US3882861A - Auxiliary control for a blood pump - Google Patents

Auxiliary control for a blood pump Download PDF

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US3882861A
US3882861A US399904A US39990473A US3882861A US 3882861 A US3882861 A US 3882861A US 399904 A US399904 A US 399904A US 39990473 A US39990473 A US 39990473A US 3882861 A US3882861 A US 3882861A
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Prior art keywords
blood
pump
blood pump
pulse
duration
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US399904A
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Donald E Kettering
Morris E Jones
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Vital Assists Inc
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Vital Assists Inc
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Priority to US399904A priority Critical patent/US3882861A/en
Priority to CH1247274A priority patent/CH582519A5/xx
Priority to DK485374A priority patent/DK156413C/en
Priority to SE7411684A priority patent/SE411704B/en
Priority to GB41134/74A priority patent/GB1487242A/en
Priority to JP49107859A priority patent/JPS6231949B2/ja
Priority to NL7412448A priority patent/NL7412448A/en
Priority to FR7431876A priority patent/FR2244546B1/fr
Priority to DE2445403A priority patent/DE2445403C2/en
Priority to DD181245A priority patent/DD115038A5/xx
Priority to BE148793A priority patent/BE820223A/en
Priority to IT27602/74A priority patent/IT1022226B/en
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3639—Blood pressure control, pressure transducers specially adapted therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A61M1/3403—Regulation parameters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3607—Regulation parameters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/104—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body
    • A61M60/109—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body incorporated within extracorporeal blood circuits or systems
    • A61M60/113—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body incorporated within extracorporeal blood circuits or systems in other functional devices, e.g. dialysers or heart-lung machines
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/30—Medical purposes thereof other than the enhancement of the cardiac output
    • A61M60/36—Medical purposes thereof other than the enhancement of the cardiac output for specific blood treatment; for specific therapy
    • A61M60/37—Haemodialysis, haemofiltration or diafiltration
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/50—Details relating to control
    • A61M60/508—Electronic control means, e.g. for feedback regulation
    • A61M60/515—Regulation using real-time patient data
    • A61M60/531—Regulation using real-time patient data using blood pressure data, e.g. from blood pressure sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3334—Measuring or controlling the flow rate
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/424—Details relating to driving for positive displacement blood pumps
    • A61M60/427—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic
    • A61M60/43—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic using vacuum at the blood pump, e.g. to accelerate filling
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S128/00—Surgery
    • Y10S128/12—Pressure infusion

