Energy generation from alternating magnetic field or rotating magnetic field in blood pump

Abstract

To provide collection of electric energy from an alternating magnetic field or a rotating magnetic field generated by a motor.SOLUTION: An extracorporeal blood flow system comprises: a blood pump including a pump rotor coupled to be rotated by a motor; a transducer disposed within operable proximity distance to the rotor, the transducer configured to generate electrical energy in response to a first changing magnetic field associated with rotation of the rotor; and at least one sensor powered by the electrical energy generated by the transducer.SELECTED DRAWING: Figure 1B

Description

[Technical Field]

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS This application claims priority to U.S. Provisional Patent Application No. 63 / 241,326, filed September 7, 2021, the entire disclosure of which is incorporated herein by reference.

[0002] The present disclosure relates to harvesting electrical energy from alternating or rotating magnetic fields generated by motors. In some embodiments, the present disclosure relates to systems and methods for harvesting electrical energy from alternating or rotating magnetic fields generated by electric blood pumps in extracorporeal blood circulation systems and powering electronic devices with the harvested electrical energy. [Background technology]

[0003] 2. Description of Related Art Cardiopulmonary bypass is a technique that bypasses a patient's natural heart and lungs using an extracorporeal device during medical procedures, such as open-heart surgery and treatment of acute respiratory distress syndrome (ARDS). Examples of extracorporeal devices include cardiopulmonary bypass machines and extracorporeal membrane oxygenation (ECMO) machines. To mimic the function of a patient's natural lungs and heart, such extracorporeal devices include an oxygenator that exposes extracted blood to oxygen and removes carbon dioxide, and a blood pump that circulates blood through the oxygenator and back into the patient's circulatory system. Various sensors associated with the oxygenator can be used to collect data and provide information used to control the operating parameters of the extracorporeal device. In conventional systems, such sensors are typically powered by a power source mounted remotely from the oxygenator. Therefore, during setup of the extracorporeal device, a technician connects power cables between the power source and these sensors, which makes such systems more complex and bulky. In addition to lengthening setup time for the extracorporeal device, power cable connections can be inadvertently forgotten or improperly performed, adversely affecting the performance of the medical procedure. In view of the above, there exists a need for an alternative means for powering the various sensors of an extracorporeal blood circulation system and / or other electronic components of an extracorporeal device to simplify the setup and operation of the extracorporeal blood circulation system. Of course, the techniques of the present disclosure may be applied more generally to fluid circulation systems and are not limited to blood circulation systems. Indeed, the techniques of the present disclosure are applicable to any system having a pump or other device that can generate a changing magnetic field, harvest electrical energy from the changing magnetic field, and use it to power one or more electronic devices of the system.

[0004] In electrical technology fields unrelated to extracorporeal devices, Wiegand sensors, first developed in the 1970s, are used to measure the position and velocity, particularly rotational position and rotational speed, of electromechanical components. Wiegand sensors operate by generating voltage pulses in response to a changing magnetic field. The voltage pulses generated by the Wiegand sensor can typically be counted by an electronic processor to determine the number and timing of magnetic field changes. This data can then be correlated to the position and / or rotational speed of the electromechanical component. Currently, Wiegand sensors are not used as a means of generating electrical power by harvesting electrical energy from the changing magnetic field associated with an electric motor to power other electrical components in the field of fluid flow systems. Summary of the Invention [Means for solving the problem]

[0005] In view of the foregoing, the present disclosure relates to devices, systems, and methods for powering sensors and / or other electrical components by harvesting energy from alternating / rotating magnetic fields generated by pumps or other devices with electric motors.

[0006] A first non-limiting exemplary embodiment of the present disclosure relates to an extracorporeal blood flow system comprising: a blood pump including a pump rotor coupled to be rotated by an electric motor; a transducer disposed in operable proximity to the pump rotor, the transducer configured to generate electrical energy in response to a first changing magnetic field associated with rotation of the pump rotor; and at least one sensor, the at least one sensor being powered by the electrical energy generated by the transducer.

[0007] A non-limiting exemplary embodiment 2 of the present disclosure further modifies the non-limiting exemplary embodiment 1 to provide that the motor includes a motor rotor and a motor stator, the motor rotor being configured to rotate relative to the motor stator in response to the motor stator and a second changing magnetic field associated with the motor rotor.

[0008] Non-limiting exemplary embodiment 3 of the present disclosure further modifies non-limiting embodiment 1 or 2 to provide that the transducer is positioned in operable proximity to the motor stator and the motor rotor to generate electrical energy in response to a second changing magnetic field associated with the motor stator and the motor rotor.

[0009] Non-limiting exemplary embodiment 4 of the present disclosure further modifies any of non-limiting embodiments 1 to 3 to provide that at least one of the motor rotor and the motor stator includes a permanent magnet, at least one of the motor rotor and the motor stator includes an electromagnet, and the motor is configured to periodically change polarity of the electromagnet to cause rotation of the motor rotor.

