentric electrode members similar to 86 may be spaced apart from the inner concentric electrode member 86 outwardly along the diameter of the circular end member 82 with additional perforated concentric electrode members 87 being sandwiched between the two electrode members 86 and spaced apart therefrom so as to provide an electric field force between all the spaced apart, separated electrically conductive electrode members 86 and 87. Additionally, if desired, a conductive surface 89 may be formed around the interior walls of the outer, insulating cylindrical housing member 81 and electrically connected to the conductive end plate 82 or 83 which is opposite in polarity to the outermost concentric electrode members 86 or 87. This will assure that the entire interior of the treatment 80 vessel cross sectional area is crossed by the electric field force and all blood or other body fluid passing the cylindrical housing member 81 is subjected to biologically compatible low electric current flow as a consequence of the electric fields produced between the different concentric electrode members including the coated surface 89 within the interior insulating housing member 81.
In operation, the embodiment of the invention shown in Figure 14 and 14A operates in substantially the same manner as described with relation to earlier embodiments of the invention to assure production of biologically compatible electric current flow through the blood or other body fluid being treated in the treatment vessel 80.
Figure 15 is a longitudinal sectional view of still another embodiment of an enlarged cross- sectional area treatment vessel 90. The treatment vessel 90 again comprises an outer, hollow, open- ended cylindrically-shaped, insulating body member 91 whose open ends are closed by electrically conductive, circular end plates 92 and 93,
respectively. Inlet and outlet tubular openings 94 and 95 are provided through the central axial opening in the conductive end plates 92 and 93 for passage of blood and/or other body fluids being treated into the interior of the treatment vessel 90. The conductive end plates 92 and 93 have respective sets of opposite polarity potential needle-like electrodes 96 and 97, respectively, projecting therefrom inwardly into the interior of the treatment vessel 90. Different polarity
electric potentials are applied to the respective conductive end plates 92 and 93 through respective negative and positive polarity terminals indicated at 98 and 99. If desired, and in order to assure complete saturation of the entire volumetric area within treatment vessel 90 with electric fields, a conductive coating similar to that shown at 89 in Figure 14 can be provided to the inner surface of the hollow, cylindrically-shaped outer body member 91 of treatment vessel 90.
Figure 15A is a cross sectional view taken through plane A-A of Figure 15 and shows how the array of needle-like electrodes appear within the interior of the treatment vessel 90. In operation, the treatment vessel 90 will function in
substantially the same manner as has been described previously with relation to earlier described embodiments of the invention.
Figure 16 is a perspective view of still another form of enlarged cross sectional area treatment vessel 100 according to the invention and Figure 16A is a partial cross sectional view taken through plane 16A-16A of Figure 16. The treatment vessel 100 comprises a relatively large
rectangular-shaped block 101 of electrical
insulating material which is biocompatible with blood and/or other human body fluids. The
insulating block 101 has a plurality of parallel, longitudinally extending, open-ended, tubular-shaped openings 102 formed therein through the entire length of the block. The tubes 102 are provided with electrically isolated, opposed, parallel extending conductive plate electrodes, best seen in Figure 16A, which have opposite polarity electric potentials applied thereto. One set of these electrodes, formed for example by the lower electrode 109 in each tube, extend out to and engage a conductive surface coating formed on one end of the insulating block, for example 101R, and the remaining upper electrodes 109 form a second set which extend out of the left hand end of the tubes and contact a conductive coating formed on the remaining end 101L of block 101. Respective, opposite polarity electric potentials are supplied to the respective conductive surfaces 101R and 101L so that a potential difference exists between the sets of positive and negative polarity electrodes within each longitudinally extending tube in block 101. The ends of the tubes 102 open into and are supplied from, or supply, respective header
reservoirs 103 and 104 formed on the respective opposite ends of the block of insulating material 101. Each of the reservoirs 103 and 104 has a centrally formed opening for receiving either an inlet tube 105 applied to header 103 or an outlet tube 106 secured to header 104 for supply of blood or other body fluids to be treated to and from the treatment vessel 100. If desired, a blood pump or other fluid pump can be inserted between the supply tube 105 and header 103, or between outlet tube 106 and the or outlet from the header reservoir 104, or both. Alternatively, both inlet and outlet pumps can be used. In operation, the electrified
treatment vessel 100 shown in Figure 16 functions in the same manner as those species of treatment vessels described previously.
For some treatment applications, it may be desirable to provide exhaust vents such as shown at 107 and 108 in Figure 16 to the inlet reservoir 103 and/or the outlet reservoir 104 with the vents that can be selectively operated by valves that can be automatically or manually controlled for venting off gases that might be trapped in the tops of reservoirs and which otherwise might interfere with the proper operation of the electrified treatment vessel. In a similar manner, suitable venting apparatus may be provided to other of the large cross sectional area electrified treatment vessels described previously.
