US3572979A - Pumps - Google Patents

Abstract

In a blood pump a fluid pressure circuit is provided which is operative to feed a variable frequency pulsating flow of water to one side of a flexible diaphragm. The other side of the flexible diaphragm is connected into a patient''s bloodstream and thus flexure of the diaphragm results in a pulsatile flow of blood on said other side of the diaphragm. The specification describes a number of devices for alternately applying suction and pressure to the water in said fluid pressure circuit and thereby to the diaphragm as well as describing one practical form of pumping head including such a diaphragm.

Description

United States Patent [72] Inventor Paul Greville Morton c/o The English Electric Company Ltd., Stafford, England [21] Appl. No. 809,681 [22] Filed Mar. 24, 1969 [45] Patented Mar. 30, 1971 [32] Priority Mar. 22, 1968 [33] Great Britain [31 14005/68 [54] PUMPS 5 Claims, 9 Drawing Figs.

[52] US. Cl 417/390, 417/427,128/1 [51 Int. Cl F04b 9/08,F04b 17/00,F04b 35/00 [50] Field ofSearch 103/152, 45; 417/390, (lnquired); 128/1 (Rand Heart-Lung Digest) [56] References Cited UNITED STATES PATENTS 491,116 2/1893 Keeney 103/152 2,186,972 1/1940 Hollander et a1. 103/152 2,815,715 12/1957 Tremblay 103/152 3,048,121 8/1962 Sheesley..... 103/152 3,208,448 9/1965 Woodward. 103/152 3,250,226 5/1966 Voelker 103/152 3,451,347 6/1969 Chimura 103/152 Primary ExaminerWilliam L. F reeh Assistant Examiner-John J. Vrablik Attorneys-Misegades & Douglas, Keith Misegades and George R. Douglas, Jr.

ABSTRACT: In a blood pump a fluid pressure circuit is provided which is operative to feed a variable frequency pulsating flow of water to one side of a flexible diaphragm. The other side of the flexible diaphragm is connected into a patients bloodstream and thus flexure of the diaphragm results in a pulsatile flow of blood on said other side of the diaphragm. The specification describes a number of devices for alternately applying suction and pressure to the water in said fluid pressure circuit and thereby to the diaphragm as well as describing one practical form of pumping head including such a diaphragm.

Paliehid Mar-1150, i971 5 Sheets-Sheet 1 Patented March 30, 1971 3,572,979

5 Sheets-Sheet 2 FIG. 3

FIG.4

PUMPS This invention relates to pumps for use in cardiac surgery.

The roller-type pump used in present-day cardiac surgery has the disadvantage that the outflow of blood from the pump is essentially of a nonpulsating nature thus being different from the natural outflow of blood from a heart, and furthen more the very localized squeezing action applied by the rollers through a flexible diaphragm to the blood itself during operation of such a roller-type pump results in damage to the constituents of the blood.

According to this invention, a pump for use in cardiac surgery includes a housing separated into two areas by a flexible diaphragm, one of the areas being adapted for connection into a patients bloodstream for taking over the function of the patients heart, and the other area forming part of a control fluid circuit which is operable to apply a pulsating control fluid pressure to said other area whereby to cause a pulsating flow of blood from said one area.

Preferably, two lines are provided from said one area for connection into the patients bloodstream, each line being provided with a nonretum valve and the valves being arranged so that one valve permits flow into said one area and the other valve permits flow from said one area.

The housing and the flexible diaphragm may be in the form of tubes, in which case the diaphragm tube is mounted coaxially within the housing tube and is sealed to the latter at its ends, the bore of said tube constituting said one area and an annular space between said tubes constituting said other area, and said nonreturn valves are carried by end fittings for the housing tube.

It will be appreciated that the frequency of pulse of said pulsating control fluid pressure may be varied so as to vary the frequency of the pulsating flow of blood.

in a preferred form of this invention the control fluid in the control fluid circuit is an incompressible fluid.