[0010] Non-limiting exemplary embodiment 5 of the present disclosure further modifies any of non-limiting embodiments 1 to 4 to provide that the transducer includes a Wiegand inductor.

[0011] A non-limiting exemplary embodiment 6 of the present disclosure further modifies any of non-limiting embodiments 1-5 to provide that the transducer includes a dynamo.

[0012] Non-limiting exemplary embodiment 7 of the present disclosure further modifies any of non-limiting embodiments 1-6, further comprising an oxygenator including at least one sensor.

[0013] Non-limiting exemplary embodiment 8 of the present disclosure further modifies any of non-limiting embodiments 1-7, providing that the at least one sensor includes at least one of a blood temperature sensor, a blood pressure sensor, a flow sensor, and a distance sensor.

[0014] Non-limiting exemplary embodiment 9 of the present disclosure further modifies any of non-limiting embodiments 1-8 to provide that the rotor is magnetically coupled to the electric motor of the blood pump so as to generate a changing magnetic field when the rotor rotates.

[0015] Non-limiting exemplary embodiment 10 of the present disclosure further modifies any of non-limiting embodiments 1-9 to provide that a drive shaft couples the rotor to an electric motor of the blood pump to rotate the rotor and generate a changing magnetic field as the rotor rotates.

[0016] Non-limiting exemplary embodiment 11 of the present disclosure further modifies any of non-limiting embodiments 1-10, further comprising a controller programmed or configured to receive an output data signal from at least one sensor.

[0017] Non-limiting exemplary embodiment 12 of the present disclosure further modifies any of non-limiting embodiments 1-11 to provide that at least one sensor is configured to wirelessly transmit an output data signal to the controller.

[0018] A non-limiting exemplary embodiment 13 of the present disclosure further modifies any of non-limiting embodiments 1-12, further comprising a heart-lung device including a controller.

[0019] Non-limiting exemplary embodiment 14 of the present disclosure further modifies any of non-limiting embodiments 1 to 13 to provide that the electrical energy generated by the transducer includes a plurality of first voltage pulses, each of which has a substantially constant voltage that is not affected by changes in the rotation speed of the first changing magnetic field.

[0020] Non-limiting exemplary embodiment 15 of the present disclosure further modifies any of non-limiting embodiments 1 to 14 to provide that the electrical energy generated by the transducer includes a plurality of first voltage pulses, each of which has a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field and the second changing magnetic field.

[0021] Non-limiting exemplary embodiment 16 of the present disclosure further modifies any of non-limiting embodiments 1 to 15 to provide that the electrical energy generated by the transducer includes a plurality of second voltage pulses, each having a substantially constant voltage that is not affected by changes in the rotational speed of the first and second changing magnetic fields, and the first voltage pulses are substantially different from the second voltage pulses.

[0022] Non-limiting exemplary embodiment 17 of the present disclosure further modifies any of non-limiting embodiments 1-16, further comprising a converter box for storing and conditioning the electrical energy generated by the transducer so that the electrical energy generated by the transducer is in a form suitable for powering at least one sensor.

[0023] Non-limiting exemplary embodiment 18 of the present disclosure further modifies any of non-limiting embodiments 1-17 to provide that the system is a medical device selected from the group consisting of a cardiopulmonary bypass device, an extracorporeal membrane oxygenator, and a pump-assisted pulmonary protection device.

[0024] A nineteenth non-limiting exemplary embodiment of the present disclosure relates to a fluid flow system comprising: a fluid pump including a pump rotor coupled to be rotated by an electric motor; a transducer disposed in operable proximity to the rotor, the transducer configured to generate electrical energy in response to a first changing magnetic field associated with rotation of the pump rotor; and at least one sensor, the at least one sensor being powered by the electrical energy generated by the transducer.

[0025] Non-limiting exemplary embodiment 20 of the present disclosure further modifies non-limiting embodiment 19 to provide that the motor includes a motor rotor and a motor stator, and the motor rotor is configured to rotate relative to the motor stator in response to the motor stator and a second changing magnetic field associated with the motor rotor.

[0026] Non-limiting exemplary embodiment 21 of the present disclosure further modifies non-limiting embodiment 19 or 20 to provide that the transducer is positioned in operable proximity to the motor stator and the motor rotor to generate electrical energy in response to a second changing magnetic field associated with the motor stator and the motor rotor.

[0027] Non-limiting exemplary embodiment 22 of the present disclosure further modifies any of non-limiting embodiments 19-21 to provide that at least one of the motor rotor and the motor stator includes a permanent magnet, at least one of the motor rotor and the motor stator includes an electromagnet, and the motor is configured to periodically change polarity of the electromagnet to cause rotation of the motor rotor.