Figure 17 is a perspective view of still another enlarged cross-sectional area treatment vessel 110 which is similar in all respects to the treatment vessel shown in Figure 16 with the exception that the body or block of insulating material 101 through which the elongate tubular openings are made, is cylindrically shaped as illustrated in Figure 17. In other respects, the embodiment of the invention shown in Figure 17 would be identical to Figure 16 in the fabrication and operation of its component parts including the reservoir headers 103 and 104 and would operate in a similar manner.
Figure 18 is a diagrammatic, sketch of a human blood or other body fluid treatment system employing one of the larger cross-sectional dimension fluid treatment vessels 60, such as any one of those shown in Figures 12-17 of the
drawings. The particular fluid treatment system shown in Figure 18 is for a continuous flow-through recirculating body fluid treatment wherein blood is withdrawn from the arm 13 of a patient and supplied through IV tubing 111 to a commercially available blood pump 28 and thence to an electrified
treatment vessel 60. The treatment vessel 60 may be like any of the treatment vessels described with relation to Figures 12-17 of the drawings wherein the blood or other body fluid being treated is exposed to a low voltage, low current electric current flow for attenuating to the point of rendering them ineffective, any contaminants entrained in the blood, such as bacteria, virus and fungus. The treated blood appearing at the output of the treatment vessel 60 then is recirculated back through IV tubing 112 to the arm 13 of the patient whose blood or other body fluid is being treated. If desired, IV tubing 111 and 112 could also be treatment tubing such as described in Figures 1-7 and 11. This could provide double treatment for the fluid if that were desirable. In the event that the entire treatment does not take place in an air conditioned, temperature controlled room, then it may be desirable to provide a
temperature controlled enclosure indicated by dotted lines 113 around at least the pump 28, electrified treatment vessel 60 and the
interconnecting IV tubing sections 111 and 112 in order to assure maintaining a substantially
constant viscosity of the blood or body fluid being treated.
Normally, the system of Figure 18 would be used in a continuous flow-through recirculating treatment system wherein blood from the patient's arm 13 is supplied through pump 28 to the treatment vessel 60 where it is treated and then discharged back through tubing section 112 to the arm of the patient. The flow rate of the blood thus processed would be adjusted to correspond substantially to the natural flow rate of blood circulated through the patient's body to the extent possible.
In addition to operation in the above manner, it would also be possible to operate the system of Figure 18 in a stopped-flow manner
wherein the blood pump is intermittently stopped to allow for more extended electrical treatment of the blood or other body fluid contained in the
treatment vessel 60 during the period of time that the blood pump is stopped thereby assuring fuller electrification treatment and the greater
attenuation of the bacteria, virus or fungus
entrained in the blood.
Figure 19 is a diagrammatic sketch of a form of closed loop, flow-through recirculating treatment system according to the invention that is somewhat similar to the system shown in Figure 18. Figure 19 differs from Figure 18 in that an inlet pump 28 and an outlet pump 28' are connected to, respectively, the intake to and outlet from the electrified treatment vessel 60. If desired, an inlet control valve 113 and an outlet control valve 114 also can be interconnected between the inlet pump 28 and the intake to the treatment vessel 60 and between the output from the treatment vessel 60 and the intake to the outlet blood pump 28'. These inlet and outlet control valves indicated at 113 and 114 preferably, are automatically operated in a time sequence which allows the system of Figure 19 to be operated as a two pump, start-stop flow through system. When operated in this manner, the first pump 28 is allowed to operate and discharge blood from the arm 13 of the patient to be pumped into the treatment vessel 60 and thereafter is closed off with both the inlet and outlet valves 113 and 114 in their closed condition. At this point electrification treatment of the blood or other body fluid takes place for a predetermined, scheduled time period to assure adequate
attenuation to the point of rendering ineffective the contaminant bacteria, virus or fungus. Upon completion of the pre-scheduled treatment period, the outlet valve 114 is opened and outlet pump 28' actuated to return the treated blood to the arm of the patient 13. Operation in the semi-continuous, start-stop, batch fashion will assure that adequate electrified treatment of the blood has been
accomplished while achieving this end in a somewhat continuous manner suitable for use in a closed loop, recycling blood treatment process.