The control fluid circuit may include first conduit means providing communication between said other area and a pressure source of said control fluid, second conduit means providing communication between said other area and a suction source of said control fluid, valve means for controlling communication between said other area and said pressure source on the one hand and said suction source on the other hand, and actuating means adapted to actuate said valve means such that the control fluid pressure and the suction pressure are applied separately to said other area whereby to apply said pulsating control fluid pressure.

The valve means may comprise a spool valve unit and, where the control fluid is an incompressible liquid (for example water), the spool valve unit may be mounted within a reservoir of the control liquid so as to be completely submerged within the liquid.

The present invention conveniently enables a blood pump to be produced for use in cardiac surgery which is sterile, easily cleaned, rugged, easily operated and cheap, and which can provide a pulsating outflow of blood without subjecting the blood to a localized squeezing action, and furthermore, which may be adjusted to provide a pulsating blood flow of a desired frequency so as to simulate the output of a heart.

Embodiments of this invention will now be described, by way of example, with reference to the accompanying drawings, oiwhich:

FIG. ii is a schematic diagram illustrating the principle of Lil FIG. 6 is a third practical embodiment of a valve and valve actuating mechanism for a blood pump according to this in-. vention,

HG. 7 illustrates a practical embodiment of a pumping head for use in a blood pump in accordance with this invention,

FIG. 8 is a schematic circuit diagram of electrical means for operating the actuating device according to another preferred embodiment of the invention, and

FIG. 9 shows a circuit waveform of the pressure signal applied to thepipe 13 of FIG. 5.

Referring to FIG. 1, a blood pump includes a pumpinghead 10 which comprises a housing 11 divided internally into twoareas 12 and 13 by aflexible diaphragm 14.

Thearea 12 on one side of the diaphragm M is provided with twononreturn valves 15 and 16 arranged so that one permits flow into thearea 12 and the other permits flow out from thearea 12. The pumpinghead 10 is. adapted to be connected into the patients blood system by way of thenonretum valves 15 and 16, thearea 12 providing a bypass around the patients heart.

Thearea 13 on the other side of the diaphragm l4 forms part of a control fluid circuit. The control fluid circuit is a closed circuit, that is a circuit in which no fluid losses have to be made up. The preferred fluid is water. The area i3 is connected to adevice 17 by apipe 18. The control fluid circuit also includes twocentrifugal pumps 19 and 20, areservoir 31 andpipes 22 to 26 respectively connecting the output of the pump w to the device K7, the input of thepump 19 to thereservoir 21, the output of thepump 20 to thereservoir 21, the input of thepump 20 to thedevice 17, and thereservoir 21 to thedevice 117. The surface of the water contained within the reservoir is open to atmosphere.

Thedevice 17 includes valve means. for connecting thepipe 22 to thepipe 18 or thepipe 26 so that the output of thepump 19 is placed in conduit communication with either the area E3 or thereservoir 21. The device l7 also includes valve means for connecting thepipe 25 to thepipe 18 or to thepipe 26 so that the input of thepump 20 is placed in conduit communication with either thearea 13 or thereservoir 21.

In operation of the blood pump, the pumps l9 and 20 are driven continuously so that water is circulated around the closed control fluid circuit. The water pressure in thearea 13 governs the position of the diaphragm l4 and movement of the diaphragm causes blood to be drawn into or expelled from thearea 12 through theappropriate valve 15 or M. It will be seen that when the output of the pump i9 is first connected to thearea 13 through the actuating device l7, the diaphragm M is deflected suddenly so that blood is suddenly expelled from thearea 12. it will also be seen that when the conduit communication between the output of thepump 19 and thearea 113 is blocked by the diversion of the water through thedevice 17 to the reservoir 2i, and when the input of thepump 20 is connected to thearea 13 through thedevice 17, suction pressure is applied by thepump 20 to the diaphragm id drawing the diaphragm towards thedevice 17 and. sucking blood into thearea 12. it will be understood that by suitably controlling the interconnection between thepipes 22;, 25 and 26 on the one side of thedevice 17 andpipe 18 on the other side of thedevice 17 the pressure in the area l3 acting on the flexible diaphragm can be varied in a pulsating manner so that the outflow of blood from the area l2 is correspondingly pulsatiie. Furthermore, it will be understood that the frequency of pulse can be varied to suit requirements.