Definitions

  • the auxihary control regulates the pump rate by producing an electrical pulse train in which the duration of the pulses corresponds to changes in negative pressure corresponding to changes in the blood flow 128/214 F, 214.2, DIG. l2, DIG. 13; 417/44 56 References Cited 7 1 rate.
  • the control presents means for achievmg a rap1d UNITED STATES PATENTS response to changes in the flow of the patients blood. 3,091,239 5/1963 Moeller 128/214 F D F 3,496,878 2/1970 Hargest et a1 1. 417 14 7 Clam", 3 "awmg gums 39 ⁇ PUMP BLOOD.
  • the present invention relates to an improved auxiliary control for an extracorporeal blood pump used in hemodialysis and more particularly to novel apparatus for controlling the blood pump rate in an extracorporeal hemodialysis system.
  • kidney diseases have been of critical concern to human life. Many kinds of kidney diseases interfere with the function of the kidney such that the kidney ceases to remove waste and excess water from the blood. When the kidney is sufficiently impaired that a large portion of the waste products and water are not removed from the blood, the life of the patient cannot be preserved unless a way is provided for artificially performing the functions of the impaired kidney through extracorporeal hemodialysis.
  • pump starvation The collapse of blood lines resulting from insufficient blood supply to a continuously operating blood pump is defined herein as pump starvation.”
  • pump starvation To avoid time consuming and sometimes dangerous pump starvation, it has conventionally been necessary to adjust the pump speed well below an optimum rate to a level which pro vides a wide safety margin in order to avoid pump starvation.
  • the attending physician must choose between (a) lowering the pump rate to accommodate the lowest possible blood flow rate as a safety margin and thereby significantly extending the dialysis time or (b) risk collapse of blood lines and premature interruption of dialysis through pump starvation in the event of a drop in the patients blood flow rate.
  • the present invention includes novel apparatus for continuously varying the pump rate of a blood pump used in hemodialysis in response to changes in blood flow from the patient so as to maximize the rate of hemodialysis while avoiding pump starvation. Furthermore, the invention provides apparatus which can accomplish the previously described function in combination with existing conventional blood pumps and control mechanisms.
  • FIG. 1 is a block diagram illustrating a presently preferred embodiment of the invention
  • FIG. 2 illustrates a waveform taken at point A in FIG. 1, the waveform particularly showing a signal representation when the patients blood flow has increased during the course of dialysis;
  • FIG. 3 illustrates a waveform taken at point A of FIG. 1, the waveform particularly showing a signal representation when the patients blood flow has decreased during the course of dialysis.
  • a conventional pressure transducer 22 provides a direct conversion between negative pressure in the blood line 24 and electrical voltage.
  • Blood line 24 connects the pressure transducer to a conduit (not shown) which carries blood from a blood vessel of a patient to the blood pump 37.
  • the electrical qualities of the pressure transducer may be characterized as either a variable resistance or a variable voltage source. Whichever type of transducer is employed or whichever electrical characterization is used, the electrical quantity varies in proportion to the blood flow as measured by the negative blood pressure in line 24.
  • the negative pressure is preferably observable on a conventional readout device 23.
  • the electrical output signal of the pressure transducer is fed into an averaging circuit 28.
  • the averaging circuit 28 may be any one of a wide variety of known discrete or integrated circuits, the most simplified of which would merely be a capacitor in parallel with the transducer output conductors to accomplish averaging of the systolic and diastolic pressure signal from the transducer 22.
  • the averaged transducer signal is then conducted to and appears at one of the inputs to a conventional operational amplifier 31 which forms part of the comparator 30.
  • the initial reference control 32 provides a reference signal for the second comparing input of the operational amplifier 31.
  • the initial reference control may be either a fixed or variable voltage divider which provides a pre-established signal level at one of at least two operational amplifier inputs.
  • the operational amplifier portion 31 of the comparator 30 is used in the summing mode, where the two inputs are added together to form an output to the electr nic switch 36 which output is proportional to the sum of the inputs.
  • the electronic switch 36 preferably comprises a conventional threshold trigger circuit capable of converting the output signal of the operational amplifier 31 into a pulse of duration proportional to the amplitude of the output signal of the operational amplifier.
  • a common, readily available device for performing the function of the electronic switch would be any suitable type of current controlled current source such as a unijunction transistor with an external base to emitter timing capacitance which acts to fire a triac or the like.
  • the power supply for the operational amplifier portion of the comparator is a pulse generator 34 which produces a generally square wave voltage signal causing the output of the operational amplifier to turn on and off at a constant rate. Any suitable conventional pulse generator having sufficient voltage output to drive the operational amplifier would be acceptable.
  • the signal from the operational amplifier is a periodic pulse having an amplitude proportional to the sum of the initial reference signal and the averaged transducer signal. It should be recognized that the higher the output signal from the comparator, the greater the time increment that switch 36 is on, and conversely the lower the signal from the comparator, the shorter the time increment that switch 36 is on.
  • the regular power supply line to a conventional blood pump and controller is diverted through the electronic switch 36.
  • the waveforms shown in FIGS. 2 and 3 are taken at point A in the diagram of FIG. 1, assuming an alternating current power supply like that available at a standard utility outlet.