Figure 20 is a partially disassembled. perspective view of a non-flow-thru, single batch, body fluid treatment vessel 120 according to the invention, which is open to atmosphere on its upper side, and which was used in conducting the
experiments described hereinafter. Figure 20A is a diagrammatic sketch of the assembled treatment vessel 120 shown in Figure 20 connected to a source of direct current electric power 128. Power source 128 was capable of providing substantially constant voltage across the conductive electrodes of the treatment vessel 120 at a given voltage setting, ranging between 0.2 volts and 12 volts DC, and for a given electrical resistivity of a sample being treated, and provided essentially constant current through the batch sample in the treatment vessel. Upon being assembled together with through bolts and nuts 124N that extend through the openings 124 in each of the teflon partitions comprising end walls 121 and 122 and a central partition 123, the parts form a fluid-tight chamber as shown in Figure 20A. A set of spaced-apart, parallel electrodes 125 and 126 are supported in suitably formed
channels in the respective end partitions 121 and 122 by threaded studs (not shown) securing the electrodes 125 and 126 in opposed parallel
relationship by means of bolts (not shown) threaded into threaded openings 127 in the tops of the end partitions 121 and 122. The electrodes 125 and 126 were connected to the negative and positive
terminals, respectively, of the battery source of direct current electric power shown at 128 in
Figure 20A. When thus assembled, the resulting structure results in a non-flow treatment vessel or cell defined by the vertically extending slot formed in a 1 millimeter wide central portion of the central segment 123 of the vessel. This vertically extending slot defines an open-sided treatment well 129 which is 1 millimeter across between electrodes 125 and 126, 1.56 millimeters in length and 8.32 millimeters in depth. With the experimental test treatment vessel constructed and energized as thus described, the following
experiments were conducted.
A non-flow vessel or cell included a pair of platinum electrodes 1 mm apart inserted into a well 1.56 mm in length and 8.32 mm in depth. The non-flow vessel was connected to a direct current source capable of creating an electric field at a constant voltage and constant amperage. Into this well was placed a suspension of the human
immunodeficiency virus type 1 (HIV-1) at a
concentration of 106 infectious particles per ml. An aliquot of approximately 10 μl of the virus suspension was placed into the well. Thereafter, the viral suspension was exposed to direct currents ranging from 0 microamps for up to 12 minutes to 100 microamp for up to 6 minutes. Intermediate currents of 25, 50 and 75 microamps were used to expose similar viral aliquots. A matrix of current and time was employed as shown in Table 1. After the exposure of the viral suspension to electric currents, the contents of the non-flow vessel where removed and placed into sterile microtubes. Five μl of each sample were removed and diluted with 95 μl tissue culture medium supplemented with 10% fetal calf serum (FCS).
In Experiment 1, the resuspended and treated viral stocks were incubated with a human T lymphoblastoid cell line named CEM-SS. This cell line, upon exposure to HIV-1, forms syncytia. It is well documented that the viral titer used is directly correlated with the number of syncytia formed. Therefore, evaluation of infectivity of HIV-1 can be used with this assay. In contrast, Experiment No. 2 used a different human T
lymphoblastoid cell line named H9. This cell line, in contrast to CEM-SS cells, produces, upon
exposure to HIV-1, many viral particles. The amount of virus produced is proportional to the amount of virus to which the cells are exposed.
Therefore, quantitation of viral particles or, more commonly viral associated protein (in this case reverse transcriptase), can be used as an index of viral infection. In both assays, the CEM syncytia forming assay and the H9 viral protein assay, similar type results were obtained. That is, with the CEM cells, although syncytium formation and quantitation is preferable, one can quantitate the HIV-1 associated protein (reverse transcriptase) activity and conversely with the H9 cells, although reverse transcriptase quantitation is preferred, one can quantitate giant cell (syncytia) formation. Both of these assays are widely used as
reproducible measures of viral infection and can be used to determine if alterations in viral
infectivity as a product of this electrical
treatment can be detected.
Approximately 105 CEM-SS cells per sample were incubated with a treated or untreated
(control) viral aliquot for up to 4 days. The cells were placed into microtiter plate wells and monitored for formation of syncytia every 24 hours by microscopic observation. In a standardized fashion, as it has been reported in the literature and is currently being conducted in many laboratories, the number of syncytia at 3 and 4 days was determined. Table 2 summarizes the results from a representative experiment using this assay. As can be noted, the number of syncytia formed was inversely proportional to the amount of electric current. That is, additionally, with increased current (50 vs. 100 microamps) there was a reduction in the number of syncytia formed.
These results and those of .additional experiments using the CEM-SS cell line indicate a consistent finding that electrical treatment of the RF strain of HiV-1 attenuates the virus potential for
inducing syncytium formation in this cell line.