it will be appreciated that various refinements and modifications to the system illustrated in FIG. 1 may be employed without departing from the basic principle of operation. For example, it is not essential to have aclosed control water circuit; where the water supply pressure is suitable thepipe 22 may be connected to a domestic water tap, thus dispensing with the pump l Furthermore, it is not essential to connect thepipe 25 to thepipe 26 when it is not required to apply the suction pressure to the area l3; thepipe 25 may simply be blocked by any convenient means. Moreover, it is not essential to employ a centrifugal pump Zll; any other suitable means for providing the required suction pressure may be employed, for example a standard venturi device.

Experiments have been carried out and these show that, in a blood pump in accordance with this invention, the pump w should preferably be capable of supplying water at a rate of flow sufficiently great to eject the full stroke volume (that is up to 30 ccs. in the case of a dog and up to 100 ccs. in the case of a man) from thearea 12 in less than 0.1 seconds. This needs a water pump capable of delivering, in the case of a dog, greater than 4 gallons per minute, and for a man, greater than 13 /2 gallons per minute. The suction device 2i should preferably be capable of applying a vacuum of more than feet of water at flow rates of about 1 gallon per minute and 4 gallons per minute for dog and man respectively.

Referring to the embodiment illustrated in FIGS. 2 and 3, there is illustrated a practical form of thedevice 17 of FIG. 1. Where appropriate the reference numerals of FIG. I have been applied to the corresponding parts. The centrifugal pump 2h! is replaced by a water jet pump which operates on the ventuzi principle. The inlet of thepump 36 is connected to the reservoir (not shown) through a pipe Ell, and thepipe 25 is connected to anintermediate port 32 of the pump 34).

The threepipes 22, 25 and 26 are passed through a valve mechanism of the actuating device l7. in this arrangement thepipe 26 is a branch from thepipe 22, the connection being upstream of the valve mechanism.

The valve mechanism includes three pairs of opposed anvils, theupper anvil 33 of each pair being carried by afixed bar 34 and thelower anvil 35 of each pair being carried by the end of a corresponding one of three levers as which are pivotally mounted at their other ends on arod 37. The actuating means for the valve mechanism comprises acam shaft 38 which extends below the threelower anvils 35 and carries threecams 39, ll), 41, which each cooperate with a corresponding one of thelevers 36. Thecams 39 and 31 are similarly profiled and similarly positioned relative to thecam shaft 38 so that they impart similar movements to their respective cooperatinglevers 36 whereby they control flow through thepipes 25 and 26 respectively. Thecam 46 controls flow through thepipe 22. The relative positions and profiles of thecams 39, 4 .3 and ll can be seen from FIG. 3.

in operation of a blood pump incorporating the arrangement described above, thecam shaft 38 is rotated about its axis. Thusit will be seen that when thecams 39 and 41 hold their corresponding lower anvil member in their uppermost positions, theseanvil members 35 cooperate with their correspondingupper anvil members 33 to close thepipes 25 and 26 which are made of rubber or any other suitable flexible material, leaving thepipe 22 fully open and supplying water under pressure to thearea 13. As thecam shaft 38 rotates, thelower anvil members 35 operated by thecams 39 and 41 fall, opening the correspondingpipes 2 and 26, and thus diverting some of the water under pressure from thepipe 22 to thepipe 26 and also applying suction pressure to thearea 13 through thepipe 25 so as to initially gradually reduce the pressure in thearea 13 until rotation of thecam shaft 38 closes thepipe 22 by way of the cam 4d. Whenpipe 22 is closed no water under pressure is supplied to thearea 13 and full suction pressure is applied. Further rotation of thecam shaft 38 opens thepipe 22 and then closes thepipes 25 and 26, and it will be seen that as thecam shaft 35% rotates, a pulsating control water pressure is applied to thediaphragm 14.