  • the solid portions of the waveforms represent that portion of the waveforms during which the electronic switch 36 is off.
  • the switch 36 turns on, it remains on until the AC cycle goes through zero.
  • the switch 36 is open or off through most of the AC cycle in FIG. 3
  • the energy delivered from the pump power supply 35 to the pump controller 39 is compara tively small.
  • the blood pump 37 operates slowly.
  • the switch 36 is on through most of the AC cycle (see FIG. 2), the energy delivered to the controller 39 is comparatively high and the blood pump 37 will operate comparatively rapidly.
  • the existing conventional blood pump controller remains useful for the purpose of setting upper limits in the speed of the blood pump.
  • the invention 20 provides for immediate and continuous compensation of the speed of the blood pump in response to changes in the patients blood flow.
  • the output of the comparator 30 is reduced and therefore the electronic switch 36 allows a smaller proportion of the pump power supply signal to be conducted to the blood pump (see FIG. 3).
  • the amount of power supplied to the blood pump increases thereby increasing the speed of the pump (see FIG. 2). Accordingly, pump starvation caused by a vacuum-induced collapse of blood lines and blood vessels will be avoided because the pump 37 will operate only at the maximum rate accommodated by the available blood supply.
  • the patient is connected to the dialyzer in a method well-known in the art, the supply line 24 being normally in direct communication with the dialyzer blood circuit upstream from the pump.
  • the auxiliary control 20 is first switched off so as to have no effect on power delivered from the supply 35 to the pump controller 39.
  • the auxiliary control 20 may remain on but the initial reference control 32 adjusted to the maximum so as not to interfere with the selection of a desirable maximum flow rate at the controller 39.
  • the blood pump 37 is energized and the speed of the blood pump is increased by adjusting the pump controller 39 to the desired maximum blood flow.
  • the desired maximum blood flow may be ascertained by observing the negative pressure read-out 23 and increasing the speed ofthe blood pump until the negative pressure reaches a level prescribed by the attending physician.
  • the maximum desired flow can be obtained by increasing the pump speed until the blood line or associated accumulator collapses and then reducing the speed of the blood pump 37 through the controller 39 slightly until full flow results.
  • the auxiliary controller 20 is activated by adjusting the initial reference control 32 at least until it appears from the negative pressure readout 23 that the auxiliary control 20 is monitoring blood flow at essentially the maximum desired rate set by the pump controller 39. It has been found frequently desir able to set the initial reference control on a specific negative pressure reading representing a desirable blood flow rate.
  • the auxiliary control When the initial reference control has been set, the auxiliary control will continuously vary the blood pump speed so as to maintain the negative pressure reading at the preset level. Thus, if the patients blood flow reduces, the auxiliary control 20 will reduce the speed of the blood pump 37 so that the negative pressure reading will not significantly change. Conversely, if the patients blood flow increases, the auxiliary control 20 will increase the speed of the blood pump and prevent the negative pressure level from changing significantly.
  • the most advantageous physical housing for the invention has been found to be an enclosure (not shown) which provides an electrical outlet for the service plug of the conventional blood pump and controller, a meter for reflecting the negative pressure, and a dial plate and dial for setting the initial reference control.
  • an enclosure not shown
  • various power switches, pilot lights, or other indicators may be used in order to monitor the status of the circuit during operation.
  • a blood pump controller responsive to changes in blood flow comprising:
  • a conventional blood pump for displacing blood through an extracorporeal hemodialysis system including a blood-conducting conduit;
  • said means comprising an attachment site means for detachably coupling the blood pump to the power source through the said means; sensing means in said bloodconducting conduit for monitoring the availability of extracorporeal blood to the pump upstream from the pump; and means responsive to the sensing means for selectively and continuously varying the amount of electrical power delivered to the blood pump from the power source thereby continuously varying the pumping flow rate of the blood pump, the magnitude of pumping variation being constantly proportional to extracorporeal blood flow upstream from the blood pump during the course of dialysis.
  • a blood pump controller responsive to changes in blood flow comprising:
  • a blood conduit for conducting blood from a patient to the blood pump
  • transducer means connected to the blood conduit producing an electrical signal representing the availability of blood to the pump
  • comparing means for comparing the transducer signal with a pre-established reference signal and producing a proportional output signal
  • switching means responsive to the output of the comparing means for producing a periodic pulse train wherein the duration of each pulse is proproportional to the output signal of the comparing means, the speed of the blood pump being a direct function of the duration of the pulse.
  • a blood pump controller as defined in claim 2 further comprising means for sensing negative blood pressure upstream from the pump and wherein the switching means comprises means for (a) producing a medium duration pulse when the proportional output signal is at an initial reference level representing a predetermined negative blood pressure, (b) decreasing the pulse duration when the proportional output signal indicates reduced patients blood flow represented by increased negative value of the blood pressure, and (c) increasing the pulse duration when the proportional output signal indicates increased patients blood flow represented by decreased negative value of the blood pressure.