[0028] Non-limiting exemplary embodiment 23 of the present disclosure further modifies any of non-limiting embodiments 19-22 to provide that the transducer includes a Wiegand inductor.

[0029] Embodiment 24 of the present disclosure further modifies any of non-limiting embodiments 19-23 to provide that the transducer includes a dynamo.

[0030] Non-limiting exemplary embodiment 25 of the present disclosure further modifies any of non-limiting embodiments 19-24 to provide that the at least one sensor includes at least one of a fluid temperature sensor, a fluid pressure sensor, a flow rate sensor, and a distance sensor.

[0031] Non-limiting exemplary embodiment 26 of the present disclosure further modifies any of non-limiting embodiments 19-25 to provide that the rotor is magnetically coupled to the electric motor of the fluid pump so as to generate a changing magnetic field when the rotor rotates.

[0032] Non-limiting exemplary embodiment 27 of the present disclosure further modifies any of non-limiting embodiments 19-26 to provide that a drive shaft couples the rotor to an electric motor of the blood pump to rotate the rotor and generate a changing magnetic field as the rotor rotates.

[0033] Non-limiting exemplary embodiment 28 of the present disclosure further modifies any of non-limiting embodiments 19-27, further comprising a controller programmed or configured to receive output data signals from the at least one sensor.

[0034] Non-limiting exemplary embodiment 29 of the present disclosure further modifies any of non-limiting embodiments 19-28 to provide that at least one sensor is configured to wirelessly transmit an output data signal to the controller.

[0035] Non-limiting exemplary embodiment 30 of the present disclosure further modifies any of non-limiting embodiments 19-29 to provide that the electrical energy generated by the transducer includes a plurality of first voltage pulses, each having a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field.

[0036] Non-limiting exemplary embodiment 31 of the present disclosure further modifies any of non-limiting embodiments 19-30 to provide that the electrical energy generated by the transducer includes a plurality of first voltage pulses, each having a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field and the second changing magnetic field.

[0037] Non-limiting exemplary embodiment 32 of the present disclosure further modifies any of non-limiting embodiments 19-31 to provide that the electrical energy generated by the transducer includes a plurality of second voltage pulses, each having a substantially constant voltage that is not affected by changes in the rotation speed of the first changing magnetic field, and the first voltage pulses are substantially different from the second voltage pulses.

[0038] Non-limiting exemplary embodiment 33 of the present disclosure further modifies any of non-limiting embodiments 19-32 to further include a converter box for storing and conditioning electrical energy generated by the transducer such that the electrical energy generated by the transducer is in a form suitable for powering at least one sensor.

[0039] Non-limiting exemplary embodiment 34 of the present disclosure further modifies any of non-limiting embodiments 19-33 to provide that the fluid pump is a blood pump and the system is a medical device selected from the group consisting of a cardiopulmonary bypass machine, an extracorporeal membrane oxygenator, a pump-assisted pulmonary protection device, and a hemodialysis machine.

[0040] A non-limiting exemplary embodiment 35 of the present disclosure relates to a method for generating electrical energy for powering at least one electronic device, the method including: in a fluid pump including a magnetic field coupling a pump rotor and an electric motor, rotating the pump rotor to generate a first changing magnetic field associated with the pump rotor; inducing a voltage in a transducer as a result of rotating the first magnetic field, the transducer including a Wiegand inductor, the induced voltage including a plurality of first voltage pulses, each first voltage pulse having a substantially constant voltage that is independent of changes in rotational speed of the first changing magnetic field as the first changing magnetic field rotates; and using the induced voltage as a source of electrical energy to power the at least one electronic device.

[0041] Non-limiting exemplary embodiment 36 of the present disclosure further modifies non-limiting embodiment 35 to provide that the electric motor includes a motor rotor and a motor stator. The motor rotor is configured to rotate relative to the motor stator in response to a second changing magnetic field associated with the motor stator and the motor rotor. The method further includes generating the second changing magnetic field to rotate the motor rotor relative to the motor stator.

[0042] Non-limiting exemplary embodiment 37 of the present disclosure further modifies non-limiting embodiment 35 or 36 to further include inducing an additional voltage in the transducer as a result of rotating the second changing magnetic field.

[0043] Non-limiting exemplary embodiment 38 of the present disclosure further modifies any of non-limiting embodiments 35-37 to provide that at least one of the motor rotor and the motor stator includes a permanent magnet, at least one of the motor rotor and the motor stator includes an electromagnet, and the electric motor is configured to periodically change polarity of the electromagnet to cause rotation of the motor rotor.

[0044] Non-limiting exemplary embodiment 39 of the present disclosure further modifies any of non-limiting embodiments 35-38 to provide that the induced voltage includes a plurality of second voltage pulses. Each second voltage pulse has a substantially constant voltage that is not affected by changes in the rotation speed of the first changing magnetic field. The first voltage pulses are substantially different from the second voltage pulses.

