Fluid pump

• US 7,238,165 B2
• Filed: 02/21/2003
• Issued: 07/03/2007
• Est. Priority Date: 02/21/2002
• Status: Active Grant

• Current Assignee: Design Mentor Incorporated
• Original Assignee: Design Mentor Incorporated
• Inventors: Vincent, Douglas, Murphy, Matthew J.
• Primary Examiner(s): Zalukaeva; Tatyana
• Assistant Examiner(s): Deak; Leslie R.
• Application Number:
  US10/372,023
• Publication Number:
  US 20040015042A1
• Time in Patent Office: 1,593 Days
• Field of Search: 604/4.01, 604/6.09, 604/6.1, 604/6.11, 604 65- 67, 604 7- 10, 604/6.13, 604/6.14, 210/645, 210/90, 422 44- 48, 623/3.1, 623/3.16, 623/3.17, 623/3.11, 222/209, 417/65, 417/85, 417/86, 417/412, 417/426, 417/321, 417/375, 417/410.1, 417/413.1, 417/477.2, 600 16- 17
• US Class Current: 604/6.11
• CPC Class Codes: A61M 2230/005 Parameter used as control input for the apparatus
• CPC Class Codes: A61M 2230/04 Heartbeat characteristics, e.g. ECG, blood pressure modulation
• CPC Class Codes: A61M 60/113 in other functional devices, e.g. dialysers or heart-lung machines
• CPC Class Codes: A61M 60/117 for assisting the heart, e.g. transcutaneous or external ventricular assist devices
• CPC Class Codes: A61M 60/148 in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
• CPC Class Codes: A61M 60/38 Blood oxygenation
• CPC Class Codes: A61M 60/43 using vacuum at the blood pump, e.g. to accelerate filling
• CPC Class Codes: A61M 60/462 Electromagnetic force
• CPC Class Codes: A61M 60/894 Passive valves, i.e. valves actuated by the blood

Abstract

A pumping system 10 provides a physiological pulsatile flow and includes controller 121, a pump drive head 50 coupled to a motor 12 and a fluid housing 52 having at least one port 60. The port 60 includes a ball valve retainer region 69, a valve seat 73, and an occluder ball 71 disposed in the ball valve retainer region 69. During operation, the motor 12 forces the fluid in and out the fluid housing 52 and causes the occluder ball 71 to move from a first position whereby the fluid cannot pass through the port 60, to a second position whereby the fluid moves annular to and generally around the occluder ball 71. This movement creates a slight flow reversal that “breaks up” any blood clots that may form. The pumping system may be used as part of a cardiopulmonary bypass system, a ventricular assist device (VAD) and/or a heart pump.

Claims

1. A pump for pumping a fluid comprising:

at least one linear electromagnetic motor;

at least one pump drive head, coupled to said linear electromagnetic motor, said pump drive head configured for movement in a linear direction;

at least one fluid housing, responsive to said linear movement of said at least one pump drive head, and defining a deformable fluid chamber configured to contain a fluid, said fluid housing including a first and at least a second port, wherein said first port is configured to allow said fluid to flow substantially into said deformable fluid chamber and said second port is configured to allow said fluid to flow substantially out of said deformable fluid chamber, wherein said pump drive head is configured to deform said deformable fluid chamber causing a pressure differential within said deformable fluid chamber thus changing the volume of said deformable fluid chamber and forcing said fluid in or out said deformable fluid chamber through said first and second ports respectively; and

a controller, coupled to said at least one linear motor, and configured to apply an energizing current to said linear electromagnetic motor in a predetermined waveform based upon a maximum positive energizing current value (systole) setting established in said controller, a maximum negative energizing current value (diastole) setting established in said controller, a cycle rate setting established in said controller, and the ratio of maximum positive to maximum negative energizing current value established in said controller such that said controller is configured to cause a maximum volume of fluid for a given pressure at a predetermined time and target pressure to be displaced within said fluid chamber.

2. The pump as claimed in claim 1 wherein said linear electromagnetic motor includes:

a core defining an air gap;

at least one coil disposed around at least a portion of said core proximate said air gap; and

a magnet member located in said air gap and movable in said linear direction.

3. The pump as claimed in claim 2 wherein said pump drive head is coupled to said magnet member.

4. The pump as claimed in claim 1 wherein

said fluid includes blood, and wherein said pump is configured to pump said blood from a venous reservoir coupled to said first port into said outlet port of said first pump and into a patient'"'"'s arterial system.

5. The pump as claimed in claim 1 wherein said pump includes a first and a second fluid housing and a first and a second pump drive head coupled to a first and a second end of said linear electromagnetic motor respectively such that said first and said second pump drive heads are configured to move 180 degrees out of phase with respect to each other.

6. The pump as claimed in claim 1 wherein said pump is configured to be coupled to a patient'"'"'s venous system, and wherein said fluid is blood and said pump is a heart pump providing a pulsatile flow of blood within said patient, wherein said controller is configured to apply said energizing current to said motor in a predetermined waveform based upon said maximum positive energizing current setting established in said controller thereby providing systole blood flow, maximum negative energizing current setting established in said controller thereby providing diastole blood flow, a cycle rate setting established in said controller, and the ratio of systole to diastole blood flow established in said controller such that said pump is configured to provide physiological pulsatile blood flow by ensuring that a maximum volume of blood for a given pressure at a predetermined time and target pressure is displaced within said fluid chamber and within a patient'"'"'s arterial system.

