Blood Pump

This invention relates in general to blood Pumps and more particularly to an implantable pump for replacement for a natural heart or for assistance to the pumping of the natural heart.

A number of designs have been developed for insertable blood pumps to replace or assist a natural heart. Typically such pumps are formed of a collapsible volume which can be filled and emptied with blood to provide pumping action. The shape has generally been ellipsoid with the mechanism for periodically collapsing the volume being pneumatic, hydraulic, or pusher plates. One such pump is the so-called Jarvik heart which employs a flexible membrane forming an inner wall of a rigid chamber, with the pumping being generated by hydraulic pressure against the flexible membrane controlled to provide appropriate stroke volume and repetition rate. Others include pumps with a roller screw, rotary cam, or magnetic actuator to actuate a pusher plate, and a high pressure pumping mechanism.

In many of these heart designs the blood is introduced into the chamber tangentially so that there is a generally rotary movement of the blood in the hemispherical chamber. Such an arrangement, coupled with the non-thrombogenic lining of the inner surface of the chamber is intended to inhibit clot formation. One problem, however, in this arrangement is that at the center of the vortex of the rotation there is a tendency for the blood to stagnate and thus provide a physical basis which can lead to formation of thrombosis. It has been suggested that a pump employing a toroidal shaped chamber completely formed of flexible material can avoid this Problem while still maintaining the generally circular flow of blood. One drawback to this configuration is the tendency of that flexible wall to kink or fold as it is contracted and expanded for pumping action. Such kinks or folds result in high local strain on the membrane material, thereby providing a limited lifetime for the pump.

It is therefore a primary object of the present invention to provide a fluid driven blood pump with a toroidal shape to avoid stagnation of portions of the blood by employing a toroidal shaped blood flow chamber.

It is another object of this invention to provide a blood pump for efficient circulation of blood employing hydraulic pumping wherein the parts of the chamber are constructed interpositioned to allow to provide for long component life.

It is finally an object of the present invention to provide a toroidal shaped Pump which not only wraps in Physical form conveniently around a cylindrical hydraulic actuator, but also provides for flexible membrane movement only on one axis, transverse to the direction of blood flow. This provides effective pump action with a toroidal blood flow, yet avoids kinking or folding, resulting in good fatigue characteristics and a long lifetime for the pump, as well as minimizing the formation of clots.

Broadly speaking, in the present invention a toroidal shaped blood pumping chamber is formed with one rigid exterior wall and includes a flexible membrane wall sealed to the rigid wall thereby forming a toroidal chamber with a rigid upper one half toroid and a flexible membrane lower half toroid. This toroidal chamber has at least its flexible portion enclosed within a fluid pressure chamber, which may be either pneumatic or hydraulic and is coupled to a suitable pneumatic or hydraulic pump. Fluid is pumped into and out of the pressure chamber with a controlled periodic variation in pressure to provide blood Pumping action by driving the membrane to move only along an axis transverse to the direction of flow of the blood. The toroidal chamber is tangentially coupled to the blood supply in the inlet port and provides blood flow from a tangentially coupled outlet port into the circulatory system.

This configuration provides the advantages of toroidal flow of having no stagnant center Portion, while the unidirectional movement of the membrane provides for long life for this component. The toroidal chamber may conveniently be wrapped around a cylindrically formed hydraulic actuator to provide a compact package. In practice, the moving and stationary walls of the toroidal blood chamber are formed of one seamless elastomer material.

In the drawings:

FIG. 1 is a plan view of a pumping chamber constructed in accordance with the principles of this invention;

FIG. 2 is an illustration in cross sectional view of the pumping chamber of FIG. 1;

FIG. 3a is a plan view of a blood pumping chamber assembled around a hydraulic pumping unit;

FIG. 3b is an illustration partially in perspective and partially in cross sectional view of the blood pump assembly of FIG. 3a showing a pair of blood pumps positioned around the hydraulic pump unit;

FIG. 4 is a cross sectional view of one embodiment of a hydraulic pump suitable for use in the practice of this invention;

FIG. 5 is a cross sectional view of the hydraulic pump of FIG. 4 in a plane perpendicular to the plane of FIG. 4.

FIG. 6 is a generally diagrammatic view of the blood pump assembly constructed in accordance with the principles of this invention.

With reference now to FIGS. 1 and 2, a toroidal shaped blood pumping chamber 11 is formed with a rigid wall forming the upper half and a flexible membrane 11b forming the lower half of the toroid chamber 11. The chamber includes an inlet port 15 and an outlet port 17, each coupled to the rigid portion of the chamber at an angle such that blood flow into and out of the chamber is tangential to the circumference of the chamber. The entire toroidal chamber 11 is immersed within a rigid walled pressure chamber 17 which has a fluid input port 19, which is out of the moving plane of the flexible membrane 116. In this embodiment the pressure chamber is a hydraulic chamber.

In operation, a hydraulic pump 27, as illustrated in FIGS. 3a and 3b is coupled to the hydraulic input port 19 to provide in controlled Periodic cycles, increases and decreases of pressure within it thereby causing the flexible membrane 11b to flex in a direction generally parallel to the axis of the toroid, thereby decreasing and increasing the volume enclosed by the rigid wall 11a and the flexible membrane 11b. In general the these increases and decreases in pressure should be substantially evenly applied around the toroid and the membrane 11b should flex only in the direction parallel to the axis.