[0045] Non-limiting exemplary embodiment 40 of the present disclosure further modifies any of non-limiting embodiments 35-39, further comprising conditioning the electrical energy generated by the transducer, wherein the electrical energy is conditioned by the converter box such that the induced voltage generated by the transducer is in a form suitable for powering at least one electronic device.

[0046] Non-limiting exemplary embodiment 41 of the present disclosure further modifies any of non-limiting embodiments 35 to 40, providing that the fluid pump is a blood pump, and the system is a medical device selected from the group consisting of a cardiopulmonary bypass machine, an extracorporeal membrane oxygenator, a pump-assisted pulmonary protection device, and a hemodialysis machine. The at least one electronic device powered by electrical energy is selected from the group consisting of a blood temperature sensor, a blood flow sensor, a blood pressure sensor, and a distance sensor.

[0047] A non-limiting exemplary embodiment 42 of the present disclosure relates to an electric system comprising: an electric motor including a rotor, the rotor coupled to be rotated by the electric motor; a transducer disposed in operable proximity to the rotor, the transducer configured to generate electric energy in response to a first changing magnetic field associated with rotation of the rotor; and at least one electronic device, the at least one electronic device being powered by the electric energy generated by the transducer.

[0048] Non-limiting exemplary embodiment 43 of the present disclosure further modifies non-limiting embodiment 42 to provide that the electric motor includes a motor rotor and a motor stator, the motor rotor configured to rotate relative to the motor stator in response to the motor stator and a second changing magnetic field associated with the motor rotor.

[0049] Non-limiting exemplary embodiment 44 of the present disclosure further modifies non-limiting embodiments 42 or 43 to provide that the transducer is positioned in operable proximity to the motor stator and motor rotor to generate electrical energy in response to a second changing magnetic field associated with the motor stator and motor rotor.

[0050] Non-limiting exemplary embodiment 45 of the present disclosure further modifies any of non-limiting embodiments 42-44 to provide that at least one of the motor rotor and the motor stator includes a permanent magnet, at least one of the motor rotor and the motor stator includes an electromagnet, and the motor is configured to periodically change polarity of the electromagnet to cause rotation of the motor rotor.

[0051] Non-limiting exemplary embodiment 46 of the present disclosure further modifies any of non-limiting embodiments 42-45 to provide that the transducer includes a Wiegand inductor.

[0052] Non-limiting exemplary embodiment 47 of the present disclosure further modifies any of non-limiting embodiments 42-46 to provide that the electrical energy generated by the transducer includes a plurality of first voltage pulses, each having a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field.

[0053] Non-limiting exemplary embodiment 48 of the present disclosure further modifies any of non-limiting embodiments 42-47 to provide that the electrical energy generated by the transducer includes a plurality of first voltage pulses, each having a substantially constant voltage that is not affected by changes in the rotational speed of the first and second changing magnetic fields.

[0054] Non-limiting exemplary embodiment 49 of the present disclosure further modifies any of non-limiting embodiments 42-48 to provide that the electrical energy generated by the transducer includes a plurality of second voltage pulses, each having a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field, and the first voltage pulses are substantially different from the second voltage pulses.

[0055] Non-limiting exemplary embodiment 50 of the present disclosure further modifies any of non-limiting embodiments 42-49, further comprising a converter box for storing and conditioning the electrical energy generated by the transducer so that the electrical energy generated by the transducer is in a form suitable for powering at least one electronic device.

[0056] Non-limiting exemplary embodiment 51 of the present disclosure further modifies any of non-limiting embodiments 42-50, providing that the electric motor is a component of a blood pump, and the system is a medical device selected from the group consisting of a cardiopulmonary bypass machine, an extracorporeal membrane oxygenator, a pump-assisted pulmonary protection device, and a hemodialysis machine. The at least one electronic device powered by electrical energy is selected from the group consisting of a blood temperature sensor, a blood flow sensor, a blood pressure sensor, and a distance sensor.