Abstract

An auxiliary control for a blood pump used in hemodialysis which acts upon an existing blood pump controller to continuously vary the pump rate in direct correspondence with changes in flow of a patient''s blood reflected as variations in negative pressure in a blood line. The auxiliary control regulates the pump rate by producing an electrical pulse train in which the duration of the pulses corresponds to changes in negative pressure corresponding to changes in the blood flow rate. The control presents means for achieving a rapid response to changes in the flow of the patient''s blood.

Description

United States Patent 1191 1 1111 3,882,861
Kettering et a1. May 13, 1975 1 AUXILIARY CONTROL FOR A BLOOD 3,656,478 4/1972 Swersey 128/214 E PUMP 3,731,680 5/1973 Wright et a1. 123/214 F 3,756,234 9/1973 Kopp 128/214 R [751 Inventors: Donald ettering. Salt a ty; 3,778,694 12/1973 Hubby et a1. 318/474 Morris E. Jones, Bountiful. both Of 3,799,702 3/1974 Weishaar 128/278 X Utah Primary Examiner-Dalton L. Truluck 7 3] Asslgnee Assists Inc Salt Lake Clty Attorney, Agent, or Ftrm--H. Ross Workman [22] Filed: Sept. 24, 1973 57 CT pp 399,904 An auxiliary control for a blood pump used in hemodialysis which acts upon an existing blood pump controller to continuously vary the pump rate in direct corre- [52] CL 128/214 E; 28/214 F; ZS/DIG l2; spondence with changes in flow of a patient's blood 417/44 [51} Int. Cl A6lm 01/03 reflected as f' m negatwe pressure m a blood [58] Field of Search 128/213 214 R 214 E line. The auxihary control regulates the pump rate by producing an electrical pulse train in which the duration of the pulses corresponds to changes in negative pressure corresponding to changes in the blood flow 128/214 F, 214.2, DIG. l2, DIG. 13; 417/44 56 References Cited 7 1 rate. The control presents means for achievmg a rap1d UNITED STATES PATENTS response to changes in the flow of the patients blood. 3,091,239 5/1963 Moeller 128/214 F D F 3,496,878 2/1970 Hargest et a1 1. 417 14 7 Clam", 3 "awmg gums 39\ PUMP BLOOD. gfl zo CONTROLLER PUMP """i 37 1 22 I so A 1 I 1 PRESSURE AVERAGING COMPARATOR ELECTRONIC TRANSDUCER CIRCUIT SWITCH 1 mp 56 y 28 3| NEGATIVE INITIAL l i 24 PRESSURE REFERENCE Z 'Z PUMP I READOUT CONTROL R TOR POWER //55 i 23 52 34 SUPPLY 1. ..J
1 AUXILIARY CONTROL FOR A BLOOD PUMP BACKGROUND 1. Field of the Invention The present invention relates to an improved auxiliary control for an extracorporeal blood pump used in hemodialysis and more particularly to novel apparatus for controlling the blood pump rate in an extracorporeal hemodialysis system.
2. The Prior Art Historically, kidney diseases have been of critical concern to human life. Many kinds of kidney diseases interfere with the function of the kidney such that the kidney ceases to remove waste and excess water from the blood. When the kidney is sufficiently impaired that a large portion of the waste products and water are not removed from the blood, the life of the patient cannot be preserved unless a way is provided for artificially performing the functions of the impaired kidney through extracorporeal hemodialysis.
Many of the presently known hemodialysis apparatus require the use of a blood pump to provide additional pressure in the withdrawn blood in order to conduct it through the hemodialysis unit. A major problem presented by the presently known blood pumps and associated control apparatus is the inability of such apparatus to provide a minimum time for dialysis while simultaneously preventing pump starvation and the resulting collapse of the supply blood lines. It is well-known that blood should be withdrawn from the patient at a rapid rate so as to reduce the time for dialysis. However, when the blood supply at the patient is insufficient to supply the blood pump, the blood lines and even the patients blood vessels collapse which interrupts effective hemodialysis until adequate blood flow is restored. The collapse of blood lines resulting from insufficient blood supply to a continuously operating blood pump is defined herein as pump starvation." To avoid time consuming and sometimes dangerous pump starvation, it has conventionally been necessary to adjust the pump speed well below an optimum rate to a level which pro vides a wide safety margin in order to avoid pump starvation.
Even with this precaution, however, it is common for the patients blood flow rate to fluctuate significantly during the course of dialysis. Accordingly, the attending physician must choose between (a) lowering the pump rate to accommodate the lowest possible blood flow rate as a safety margin and thereby significantly extending the dialysis time or (b) risk collapse of blood lines and premature interruption of dialysis through pump starvation in the event of a drop in the patients blood flow rate.
Several attempts have been made to produce a pump which is able to compensate for changes in the amount of available blood while the patient is undergoing dialysis. The prior art shows the use of step-wise regulation apparatus which only vary the volume of blood pumped in a series of discrete steps and do not allow for continuously variable changes in the volume of blood pumped. That type of pump and control apparatus requires a threshold level of pressure change before any responsive action is taken. One such step-wise system is shown in U.S. Pat. No. 3,698,381.
Other types of control apparatus have employed specially designed pumps which are mechanically capable of increasing the force applied to a collapsible blood reservoir in order to thereby increase the pressure of blood supplied from the reservoir. One such specialized blood pump and associated control is shown in U.S. Pat. No. 3,592,183.
A major deficiency which is observed in the attempts to solve the regulation of pump starvation is that the solution involves the replacement of all existing pump controllers and/or blood pumps. Until the present invention, it has not been possible to continuously vary the rate of a continuous flow blood pump in response to the availability of blood while retaining the existing conventional blood pump and controller.
BRIEF DESCRIPTION AND OBJECTS OF THE INVENTION The present invention includes novel apparatus for continuously varying the pump rate of a blood pump used in hemodialysis in response to changes in blood flow from the patient so as to maximize the rate of hemodialysis while avoiding pump starvation. Furthermore, the invention provides apparatus which can accomplish the previously described function in combination with existing conventional blood pumps and control mechanisms.
It is, therefore, a primary object of the present invention to provide improved extracorporeal hemodialyzing pump control apparatus.