it will be understood that the variation of pressure applied to the diaphragm 1 3 during one rotation of thecam shaft 38 can be varied by suitable selection of cam profiles and cam positions. Moreover, the frequency of pulse of the pulsating control pressure applied and thus of the pulsating flow of blood induced by the blood pump can be altered by varying the speed of rotation of thecam shaft 38. A tap (not shown) may be provided inpipe 22 whereby the flow of water flowing through thepipe 22 may be altered so as to correspondingly alter the amount of blood which is caused to flow by the blood pump.

Referring to FIG. 4, there is illustrated a second practical form of thedevice 17 of FIG. ll. Where appropriate the reference numerals of HG. l have been applied to the corresponding parts. Thedevice 17 in this embodiment comprises a spool valve unit which is immersed within the water contained within thereservoir 21. Consequently the pipe as connecting theactuating device 17 to thereservoir 21 is not required. The spool valve unit has a balanced two-land spool 62. Thespool 42 is mounted for reciprocatory movement within avalve body 43. Thepipes 18, 22 and 25 are connected to the valve body in such a way that thespool 42 connects either thepipe 22 or thepipe 25 to thepipe 13 and blocks the other.'A bearinghousing 44 is mounted on thevalve body 43 so as to support a crank 35 for rotation. The radially outer end of thecrank 35 is pivotally connected to one end of a connecting rod as, the other end of the connecting rod being pivotally connected to anextension member 47 carried by thevalve spool 32.

In operation of a blood pump incorporating the actuating device described above, thecrank 45 is rotated continuously so that thevalve spool 52 is reciprocated within thevalve body 43 through the connectingrod 46 and theextension member 37. Reciprocation of thevalve spool 42 connects thepipe 22 or thepipe 25 to thepipe 18 alternately, thus applying pressure or suction to the flexible diaphragm l4 alternately, as in the arrangement described hereinbefore with reference to F168. 2 and 3. The length of the connectingrod 46 may be adjusted so that thevalve spool 42 dwells longer in either the pressure applying or suction positions as required. As in the previous embodiment, the frequency of the pulsating pressure applied to the diaphragm l4, and thus the frequency of the pulsating flow of blood expelled from the pump, may be altered by varying the speed of rotation of thecrank 45, and the flow of the water flowing throughpipe 22 may be altered so as to alter the amount of blood which is caused to flow by the blood pump.

Location of the spool valve unit below the level of water in thereservoir 21 permits said valve to be made with liberal tolerances, since water leakage and air entrainment due to a poorly fitting spool are no problem.

Referring to PK]. 5, this shows a modified form of the arrangement of H0. 4} and like parts have been given the same reference numerals. In this modified arrangement, thespool valve 43 is carried by ascrew device 67 which is arranged with the longitudinal axis of its threadedpart 63 vertical and with the threaded part engaged in two longitudinally aligned tappedblocks 69, 70 carried one at each end of thevalve body 43. The screw device 6'7 is mounted in a fixedstructure 71 outside thereservoir 21 in such a way that it is prevented from moving along its longitudinal axis but may be rotated about that axis. The valve body 4 13 is orientated in such a way that the longitudinal axis of the spool 82 is vertical and is suitably held against lateral movement so that rotation of the threaded part as of thescrew device 67 causes vertical movement of thevalve body 43.

in this modified arrangement, theextension member 37 described with reference to FIG. 4 for connecting thespool 62 to the connectingrod 46, is replaced by aspring coupling 72 which is flexible in bending but is fairly stiff in tension. The bearinghousing 44 of H6. 4 is also dispensed with, thecrank 45 being in the form of an eccentric and being supported by ashaft 73 by which it is rotatably driven.