[0057] Further details and advantages of the various non-limiting embodiments detailed herein will become apparent upon review of the following detailed description of the various non-limiting embodiments in conjunction with the accompanying drawings. The present invention provides, for example, the following. (Item 1) 1. An extracorporeal blood flow system, comprising: a blood pump having a pump rotor coupled to be rotated by an electric motor; a transducer positioned in operable proximity to the pump rotor, the transducer configured to generate electrical energy in response to a first changing magnetic field associated with rotation of the pump rotor; at least one sensor powered by electrical energy generated by the transducer; The extracorporeal blood flow system. (Item 2) 2. The system of claim 1, wherein the motor comprises a motor rotor and a motor stator, the motor rotor configured to rotate relative to the motor stator in response to a second changing magnetic field associated with the motor stator and the motor rotor. (Item 3) 3. The system of claim 2, wherein the transducer is positioned in operable proximity to the motor stator and the motor rotor to generate electrical energy in response to the second changing magnetic field associated with the motor stator and the motor rotor. (Item 4) At least one of the motor rotor and the motor stator includes a permanent magnet; at least one of the motor rotor and the motor stator includes an electromagnet; the motor is configured to periodically change polarity of the electromagnet to cause rotation of the motor rotor. Item 2. The system according to item 2. (Item 5) Item 10. The system of item 1, wherein the transducer includes a Wiegand inductor. (Item 6) Item 10. The system of item 1, wherein the transducer comprises a dynamo. (Item 7) Item 10. The system of item 1, further comprising an oxygenator including the at least one sensor. (Item 8) Item 10. The system of item 1, wherein the at least one sensor includes at least one of a blood temperature sensor, a blood pressure sensor, a flow sensor, and a distance sensor. (Item 9) Item 10. The system of item 1, wherein the rotor is magnetically coupled to the electric motor of the blood pump so as to generate the changing magnetic field when the rotor rotates. (Item 10) Item 10. The system of item 1, wherein a drive shaft couples the rotor to the electric motor of the blood pump to rotate the rotor and generate the changing magnetic field when the rotor rotates. (Item 11) Item 10. The system of item 1, further comprising a controller programmed or configured to receive an output data signal from the at least one sensor. (Item 12) Item 12. The system of item 11, wherein the at least one sensor is configured to wirelessly transmit the output data signal to the controller. (Item 13) Item 12. The system of item 11, further comprising a heart-lung machine including the controller. (Item 14) Item 10. The system of item 1, wherein the electrical energy generated by the transducer includes a plurality of first voltage pulses, each first voltage pulse having a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field. (Item 15) 4. The system of claim 3, wherein the electrical energy generated by the transducer includes a plurality of first voltage pulses, each first voltage pulse having a substantially constant voltage that is not affected by changes in rotational speed of the first changing magnetic field and the second changing magnetic field. (Item 16) Item 16. The system of item 15, wherein the electrical energy generated by the transducer includes a plurality of second voltage pulses, each second voltage pulse having a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field and the second changing magnetic field, and the first voltage pulses are substantially different from the second voltage pulses. (Item 17) Item 10. The system of item 1, further comprising a converter box for storing and conditioning the electrical energy generated by the transducer so that the electrical energy generated by the transducer is in a form suitable for powering the at least one sensor. (Item 18) Item 10. The system of item 1, wherein the system is a medical device selected from the group consisting of a cardiopulmonary bypass machine, an extracorporeal membrane oxygenator, and a pump-assisted pulmonary protection device. (Item 19) 1. A fluid flow system comprising: a fluid pump having a pump rotor coupled for rotation by an electric motor; a transducer positioned in operable proximity to the rotor, the transducer configured to generate electrical energy in response to a first changing magnetic field associated with rotation of the pump rotor; at least one sensor powered by electrical energy generated by the transducer; The fluid flow system comprises: (Item 20) 20. The fluid system of claim 19, wherein the motor comprises a motor rotor and a motor stator, the motor rotor configured to rotate relative to the motor stator in response to a second changing magnetic field associated with the motor stator and the motor rotor. (Item 21) 21. The system of claim 20, wherein the transducer is positioned in operable proximity to the motor stator and the motor rotor to generate electrical energy in response to the second changing magnetic field associated with the motor stator and the motor rotor. (Item 22) At least one of the motor rotor and the motor stator includes a permanent magnet; at least one of the motor rotor and the motor stator includes an electromagnet; the motor is configured to periodically change polarity of the electromagnet to cause rotation of the motor rotor. Item 21. The system according to item 20. (Item 23) 20. The system of claim 19, wherein the transducer includes a Wiegand inductor. (Item 24) 20. The system of claim 19, wherein the transducer comprises a dynamo. (Item 25) 20. The system of claim 19, wherein the at least one sensor includes at least one of a fluid temperature sensor, a fluid pressure sensor, a flow rate sensor, and a distance sensor. (Item 26) 20. The system of claim 19, wherein the rotor is magnetically coupled to the electric motor of the fluid pump so as to generate the changing magnetic field when the rotor rotates. (Item 27) 20. The system of claim 19, wherein a drive shaft couples the rotor to the electric motor of the blood pump to rotate the rotor and generate the changing magnetic field when the rotor rotates. (Item 28) 20. The system of claim 19, further comprising a controller programmed or configured to receive an output data signal from the at least one sensor. (Item 29) Item 29. The system of item 28, wherein the at least one sensor is configured to wirelessly transmit the output data signal to the controller. (Item 30) 20. The system of claim 19, wherein the electrical energy generated by the transducer includes a plurality of first voltage pulses, each first voltage pulse having a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field. (Item 31) 22. The system of claim 21, wherein the electrical energy generated by the transducer includes a plurality of first voltage pulses, each first voltage pulse having a substantially constant voltage that is not affected by changes in rotational speed of the first changing magnetic field and the second changing magnetic field. (Item 32) 31. The system of claim 30, wherein the electrical energy generated by the transducer includes a plurality of second voltage pulses, each second voltage pulse having a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field, and the first voltage pulses are substantially different from the second voltage pulses. (Item 33) 20. The system of claim 19, further comprising a converter box for storing and conditioning the electrical energy generated by the transducer so that the electrical energy generated by the transducer is in a form suitable for powering the at least one sensor. (Item 34) 20. The system of claim 19, wherein the fluid pump is a blood pump and the system is a medical device selected from the group consisting of a cardiopulmonary bypass machine, an extracorporeal membrane oxygenator, a pump-assisted pulmonary protection device, and a hemodialysis machine. (Item 35) 1. A method for generating electrical energy for powering at least one electronic device, comprising: In a fluid pump including a magnetic field coupling a pump rotor and an electric motor, rotating the pump rotor to generate a first changing magnetic field associated with the pump rotor; inducing a voltage in a transducer as a result of rotating the first magnetic field, the transducer including a Wiegand inductor, the induced voltage including a plurality of first voltage pulses, each first voltage pulse having a substantially constant voltage that is not affected by changes in the rotation rate of the first changing magnetic field as the first changing magnetic field is rotated; using the induced voltage as a source of electrical energy to power the at least one electronic device; The method comprising: (Item 36) The electric motor includes a motor rotor and a motor stator, the motor rotor configured to rotate relative to the motor stator in response to a second changing magnetic field associated with the motor stator and the motor rotor, and the method further comprises: generating the second changing magnetic field to rotate the motor rotor relative to the motor stator; Item 36. The method according to Item 35, comprising: (Item 37) rotating the second changing magnetic field to induce a further voltage in the transducer; Item 37. The method of item 36, further comprising: (Item 38) At least one of the motor rotor and the motor stator includes a permanent magnet; at least one of the motor rotor and the motor stator includes an electromagnet; the electric motor is configured to periodically change the polarity of the electromagnet to cause rotation of the motor rotor. Item 37. The method according to item 36. (Item 39) Item 36. The method of item 35, wherein the induced voltage includes a plurality of second voltage pulses, each second voltage pulse having a substantially constant voltage that is not affected by changes in the rotation speed of the first changing magnetic field, and the first voltage pulse is substantially different from the second voltage pulse. (Item 40) 36. The method of claim 35, further comprising: conditioning the electrical energy generated by the transducer, wherein the electrical energy is conditioned by a converter box such that the induced voltage generated by the transducer is in a form suitable for powering the at least one electronic device. (Item 41) Item 36. The method of item 35, wherein the fluid pump is a blood pump, the system is a medical device selected from the group consisting of a cardiopulmonary bypass machine, an extracorporeal membrane oxygenator, a pump-assisted pulmonary protection device, and a hemodialysis machine, and the at least one electronic device powered by the electrical energy is selected from the group consisting of a blood temperature sensor, a blood flow sensor, a blood pressure sensor, and a distance sensor. (Item 42) 1. An electric system comprising: an electric motor having a rotor, the rotor coupled to be rotated by the electric motor; a transducer positioned in operable proximity to the rotor, the transducer configured to generate electrical energy in response to a first changing magnetic field associated with rotation of the rotor; at least one electronic device powered by electrical energy generated by the transducer; The electric system comprises: (Item 43) Item 43. The system of item 42, wherein the electric motor comprises a motor rotor and a motor stator, the motor rotor configured to rotate relative to the motor stator in response to a second changing magnetic field associated with the motor stator and the motor rotor. (Item 44) Item 44. The system of item 43, wherein the transducer is positioned in operable proximity to the motor stator and the motor rotor to generate electrical energy in response to the second changing magnetic field associated with the motor stator and the motor rotor. (Item 45) At least one of the motor rotor and the motor stator includes a permanent magnet; at least one of the motor rotor and the motor stator includes an electromagnet; the motor is configured to periodically change polarity of the electromagnet to cause rotation of the motor rotor. Item 44. The system according to item 43. (Item 46) Item 43. The system of item 42, wherein the transducer includes a Wiegand inductor. (Item 47) Item 43. The system of item 42, wherein the electrical energy generated by the transducer includes a plurality of first voltage pulses, each first voltage pulse having a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field. (Item 48) Item 45. The system of item 44, wherein the electrical energy generated by the transducer includes a plurality of first voltage pulses, each first voltage pulse having a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field and the second changing magnetic field. (Item 49) Item 43. The system of item 42, wherein the electrical energy generated by the transducer includes a plurality of second voltage pulses, each second voltage pulse having a substantially constant voltage that is not affected by changes in the rotational speed of the first changing magnetic field, and the first voltage pulses are substantially different from the second voltage pulses. (Item 50) Item 43. The system of item 42, further comprising a converter box for storing and conditioning the electrical energy generated by the transducer so that the electrical energy generated by the transducer is in a form suitable for powering the at least one electronic device. (Item 51) Item 43. The system of item 42, wherein the electric motor is a component of a blood pump, the system is a medical device selected from the group consisting of a cardiopulmonary bypass machine, an extracorporeal membrane oxygenator, a pump-assisted pulmonary protection device, and a hemodialysis machine, and the at least one electronic device powered by the electrical energy is selected from the group consisting of a blood temperature sensor, a blood flow sensor, a blood pressure sensor, and a distance sensor. [Brief explanation of the drawings]