It is another primary object of the present invention to provide extracorporeal hemodialysis pump control apparatus which cooperates with presently known pumps and associated controls to achieve a continuously variable pump rate responsive to changes in blood flow.
These and other objects and features of the present invention will become more fully apparent from the following description and appended claims taken in conjunction with the accompanying drawing.
BRIEF DESCRIPTION OF THE DRAWING FIG. 1 is a block diagram illustrating a presently preferred embodiment of the invention;
FIG. 2 illustrates a waveform taken at point A in FIG. 1, the waveform particularly showing a signal representation when the patients blood flow has increased during the course of dialysis; and
FIG. 3 illustrates a waveform taken at point A of FIG. 1, the waveform particularly showing a signal representation when the patients blood flow has decreased during the course of dialysis.
DETAILED DESCRIPTION OF THE INVENTION dialyzer by blood pump 37. Accordingly, a negative pressure will exist in blood lines upstream from the pump. If outflow of the patients blood should be limited through stricture, clotting, hypotension or any other of a variety of common circumstances, negative pressureupstream from the pump will increase proportionately. Conversely, negative pressure will decrease as blood becomes more available to the pump.
According to one presently preferred embodiment of the invention, a conventional pressure transducer 22 provides a direct conversion between negative pressure in the blood line 24 and electrical voltage. Blood line 24 connects the pressure transducer to a conduit (not shown) which carries blood from a blood vessel of a patient to the blood pump 37. The electrical qualities of the pressure transducer may be characterized as either a variable resistance or a variable voltage source. Whichever type of transducer is employed or whichever electrical characterization is used, the electrical quantity varies in proportion to the blood flow as measured by the negative blood pressure in line 24. The negative pressure is preferably observable on a conventional readout device 23.
The electrical output signal of the pressure transducer is fed into an averaging circuit 28. The averaging circuit 28 may be any one of a wide variety of known discrete or integrated circuits, the most simplified of which would merely be a capacitor in parallel with the transducer output conductors to accomplish averaging of the systolic and diastolic pressure signal from the transducer 22.
Certain types of pressure transducers which maintain a reservoir of blood and mechanically measure expansion and contraction of a chamber would not require the averaging circuit since the output signal from that type of transducer would be averaged mechanically.
The averaged transducer signal is then conducted to and appears at one of the inputs to a conventional operational amplifier 31 which forms part of the comparator 30. The initial reference control 32 provides a reference signal for the second comparing input of the operational amplifier 31. The initial reference control may be either a fixed or variable voltage divider which provides a pre-established signal level at one of at least two operational amplifier inputs.
The operational amplifier portion 31 of the comparator 30 is used in the summing mode, where the two inputs are added together to form an output to the electr nic switch 36 which output is proportional to the sum of the inputs. The electronic switch 36 preferably comprises a conventional threshold trigger circuit capable of converting the output signal of the operational amplifier 31 into a pulse of duration proportional to the amplitude of the output signal of the operational amplifier. A common, readily available device for performing the function of the electronic switch would be any suitable type of current controlled current source such as a unijunction transistor with an external base to emitter timing capacitance which acts to fire a triac or the like.
The power supply for the operational amplifier portion of the comparator is a pulse generator 34 which produces a generally square wave voltage signal causing the output of the operational amplifier to turn on and off at a constant rate. Any suitable conventional pulse generator having sufficient voltage output to drive the operational amplifier would be acceptable.
It should be recognized that the signal from the operational amplifier is a periodic pulse having an amplitude proportional to the sum of the initial reference signal and the averaged transducer signal. It should be recognized that the higher the output signal from the comparator, the greater the time increment that switch 36 is on, and conversely the lower the signal from the comparator, the shorter the time increment that switch 36 is on.
As shown in FIG. 1, the regular power supply line to a conventional blood pump and controller is diverted through the electronic switch 36. The waveforms shown in FIGS. 2 and 3 are taken at point A in the diagram of FIG. 1, assuming an alternating current power supply like that available at a standard utility outlet. The solid portions of the waveforms represent that portion of the waveforms during which the electronic switch 36 is off. When the switch 36 turns on, it remains on until the AC cycle goes through zero. Because the switch 36 is open or off through most of the AC cycle in FIG. 3, the energy delivered from the pump power supply 35 to the pump controller 39 is compara tively small. Thus, the blood pump 37 operates slowly. Conversely, when the switch 36 is on through most of the AC cycle (see FIG. 2), the energy delivered to the controller 39 is comparatively high and the blood pump 37 will operate comparatively rapidly.
The existing conventional blood pump controller remains useful for the purpose of setting upper limits in the speed of the blood pump. However, the invention 20 provides for immediate and continuous compensation of the speed of the blood pump in response to changes in the patients blood flow. When blood flow decreases, the output of the comparator 30 is reduced and therefore the electronic switch 36 allows a smaller proportion of the pump power supply signal to be conducted to the blood pump (see FIG. 3). Also, if the blood flow of the patient should increase during the course of dialysis, the amount of power supplied to the blood pump increases thereby increasing the speed of the pump (see FIG. 2). Accordingly, pump starvation caused by a vacuum-induced collapse of blood lines and blood vessels will be avoided because the pump 37 will operate only at the maximum rate accommodated by the available blood supply.