The operation of this modified arrangement is the same as for the arrangement of FIG. 4,, except that the adjustment, whereby the spool d2 dwells longer in the pressure-applying or suction position as required, is efiectcd by rotation of thescrew device 67 so that thevalve body 43 is raised or lowered relative to thespool 42.

Referring to PM). 6, there is illustrated a third practical form of thedevice 117 of $16. i employing a spool valve in a manner similar to the embodiments of H63. 4 and 5. Where appropriate, the reference numerals of FlGS. l, 4 and 5 have been applied to the corresponding parts.

in this arrangement a three-land spool valve 48A is mounted below the level of water in thereservoir 21 with the longitudinal axis of itsvalve spool 42A vertical. The bottom port of thespool valve 48A opens directly into the reservoir the other three ports are connected to thepipes 13, 22 and in a similar manner to the spool valve 453 of H6. 5, so that t, espool valve 43A controls the flow of water through the pipe in much the same way. Athreeland spool valve 49 is also mounted below the water level within thereservoir 21 with the longitudinal axis of itsspool 50 vertical. The spaces below the lower land of eachspool valve 48A and 49 are connected together by a pipe $1 which is also connected to the space below apiston 52 in a cylindrical 53. Thecylinder 53 is also mounted below the water level within thereservoir 21 with its longitudinal axis vertical. Thepiston rod 54 of thepiston 52 and the valve spools 412A and 50 all extend vertically and are loaded respectively withweights 55 to 57.

The spool valve d9 has fourports 58 to s1 respectively which are spaced apart from each other vertically, the lowermost port being theport 53. Theport 58 opens directly into thereservoir 21, theport 59 is connected to thepressure pipe 22 through abranch pipe 62, the port oil is connected to thepipe 51 through abranch pipe 63, theport 60 is connected to the pipe i through abranch pipe 63, and theport 61 is connected to thesuction pipe 25 through a branch pipe 6d. The three lands of thespool 50 are arranged so that the port so communicates with either theport 61 or theport 59 and thus with either suction or pressure, through the space between the upper and middle lands of the spool, and so that theport 58 always cornmunicates with the space between the middle and lower lands of the spool 5t) and is never connected to either of theports 59 or M. Thecylinder 53 carries an adjustable stop M which is abutted by the topside of thepiston 52 at the top of the pistons stroke.

in operation of a blood pump incorporating the actuating device described above, thespool valve 48A controls the supply or" lluid pressure to the pumping head through the pipe lid in much the same way as has been described above with reference to FIGS. 4 and 5. The difference between the embodiment of FIGS. 4 and 5 and the present embodiment lies in the actuation of thevalve spool 42A.

Starting from the normal rest position in which the valve spools 42A and 5d and thepiston 52 are at the bottom of their respective strokes and in which the ports communicating with the respective pressure-applyingpipes 22 and 62 are open, when water under pressure is supplied through thepipes 22 and so, it is applied to the flexible diaphragm id of the pumping head lid through thespool valve 48A and the pipe l8 and to the area under thepiston 52 through thepipes 63 and 51. Thepiston 52 moves vertically upwards against the action of theweight 55, until it abuts stop 7d, whereupon there is a buildup of water pressure beneath the lower lands of thespools 42A and 5h forcing the spools to move vertically upwards against the action of therespective weights 5s and 57. The inertia of this upward movement carries thespools 42A and 50 through the point at which they close the respective ports communicating with the respective pressure-applying passages .32. and as to the position in which they open the ports which are in communication with therespective suctionapplying passages 25 and 6d. it will now be appreciated that suction pressure is applied to the flexible diaphragm M and to the area below thepiston 52 so that thepiston 52 descends under the influence of itsweight 55.