A suitable material for the toroid has been found to be thin (between approximately 0.25 and 0.5 mm) polyurethane formed into a generally toroidal shape. In order to provide for the rigid portion of the toroidal chamber, approximately half of the toroid is coated with a suitable epoxy such as Stycast Epoxy 1267 manufactured by Emerson & Cummings, Woburn, Masssachusetts, which can have a thickness any where from 0.2 to 5.0 mm, thereby providing for a completely sealed chamber having a rigid wall and a flexible membrane wall. The free length of the membrane should be sufficient to allow full collapse but not long enough to cause folds. Suitable dimensions for the chamber 11 include a displaced volume of 70 cubic cm, an outer diameter of approximately 10 cm and an inner diameter of the toroid of approximately 5.5 cm. Alternatively the rigid portion may be formed of a thicker walled section of elastomer.

As illustrated in FIGS. 3a and 3b hydraulic pump 27 may be fabricated in a generally cylindrical form and appropriately valved to provide for controlled pulsatile flow of hydraulic fluid into and out of the hydraulic chamber 13.

As is shown, particularly in FIGS. 3a and 3b, the toroidal chamber 11 is coupled through its inlet and outlet port and one-way leaflet valves 25 and 28 to provide for blood flow, in this instance in a clockwise fashion around the toroid. In a total implanted heart configuration, the valve 25 would be placed at the outlet of an atrial cuff 23 which can be sewn to the portion of the circulatory system which, in a natural heart, would be coupled to one of the atria of the natural heart. In either instance the valves are located out of the plane of the flexing part of the torus so that they do not distort its shape. The blood outflow through valve 28 would be coupled to either the aorta or the pulmonary artery in an individual circulatory system. Artificial valves suitable for this purpose are known in the art. One particularly suitable type of valve is described in U.S. Pat. application Ser. No. 06/720,361, filed May 1, 1985 and entitled Prosthetic Heart Valve. Mechanical valves such as those manufactured by Bjork-Shively Medronic-Hill or St. Jude Corp. could also be utilized. In general, in this configuration the displaced volume. Of the toroidal chamber is approximately 70 cubic cm with an effective stroke volume in the pumping made of 60 cubic cm. The inner diameter of the inlet and outlet ports is approximately 20 to 25 mm, which is compatible with a 25 mm diameter artificial leaflet valve.

The pressure waveform in the hydraulic fluid will then reflect the pressure in the blood vessels accessed by the open valve. It takes the form of an approximately rectangular wave, with Pressure during systole equal to the arterial pressure supplied by the ventricle, and pressure during diastole equal to the central venous pressure filling the blood pump. These pressure waves may be sampled at appropriate times with a pressure sensor to obtain signals for control of the hydraulic fluid pump speed.

In FIG. 3b a second toroidal blood pump 21 is shown positioned around the hydraulic pump so that the total assembly would provide for both right and left ventricle pumping. As will be described in more detail below, the hydraulic pump 27 can be arranged so that the hydraulic pressure is valved and applied alternately to blood pump 11 or blood pump 21.

A particularly suitable pump for operating this toroidal blood pump has been found to be a centrifugal pump. Such a pump is illustrated in FIGS. 4 and 5. The hydraulic pump includes an electrical pump motor 40 which drives impeller 35 to produce flow of the hydraulic fluid contained within the cavity 36 formed by housing 38. The valving action is accomplished by a rotating valve 39 driven by a valve motor 44 to control the hydraulic fluid output flow to pass alternately through hydraulic output ports 41 and 42. One of these outlet ports, for example, port 41, may be coupled to toroidal chamber 11, while the other would be coupled to toroidal chamber 21.

A suitable electric motor for driving a centrifugal pump of this design is that manufactured by Inland Motor of Sierra Vista, Arizona under the name RBE Motor Series. A suitable beat rate is slightly faster than the natural heart, for example, 80 to 160 beats per minute. To accomplish the control function, it may be desirable to have a sensor 46 sensing the spacing between the membrane 11b and the rigid wall 11a of the toroidal cavity. This sensor may, for example, be an optical sensor providing an output signal indicative of the variation of this spacing as a measure of the change in stroke volume to a suitable electrical control circuit (not shown).

In FIG. 6 there is illustrated an appropriate configuration for a total artificial heart employing the toroidal chamber and a centrifugal hydraulic pump. In FIG. 6 like numbers refer to like parts of the previous figures. Also included in the artificial heart configuration of FIG. 6 is an additional volume compensation chamber 50, also formed as a toroidal chamber which can be hydraulically coupled to the hydraulic chamber of the right blood pump 11 and fluidically coupled to the blood volume 11 in the left atrium, which is valved into the left blood pump 21 to provide for asymmetrial pumping of the left and right ventricles of the artificial heart. A pump of the configuration of FIG. 6 can be formed with an outer dimension of the toroidal chambers of less than 11 cm with axial dimension of less than 9 cm.

Having described the invention it will be realized that the pump may be formed of different materials and in different configurations. For example, the hydraulic pump and valves may be reciprocally operating rather than rotationally. The operation may be accomplished pneumatically, with pressurized gas, as is done in the Jarvik heart, as well as hydraulically utilizing a liquid. Another actuation method is by mechanical means in the form of a ring push plate attached to the flexing portion of the toroidal pump. The invention is set forth in the following claims.