[0058] [Figure 1A] 1 is a perspective view of an extracorporeal circulation system according to an embodiment of the present disclosure. FIG. [Figure 1B] 1 is a schematic diagram of an extracorporeal circulation system according to an embodiment of the present disclosure. [Figure 2A] FIG. 1C is a partial schematic diagram of the extracorporeal circulation system of FIG. 1B according to an embodiment of the present disclosure. [Figure 2B] FIG. 1C is a partial schematic diagram of the extracorporeal circulation system of FIG. 1B according to an embodiment of the present disclosure. [Figure 3A] FIG. 1 is a top view of a blood pump including an associated transducer according to an embodiment of the present disclosure. [Figure 3B] 3B is a schematic top view of the blood pump of FIG. 3A illustrating the rotating magnetic field generated during operation of the blood pump. [Figure 3C] FIG. 3B is a cross-sectional side view of the blood pump of FIG. 3A in accordance with an embodiment of the present disclosure. [Figure 3D] 3D is a cross-sectional view of the blood pump of FIG. 3C taken along section line II-II of FIG. 3C. [Figure 3E] FIG. 3B is a cross-sectional side view of the blood pump of FIG. 3A in accordance with an embodiment of the present disclosure. [Figure 3F] 3E taken along section line III-III of FIG. 3E. FIG. [Figure 4A] 1 is a partial schematic diagram of an extracorporeal circulation system according to an embodiment of the present disclosure. [Figure 4B] 1 is a partial schematic diagram of an extracorporeal circulation system according to an embodiment of the present disclosure. [Figure 5] 1 is a partial schematic diagram of an extracorporeal circulation system according to an embodiment of the present disclosure. [Figure 6] 1A-F are schematic diagrams of a Wiegand inductor responsive to a changing magnetic field, according to embodiments of the present disclosure. [Figure 7] FIG. 6B is a hysteresis diagram of the Wiegand inductor of FIGS. 6A to 6F. [Figure 8] FIG. 6C is a graph of the electrical output of the Wiegand inductor of FIGS. 6A-6F. [Figure 9] 6A-6F are graphs of the voltage output of the Wiegand inductors of FIGS. 6A-6F. [Figure 10] FIG. 10 is a detailed view of the first voltage pulse of the graph of FIG. [Figure 11] FIG. 1 is a graphical illustration of the electrical output of a dynamo, in accordance with an embodiment of the present invention. [Figure 12] 12 is a graph of the voltage output of the dynamo of FIG. 11. DETAILED DESCRIPTION OF THE INVENTION