Once thepiston 52 reaches the bottom of thecylinder 53 the suction pressure acts upon the underside of the lower lands of the valve spools 42A and 59 causing them to descend under the influence of their respective weights es and 57. This downward movement carries thespools 42A and 5t through the point at which they close the respective ports communicating with the respective suction-applyingpassages 25 and as to the position in which they open the ports which are in communication with the respective pressure-applying passages 21B and as. it will be understood that once this cycle of motion of the valve spools and the piston has been initiated, it will continue as long as water pressure and suction pressure are applied through therespective pipes 22 and s2, and 2d and lid.

The magnitude of the weight ss may be adjusted so that the valve spool dZA dwells longer in either the pressure-applying or suction-applying positions as required. The frequency of the pulsating flow of water supplied to the diaphragm M through thepipe 18 may be altered by adjusting throttle valves 7d provided in the pipes 5i, s2 and! 64, or by adjusting the position of the stop 74), or by altering the magnitude of theweights 55 to 57, and the volume of water flowing into thepipe 18 may be altered by adjustingthrottle valves 76 provided in thepipes 22 and 25.

Springs may be employed in place of theweights 55 to 57. Such springs would preferably be compression springs acting on the topside of thespools 42A and 50 and of thepiston 52. However, should the weight of the spools i2, 50, and thepiston 52 be sufficient to ensure movement of the spools through the midposition (that is the position shown in FIG. s where the lands block both the pressure and the suction ports) then external loading means such as theweights 55 to 57 or the compression springs referred to above may be disposed with. I

it will be appreciated that both thespool valves 48A and 49 may be replaced by twoland spool valves 48 of HG. 5. However, in this embodiment it would be: necessary for the valve spool of such a two-land spool to be very good sliding fit in the valve body in order to minimize the likelihood of water under pressure from thepipes 22 or 62 leaking past the lower land into thepipe 51. Use of three-land spools as in the arrangement of FIG. 6 avoids this problem.

Referring to FIG. 7, there is illustrated a suitable form of pumping head it) which may be employed in a blood pump in accordance with this invention. The pumping head ii) is generally tubular in form with the nonreturn valves l5 and 16 being located at each end of the head! ll). Extending between the twovalves 15 and lo and surrounding the appropriate inlet or outlet of the respective valve l5, rs, is a thin tube of flexible material, such as suitable rubher or polythene, which acts as the flexible diaphragm M separating the areas l2 and i3. Coaxially surrounding the tubular diaphragm id is athick tube 65 of a transparent plastics material, although it is to be understood that any other suitable material may be employed. Thetube 65 is clamped at each end to the respective valve body of the correspondingvalve 15, to, by screwed end fittings or. The tubular diaphragm id has enlarged shaped end portions s7 which fit into correspondingly shapedannular grooves 68 in the respective valve bodies; theshaped end portions 67 are clamped between thetube 65 and said respective valve bodies by the end fittings or. Thepipe 18 extends radially through the wall of the tube as and opens into the area l3 at a position adjacent theinlet valve 15 via an annular water feed groove lilA formed in thetube wall 65, which groove prevents the diaphragm id from'bloclting the pipe opening in operation.

in operation of the pumping head it) illustrated in FIG. 7, it will be seen that when water under pressure is supplied through thepipe 18 it forces its way around the tubular flexible diaphragm l4 inside the thick tube as and presses the tubular flexible diaphragm id radially inwards, thus reducing the volume of the area l2 between the two valves l5, l6 and within the tubular flexible diaphragm l4 so as to force blood out of that area l2 through the nonreturn outlet valve l6. Furthermore, it will be understood that when the pressure of the water supplied through the pipe 118 is subsequently reduced and replaced by suction pressure, the flexible diaphragm id is sucked radially outwards until it contacts the inner surface of thetube 65, thereby increasing the volume of thearea 112 and drawing blood into thatarea 112 through thenonreturn valve 15.

it will be appreciated that the pipe Ill opens into the space l3 adjacent thevalve 15 to ensure that a maximum amount of blood may be fed, if required, through the valve l6 during the pressure applying stroke.