A separate and independent assay to determine the ability of electric current to alter HIV-1 infectivity using H9 cells was employed. The basic strategy was similar to that used for the CEM cells with the exception that the initial
suspension of treated and controlled viral stock was incubated with 105 H9 cells for 2 hours at 37°C. Thereafter, the cell virus suspensions were further diluted to 5 ml in standard tissue culture medium. The cell-viral suspensions were then incubated for up to 14 days at 37°C 5% CO2. At 3 day intervals (beginning at day 2), aliquots of cell suspension were removed from each sample. The aliquots were centrifuged at 1,000 rpm for 5 minutes in order to pellet the cells. After centrifugation, the supernatant and cell pellets were separated. The supernatant was cryopreserved for subsequent reverse transcriptase assay and the cell pellets were resuspended in fixatives and maintained in a tissue bank for additional studies employing in situ hybridization and
immunocytochemistry to detect qualitatively and semi-qualitatively viral infection by HIV-1. At the end of each experiment, the supernatant samples from each of the tests and time points were
examined using standard reverse transcriptase assay. The results of a representative experiment are shown in Table 3. The results of this
experiment indicate that the ability of HIV-1 to infect H9 cells is attenuated by the magnitude of the electrical currents to which the virus is exposed. Additionally, at lower current magnitude, but with prolonged exposure time, attenuation of viral infectivity is achieved. That is, analogous to the results observed using syncytium formation and the CEM-SS cell line, either increased current or increased duration of exposure time was
inversely proportional to the amount of reverse transcriptase produced by the cell line.
In conclusion, these experiments which have been repeated several times and those using the CEM-SS cell line indicate at a statistically significant level that direct electrical current at biocompatible amperages for discrete exposure time intervals can attenuate the ability of HIV-1 to infect normally healthy cells which are susceptible to the HIV-1 AIDS virus.
Although it is uncertain what is
specifically causing the attenuation of the
contaminants (virus, bacteria, parasites and/or fungus), some possible explanations have been put forward. One is that the attenuation is caused simply by the direct affect of the electric current and voltage. Another entails the following. When a voltage is applied to the electrodes, a small current will flow through the electrically
conductive medium. The applied voltage and ensuing current will induce changes in the complex
biologically active fluid. Current can flow through the media if positive and/or negative charges are transported through said media. The transport might induce changes in the charge distribution of the biologically active molecules thus changing their biological activity.
Furthermore, the voltage and current can induce the production or elimination of different ions, radicals, gases and/or PH levels which may affect, alone or in combination, the biologically active molecules and/or cells. The above products of the electrical processes may either be very short lived and stay in the close proximity of the electrodes or can diffuse or mix in the bulk of the media and react with the biologically active molecules or cells to result in their attenuation.
Current (μA) Time (Minutes)
0 1 4 8 12
25 2 4 8 12
50 2 4 8 12
75 2 4 8 12
100 1 3 4 6
(Number of Syncytia)
Dilution of virus
1:20 TNTC* TNTC 28 66 15
1:40 TNTC 175 22 42 7
1:80 TNTC 90 20 25 4
1:160 180 44 9 9 2
1:320 115 28 4 6 0
1:640 70 10 0 2 0
1:1280 40 7 0 0 0
1:2560 28 4 0 0 0
1:5120 15 2 0 0 0
1:10,240 10 1 0 0 0
1:20,480 4 0 0 0 0
0μA8 ' 25 μA8 ' 50μA6 ' 75μA4 ' 100μA3 ' * TNTC = Too numerous to count TABLE 3
Reverse Transcriptase Activity
D a y s o f i n c u b a t i o n
μ Ampe/Time (Min.)
0/6 0 13.8
0/12 0 11.7
50/3 0 9.1
50/6 0 9.1
50/12 0 4.8
100/3 0 5.7
100/6 0 3.6
PRACTICAL USES OF INVENTION
While the disclosure herein presented has been directed to principally the electrical treatment of blood, it is believed obvious to those skilled in the art that the invention can be applied with corresponding effect to other body fluids which are electrically conductive for the treatment of contaminants such as bacteria, virus and fungus contained therein. Further, while voltages of the order of from about 0.2 volts to 12 volts have been indicated as preferable, it is possible that certain virus may be attenuated (or attenuated at a faster rate) if they are subjected to a greater electric current magnitude of the order of 500 microamperes for shorter time periods. Acceptable current magnitudes normally would require an excitation voltage of from 0.2 to 12 volts. However, in certain cases where faster or more complete attenuation of the contaminants in body fluids may be desired under certain
circumstances and conditions, the excitation
voltage supplied to the conductive tubing may in fact exceed the 0.2 to 12 volt range indicated for most treatments.
Having described several embodiments of new and improved electrically conductive treatment methods and vessels for use in practicing the novel method for the treatment of blood and/or other body fluids with electric field forces and treatment systems employing the same, it is believed obvious that other Modifications and variations of the invention will be suggested to those skilled in the art in the light of the above teachings. It is therefore to be understood that changes may be made in the particular embodiments of the invention described which are within the full intended scope of the invention as defined by the appended claims.
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|Citing Patent||Filing date||Publication date||Applicant||Title|
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|International Classification||A61M1/00, A61L2/00, A61M1/36, A61L2/02|
|Cooperative Classification||A61M1/36, A61L2/0011, A61L2/02|
|European Classification||A61L2/02, A61M1/36, A61L2/00P2|
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