[0059] Referring to the drawings, in which like reference symbols refer to like parts throughout the several views, the present disclosure generally relates to systems and methods for harvesting electrical energy from a rotating magnetic field generated by a blood pump in an extracorporeal circulation system, although the pump need not be a blood pump, the fluid may be a fluid other than blood, and the system may be a fluid flow system.

[0060] For purposes of the following description, the terms "upper," "lower," "right," "left," "vertical," "horizontal," "top," "bottom," "lateral," "longitudinal," and derivatives thereof, refer to the disclosure as oriented in the drawings. Because the disclosed embodiments may assume various alternative orientations, spatial or directional terms such as "left," "right," "inner," "outer," "above," and "below" should not be considered limiting.

[0061] As used herein, the singular forms "a," "an," and "the" include plural referents unless the context clearly dictates otherwise.

[0062] All numbers used in this specification and claims are understood to be modified in all instances by the term "about." The terms "approximately," "about," and "nearly / substantially" refer to a range of plus or minus ten percent of the stated value.

[0063] As used herein, the term "at least one of" is synonymous with "one or more of." For example, the phrase "at least one of A, B, and C" means any one of A, B, and C, or any combination of any two or more of A, B, and C. For example, "at least one of A, B, and C" includes one or more As alone, or one or more Bs alone, or one or more Cs alone, or one or more As and one or more Bs, or one or more As and one or more Cs, or one or more Bs and one or more Cs, or one or more of all As, Bs, and Cs. Similarly, as used herein, the term "at least two of" is synonymous with "two or more of." For example, the phrase "at least two of D, E, and F" means any combination of any two or more of D, E, and F. For example, "at least two of D, E, and F" includes one or more D and one or more E, or one or more D and one or more F, or one or more E and one or more F, or one or all of D, E, and F.