All the arrangements described so far have employed an essentially mechanical means'for operating thedevice 17 it is also possible to use electrical means for this purpose, and a suitable circuit is illustrated in FIG. 8. A high-gain amplifier 169, a positive feedback resistor 101, a negative feedback network MP2 and a capacitor 1103 together form a multivibrator which produces an output signal of the form shown in HQ. 9. This signal is applied to the coil lllg A of a reed relay, whose contact 1698 in turn drives the coil llllA of another relay. The contact H63 of the latter relay energizes one or other of two solenoids ill and M2 according as the coil 110A is energized or not. The solenoids lit) and 112 are connected to opposite ends of aspool valve 113 which may be similar to the spool valve 4b of FIG. 5. Thus the pressure signal applied to thepipe 33 will vary substantially, as the waveform ofF 36. 9.

The circuit includes a pair of linkedswitches 104A and 1MB. With these switches in the positions shown, the multivibrator is free-naming; by moving the switches to their other positions, the multivibrator can be synchronized with a patients own heartbeat by means of signals fed in online 114 from a cardiograph.

The operation of the circuit is as follows. Assume that the switches 1104A and 1048 are in the free-running positions as shown, and that the output of theamplifier 100 is slightly positive. This positive output is fed back through the resistor 101 to the positive input to the amplifier, driving its output more positive, so that it immediately saturates with its output at the maximum positive level, This positive output is also applied through the network N32 to the negative input of the amplifier 160; however, thecapacitor 103 is also connected to this negative input, so that the voltage at this negative input can only rise gradually as the capacitor charges through the network MBZ. Eventually however the voltage at the negative input ofamplifier 100 will exceed the voltage at the positive input from resistor MM, and the output of the amplifier will therefore go negative. Resistor 101 will now act to hold the output at its maximum negative level, and this negative level will be fed back through thenetwork 102 to charge thecapacitor 103 in the opposite direction. Eventually, the signal at the negative input of amplifier 1% will again overpower the signal from the resistor tilt at the positive input, and the output will go positive one more. The circuit will continue to switch between positive and negative outputs in this manner indefinitely.

Thenetwork 102 consists of two separate paths. When the output of amplifier llllll is positive,diode 105 is forwardbiassed and current can flow through thevariable resistor 106,diode 107 being cut off; when the output ofamplifier 100 is negative, current can flow throughdiode 107 and variable resistor W8,diode 105 being cut off. By adjusting the resistors we and 108 the durations of the positive and negative outputs from the amplifier th, i.e. of the times t1 and :2 respectively (FIG. 9), can be individually adjusted.

In order to operate the circuit in the synchronized mode, theswitches 104A and 104B are moved to their other positions. The signals online 114 are amplified by anamplifier 115 and coupled over acoupling network 116. Also a variable resistor H7 is connected in series withresistor 106, thus increasing the period tl. This decreases the natural frequency of the multivibrator, so that the synchronizing signal can increase its frequency again to the required value.

The power supply to the relay coil 110A and to the solenoids M1 and 112 may be the AC mains.

lclaim:

E, An artificial heart pump for connection into a vascular system including:

a diaphragm pump having first and second chambers separated by a flexible diaphragm, the first chamber having a first valve through which it can receive blood from the vascular system and a second valve through which it can deliver blood to the vascular systern the second chamber being connected to hydraulic fluid operated control means which causes a pulsating flow of blood through the first said chamber; the hydraulic fluid operated control means including:

a reservoir of hydraulic fluid,

a first pump for pumping fluid from the reservoir into the second chamber of the diaphragm pump to cause blood to flow from the first chamber through the said second valve and into the vascular system, and

a second pump for pumping fiuid from the second chamber of the diaphragm pump into the reservoir to cause blood from the vascular system to flow into the first chamber of the diaphragm pump through the said first valve 4 a spool valve submerged in the hydraulic fluid and comprising a valve body having first, second and third ports therein and a two-land spool slidably mounted within the valve body;

means connecting the first port to the outlet from the first means connecting the second port to the inlet to the second means connecting the third portto the second chamber of diaphragm pump alternatively with the outlet of the first pump and the inlet of the second pump.