In using the invention, the patient is connected to the dialyzer in a method well-known in the art, the supply line 24 being normally in direct communication with the dialyzer blood circuit upstream from the pump. In one preferred method embodiment, the auxiliary control 20 is first switched off so as to have no effect on power delivered from the supply 35 to the pump controller 39. Alternatively, the auxiliary control 20 may remain on but the initial reference control 32 adjusted to the maximum so as not to interfere with the selection of a desirable maximum flow rate at the controller 39.
Subsequently, the blood pump 37 is energized and the speed of the blood pump is increased by adjusting the pump controller 39 to the desired maximum blood flow. The desired maximum blood flow may be ascertained by observing the negative pressure read-out 23 and increasing the speed ofthe blood pump until the negative pressure reaches a level prescribed by the attending physician. Alternatively, the maximum desired flow can be obtained by increasing the pump speed until the blood line or associated accumulator collapses and then reducing the speed of the blood pump 37 through the controller 39 slightly until full flow results.
Once the maximum desired flow has been established in the blood pump 37, the auxiliary controller 20 is activated by adjusting the initial reference control 32 at least until it appears from the negative pressure readout 23 that the auxiliary control 20 is monitoring blood flow at essentially the maximum desired rate set by the pump controller 39. It has been found frequently desir able to set the initial reference control on a specific negative pressure reading representing a desirable blood flow rate.
When the initial reference control has been set, the auxiliary control will continuously vary the blood pump speed so as to maintain the negative pressure reading at the preset level. Thus, if the patients blood flow reduces, the auxiliary control 20 will reduce the speed of the blood pump 37 so that the negative pressure reading will not significantly change. Conversely, if the patients blood flow increases, the auxiliary control 20 will increase the speed of the blood pump and prevent the negative pressure level from changing significantly.
The most advantageous physical housing for the invention has been found to be an enclosure (not shown) which provides an electrical outlet for the service plug of the conventional blood pump and controller, a meter for reflecting the negative pressure, and a dial plate and dial for setting the initial reference control. Of course, various power switches, pilot lights, or other indicators may be used in order to monitor the status of the circuit during operation.
The invention may be embodied in other specific forms without departing from its spirit or essential characteristics. The described embodiment is to be considered in all respects only as illustrative and not restrictive and the scope of the invention is, therefore, indicated by the appended claims rather than by the foregoing description. All changes which come within the meaning and range of equivalency of the claims are to be embraced within their scope.
What is claimed and desired to be secured by United States Letters Patent is:
l. A blood pump controller responsive to changes in blood flow comprising:
a conventional blood pump for displacing blood through an extracorporeal hemodialysis system including a blood-conducting conduit;
a conventional power source and means for delivering electrical power to the blood pump, the pumping capacity of the pump being proportional to the electrical power delivered to the pump;
means electrically interposed between the power source and the blood pump said means comprising an attachment site means for detachably coupling the blood pump to the power source through the said means; sensing means in said bloodconducting conduit for monitoring the availability of extracorporeal blood to the pump upstream from the pump; and means responsive to the sensing means for selectively and continuously varying the amount of electrical power delivered to the blood pump from the power source thereby continuously varying the pumping flow rate of the blood pump, the magnitude of pumping variation being constantly proportional to extracorporeal blood flow upstream from the blood pump during the course of dialysis.
2. A blood pump controller responsive to changes in blood flow comprising:
a conventional blood pump for displacing blood through an extracorporeal hemodialysis system;
a blood conduit for conducting blood from a patient to the blood pump; and
a conventional power source and means for delivering electrical power to the blood pump;
means electrically interposed between the power source and the blood pump, said electrically interposed means comprising:
transducer means connected to the blood conduit producing an electrical signal representing the availability of blood to the pump;
comparing means for comparing the transducer signal with a pre-established reference signal and producing a proportional output signal; and
switching means responsive to the output of the comparing means for producing a periodic pulse train wherein the duration of each pulse is proproportional to the output signal of the comparing means, the speed of the blood pump being a direct function of the duration of the pulse.
3. A blood pump controller as defined in claim 2 wherein said transducer means comprises averaging means for averaging the systolic and diastolic blood pressures.
4. A blood pump controller as defined in claim 2 further comprising means for sensing negative blood pressure upstream from the pump and wherein the switching means comprises means for (a) producing a medium duration pulse when the proportional output signal is at an initial reference level representing a predetermined negative blood pressure, (b) decreasing the pulse duration when the proportional output signal indicates reduced patients blood flow represented by increased negative value of the blood pressure, and (c) increasing the pulse duration when the proportional output signal indicates increased patients blood flow represented by decreased negative value of the blood pressure.
5. A blood pump controller as defined in claim 4 wherein said pulse responsive switching means further comprises means for closing the circuit between the pump and its corresponding power supply for the duration of each pulse.
6. A blood pump controller as defined in claim 2 wherein said comparing means comprises an operational amplifier.
7. A blood pump controller as defined in claim 2, further comprising means responsive to the transducer means for terminating the operation of the blood pump when blood flow is reduced below a predetermined