7. The pump as claimed in claim 1 wherein said pump includes an actuator housing coupled to said deformable fluid housing by way of a tube, said actuator housing defining an actuator chamber having an actuation fluid and a deformable wall proximate said pump drive head, said fluid housing containing said fluid to be pumped and including inlet and outlet ports, wherein said pump drive head deforms said deformable wall of said actuator chamber causing said actuation fluid to flow through said tube and deform said deformable fluid housing, thereby creating a pressure differential within said fluid housing which causes said fluid to be pumped to flow through said inlet and outlet ports.

8. The pump of claim 1 wherein said at least one valve is configured to allow for a slight reversal in the flow of said fluid.

9. The pump of claim 1 wherein said valve is selected from the group consisting of a ball valve, a gate valve, a pinch valve, a magnetic valve, a multi leaflet valve and a butterfly valve.

10. The pump of claim 1 wherein said valve includes a ball valve, and wherein said at least one fluid housing includes at least one port, said port including a ball valve retainer region, a valve seat, and an occluder ball disposed in said ball valve retainer region, wherein said pump drive head is configured to deform said deformable fluid chamber and cause a pressure differential within said fluid chamber thus changing the volume of said fluid chamber and forcing said fluid in or out said fluid chamber, wherein said pressure differential causes said occluder ball to move from a first position within said ball valve retainer region whereby said fluid cannot pass through said port, to a second position within said ball valve retainer region whereby said occluder ball is forced against said valve retainer and said fluid moves annular to and generally around said occluder ball, and wherein said movement of said occluder ball from said first position to said second position creates a slight reversal in the flow of said fluid.

11. The pump as claimed in claim 1 wherein said pump includes first and second linear electromagnetic drive motors and a first and a second fluid housing and a first and a second pump drive head coupled to said first and second linear electromagnetic motors respectively, and wherein said controller is coupled to said first and second linear electromagnetic motors and configured to apply an energizing current to each said first and second linear electromagnetic motors in a predetermined waveform such that said first and said second pump drive heads are caused to move 180 degrees out of phase with respect to each other.

12. The pump as claimed in claim 1 wherein said controller is configured to provide physiological pulsatile flow by ensuring that a maximum volume of fluid for a given pressure at a predetermined time and target pressure is displaced within said fluid chamber and output from said pump.

13. The pump as claimed in claim 1 wherein said controller is configured to provide physiological pulsatile blood flow by ensuring that a maximum volume of blood for a given pressure at a predetermined time and target pressure is displaced within said fluid chamber and within a patient'"'"'s arterial system.

14. A cardiopulmonary bypass system configured to provide physiological pulsatile blood flow, the system comprising at least a first pump including:

at least a first linear electromagnetic motor;

at least one pump drive head coupled to said at least a first linear electromagnetic motor, said pump drive head configured for moving in a linear direction;

at least a first deformable fluid housing, responsive to said linear movement of said a least one pump drive head, defining a fluid chamber configured to contain blood, said first deformable fluid housing including an inlet and an outlet port configured for allowing said blood to pass generally into and generally out of said fluid housing respectively, each port including a ball valve configured for moving between a first and a second position wherein in said first position said fluid can pass through said port and wherein in said second position said fluid cannot pass through said port, wherein said pump drive head is configured to deform said deformable fluid chamber causing a pressure differential within said deformable fluid chamber which causes said ball valves to move from said first to said second position and creates a slight reversal in the flow of said blood in said deformable fluid chamber, wherein said first pump is configured to pump said blood from a venous reservoir into said input port and into a heat exchanger, an oxygenator and an arterial filter all coupled to said outlet port of said at least a first pump and into a patient'"'"'s arterial system; and

a controller, coupled to said at least one linear motor, and configured to apply an energizing current to said linear electromagnetic motor in a predetermined waveform based upon a maximum positive energizing current value (systole) setting established in said controller, a maximum negative energizing current value (diastole) setting established in said controller, a cycle rate setting established in said controller, and the ratio of maximum positive to maximum negative energizing current value established in said controller such that said controller is configured to cause said pump to provide physiological pulsatile blood flow by ensuring that a maximum volume of blood for a given pressure at a predetermined time and target pressure is displaced within said fluid chamber and within a patient'"'"'s arterial system.

15. The cardiopulmonary bypass system as claimed in claim 14 wherein said linear electromagnetic motor includes:

a core defining an air gap;

at least one coil disposed around at least a portion of said core proximate said air gap; and

a magnet member located in said air gap and movable in said linear direction.

16. The cardiopulmonary bypass system as claimed in claim 15 wherein said pump drive head is coupled to said magnet member.

17. The cardiopulmonary bypass system as claimed in claim 14 wherein a first and a second pump drive head are coupled to a first and a second end of said first motor and move 180 degrees out of phase with respect to each other, wherein said first and said second pump heads are configured to cause alternating pressure differentials within first and said second deformable fluid housings of first and said second pumps respectively.

18. The cardiopulmonary bypass system as claimed in claim 14 wherein each of said pumps includes an actuator housing coupled to said deformable fluid housings through a tube, each of said actuator housings defining an actuator chamber having an actuation fluid and a deformable wall proximate said pump drive heads, wherein said pump drive heads are configured to deform said deformable walls of said actuator chambers causing said actuation fluids to flow through said tubes and deform said deformable fluid housings, thereby creating a pressure differential within said deformable fluid housings which causes said blood to be pumped to flow through said inlet and outlet ports.