2. An artificial heart pump according to claim 1 in which the spool valve is disposed within the reservoir of hydraulic fluid.

3. An artificial heart pump according to claim 1 including means for adjusting the position of the valve body relative to the two-land spool to vary the times during which the second chamber of the diaphragm pump is connected with the outlet of the first pump and the inlet of the second pump.

4. An artificial heart pump according to claim 2 including means for adjusting the position of the valve body relative to the two-land spool to vary the times during which the second chamber of the diaphragm pump is connected with the outlet of the first pump and the inlet of the second pump.

5. An artificial heart pump according to claim 1 in which the diaphragm pump comprises:

an outer rigid tubular member having a port in the wall of the member adjacent one end thereof;

a flexible tubular member disposed within the outer tubular member and spaced therefrom;

an end fitting at each end of the tubular members for sealing each end of the inner tubular member to the adjacent end of the outer tubular member so that the space within the inner tubular member defines said first chamber and the space between the two tubular members defines the second chamber;

the said first valve being accommodated in that end fitting which is adjacent the port in the wall of the outer tubular member;

the said second valve being accommodated in the other end fitting; and

the means connecting the third port of the spool valve to the second chamber of the diaphragm pump including means communicating with the port in the outer tubular member.

Claims (5)

1. An artificial heart pump for connection into a vascular system including: a diaphragm pump having first and second chambers separated by a flexible diaphragm, the first chamber having a first valve through which it can receive blood from the vascular system and a second valve through which it can deliver blood to the vascular system, the second chamber being connected to hydraulic fluid operated control means which causes a pulsating flow of blood through the first said chamber; the hydraulic fluid operated control means including: a reservoir of hydraulic fluid, a first pump for pumping fluid from the reservoir into the second chamber of the diaphragm pump to cause blood to flow from the first chamber through the said second valve and into the vascular system, and a second pump for pumping fluid from the second chamber of the diaphragm pump into the reservoir to cause blood from the vascular system to flow into the first chamber of the diaphragm pump through the said first valve a spool valve submerged in the hydraulic fluid and comprising a valve body having first, second and third ports therein and a two-land spool slidably mounted within the valve body; means connecting the first port to the outlet from the first pump; means connecting the second port to the inlet to the second pump; means connecting the third port to the second chamber of the diaPhragm pump; and means for reciprocating the two-land spool within the valve body so as to connect the second chamber of the diaphragm pump alternatively with the outlet of the first pump and the inlet of the second pump.

2. An artificial heart pump according to claim 1 in which the spool valve is disposed within the reservoir of hydraulic fluid.

3. An artificial heart pump according to claim 1 including means for adjusting the position of the valve body relative to the two-land spool to vary the times during which the second chamber of the diaphragm pump is connected with the outlet of the first pump and the inlet of the second pump.

4. An artificial heart pump according to claim 2 including means for adjusting the position of the valve body relative to the two-land spool to vary the times during which the second chamber of the diaphragm pump is connected with the outlet of the first pump and the inlet of the second pump.

5. An artificial heart pump according to claim 1 in which the diaphragm pump comprises: an outer rigid tubular member having a port in the wall of the member adjacent one end thereof; a flexible tubular member disposed within the outer tubular member and spaced therefrom; an end fitting at each end of the tubular members for sealing each end of the inner tubular member to the adjacent end of the outer tubular member so that the space within the inner tubular member defines said first chamber and the space between the two tubular members defines the second chamber; the said first valve being accommodated in that end fitting which is adjacent the port in the wall of the outer tubular member; the said second valve being accommodated in the other end fitting; and the means connecting the third port of the spool valve to the second chamber of the diaphragm pump including means communicating with the port in the outer tubular member.

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