Claims (7)

1. A blood pump controller responsive to changes in blood flow comprising: a conventional blood pump for displacing blood through an extracorporeal hemodialysis system including a blood-conducting conduit; a conventional power source and means for delivering electrical power to the blood pump, the pumping capacity of the pump being proportional to the electrical power delivered to the pump; means electrically interposed between the power source and the blood pump said means comprising an attachment site means for detachably coupling the blood pump to the power source through the said means; sensing means in said blood-conducting conduit for monitoring the availability of extracorporeal blood to the pump upstream from the pump; and means responsive to the sensing means for selectively and continuously varying the amount of electrical power delivered to the blood pump from the power source thereby continuously varying the pumping flow rate of the blood pump, the magnitude of pumping variation being constantly proportional to extracorporeal blood flow upstream from the blood pump during the course of dialysis.
2. A blood pump controller responsive to changes in blood flow comprising: a conventional blood pump for displacing blood through an extracorporeal hemodialysis system; a blood conduit for conducting blood from a patient to the blood pump; and a conventional power source and means for delivering electrical power to the blood pump; means electrically interposed between the power source and the blood pump, said electrically interposed means comprising: transducer means connected to the blood conduit producing an electrical signal representing the availability of blood to the pump; comparing means for comparing the transducer signal with a pre-established reference signal and producing a proportional output signal; and switching means responsive to the output of the comparing means for producing a periodic pulse train wherein the duration of each pulse is pro-proportional to the output signal of the comparing means, the speed of the blood pump being a direct function of the duration of the pulse.
3. A blood pump controller as defined in claim 2 wherein said transducer means comprises averaging means for averaging the systolic and diastolic blood pressures.
4. A blood pump controller as defined in claim 2 further comprising means for sensing negative blood pressure upstream from the pump and wherein the switching means comprises means for (a) producing a medium duration pulse when the proportional output signal is at an initial reference level representing a predetermined negative blood pressure, (b) decreasing the pulse duration when the proportional output signal indicates reduced patient''s blood flow represented by increased negative value of the blood pressure, and (c) increasing the pulse duration when the proportional output signal indicates increased patient''s blood flow represented by decreased negative value of the blood pressure.
5. A blood pump controller as defined in claim 4 wherein said pulse responsive switching means further comprises means for closing the circuit between the pump and its corresponding power supply for the duration of each pulse.
6. A blood pump controller as defined in claim 2 wherein said comparing means comprises an operational amplifier.
7. A blood pump contrOller as defined in claim 2, further comprising means responsive to the transducer means for terminating the operation of the blood pump when blood flow is reduced below a predetermined level.
US399904A 1973-09-24 1973-09-24 Auxiliary control for a blood pump Expired - Lifetime US3882861A (en)

Priority Applications (12)

Application Number Priority Date Filing Date Title
US399904A US3882861A (en) 1973-09-24 1973-09-24 Auxiliary control for a blood pump
CH1247274A CH582519A5 (en) 1973-09-24 1974-09-13
DK485374A DK156413C (en) 1973-09-24 1974-09-16 BLOOD PUMP CONTROL UNIT
SE7411684A SE411704B (en) 1973-09-24 1974-09-17 Blood Pump Controller.
JP49107859A JPS6231949B2 (en) 1973-09-24 1974-09-20
NL7412448A NL7412448A (en) 1973-09-24 1974-09-20 REGULATOR FOR A BLOOD PUMP.
GB41134/74A GB1487242A (en) 1973-09-24 1974-09-20 Blood pump controller
FR7431876A FR2244546B1 (en) 1973-09-24 1974-09-20
DE2445403A DE2445403C2 (en) 1973-09-24 1974-09-23 Device for regulating the delivery rate of a blood pump in a system for extracorporeal hemodialysis
DD181245A DD115038A5 (en) 1973-09-24 1974-09-23
BE148793A BE820223A (en) 1973-09-24 1974-09-23 CONTROL DEVICE FOR THE PUMP OF A HEMODIALYSIS SYSTEM
IT27602/74A IT1022226B (en) 1973-09-24 1974-09-23 REGULATOR FOR A BLOOD CIRCULATION PUMP

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US399904A US3882861A (en) 1973-09-24 1973-09-24 Auxiliary control for a blood pump

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US3882861A true US3882861A (en) 1975-05-13

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JP (1) JPS6231949B2 (en)
BE (1) BE820223A (en)
CH (1) CH582519A5 (en)
DD (1) DD115038A5 (en)
DE (1) DE2445403C2 (en)
DK (1) DK156413C (en)
FR (1) FR2244546B1 (en)
GB (1) GB1487242A (en)
IT (1) IT1022226B (en)
NL (1) NL7412448A (en)
SE (1) SE411704B (en)

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JPS6231949B2 (en) 1987-07-11
GB1487242A (en) 1977-09-28
DK156413B (en) 1989-08-21
DE2445403A1 (en) 1975-04-03
SE7411684L (en) 1975-03-25
JPS5063790A (en) 1975-05-30
DK156413C (en) 1990-01-22
BE820223A (en) 1975-01-16
CH582519A5 (en) 1976-12-15
FR2244546A1 (en) 1975-04-18
DK485374A (en) 1975-05-20
SE411704B (en) 1980-02-04
FR2244546B1 (en) 1978-04-28
NL7412448A (en) 1975-03-26
IT1022226B (en) 1978-03-20
DD115038A5 (en) 1975-09-12
DE2445403C2 (en) 1983-09-01

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