[0064] It should also be understood that the specific devices and processes illustrated in the accompanying drawings, and described in the following specification, are simply representative embodiments of the present disclosure, and thus specific dimensions and other physical characteristics relating to the embodiments disclosed herein are not to be considered as limiting.

[0065] The terms "first" and "second", etc. are not intended to refer to any particular order or chronology, but rather to different conditions, attributes, or elements.

[0066] The term "at least" is synonymous with "greater than or equal to." The term "not exceeding" is synonymous with "less than or equal to."

[0067] As used herein, the term "dynamo" means an electrical component that produces an alternating current (AC) output voltage in response to a changing magnetic field, the magnitude of the output voltage being positively related to the rate at which the magnetic field changes.

[0068] It is to be understood that the present disclosure may contemplate alternative variations and step sequences unless expressly specified to the contrary. It is also to be understood that the specific devices and processes illustrated in the accompanying drawings, and described in the following specification, are merely representative aspects of the present disclosure. Hence, specific dimensions and other physical characteristics relating to the examples disclosed herein are not to be considered limiting.

[0069] 1A and 1B, an extracorporeal circulation system 10 (also referred to as a heart-lung machine, or cardiac bypass system, or cardiopulmonary bypass system, which should be broadly interpreted to include cardiopulmonary bypass (CPB) systems, minimal extracorporeal circulation (MECC) systems, extracorporeal membrane oxygenation (ECMO) systems (respiratory and cardiac), and pump-assisted pulmonary protection (PALP) systems) includes a controller 12, a venous blood reservoir 14, one or more blood pumps 16, and an oxygenator 18. The venous blood reservoir 14, the blood pump 16, and the oxygenator 18 are interconnected in a conventional manner, such that venous blood extracted from the venous side of a patient's circulatory system, e.g., from a caval-atrial cannula 37 inserted into the vena cava and / or right atrium of the heart H, flows via tubing 22 into the venous blood reservoir 14, and from there is pumped via the blood pump 16 to the oxygenator 18. The oxygenator 18 oxygenates the blood, which then flows through tubing 24 into an arterial cannula 26 inserted into the aortic root of the heart H. The blood pump 16 may be a roller pump or a centrifugal pump, each of which includes an electric motor for pumping blood, albeit via substantially different mechanisms known in the art. Commercially available examples of suitable blood pumps 16 and related components include, but are not limited to, the Maquet Cardiohelp® system and the Maquet Rotaflow® system offered by Maquet Cardiopulmonary GmbH. The extracorporeal circulation system 10 shown in FIGS. 1A and 1B constitutes a simplified, non-limiting illustration, as such systems are typically quite complex.

[0070] 1B , at least one sensor 180 may be provided in association with the oxygenator 18 to measure one or more parameters, such as blood temperature, blood pressure, and blood flow. The at least one sensor 180 may be configured to detect or measure an attribute of blood entering, exiting, or passing through the oxygenator 18, such as blood pressure, blood temperature, or blood flow. The at least one sensor 180 may further be configured to transmit an output data signal corresponding to the detected or measured attribute to the controller 12. The at least one sensor 180 may be provided at a clinically desirable location relative to the oxygenator 18, such as near an inlet of the oxygenator 18, near an outlet of the oxygenator 18, or within the oxygenator 18. Such sensors 180 typically require a 5-volt power source to operate, although in some cases electronic sensors requiring only 1.2 volts, 1.8 volts, or 3.3 volts may be available.

[0071] Further details of the extracorporeal circulation system 10 of the present disclosure are described in U.S. Provisional Patent Application No. 62 / 160,689, filed May 13, 2015, and its corresponding U.S. Patent Application Publication No. US2018 / 0344919, both of which are incorporated herein by reference in their entireties.

[0072] 2A and 2B, an extracorporeal circulation system 10 according to the present disclosure includes components for harvesting energy from an electric motor of a blood pump 16 to power at least one sensor 180 and / or other circuits or electronic devices of the electronic system 10. The blood pump 16 includes an electric motor 162, such as an induction motor, connected to and configured to drive a pump rotor 164 (e.g., an impeller). The motor 162 and rotor 164 may be magnetically coupled by a magnetic coupling 166, i.e., a coupling magnetic field, such that rotation of the rotor 164 by the motor 162 generates an alternating magnetic field. The alternating magnetic field may be, for example, a rotating magnetic field generated during operation of the electric motor 162, which causes rotation of the rotor 164. With particular reference to the embodiment shown in FIG. 2A, a transducer 168 including a Wiegand inductor is positioned in operable proximity to the rotor 164 so as to reside within the alternating magnetic field. Transducer 168 is configured to generate electrical energy in response to changes in the alternating magnetic field associated with rotor 164. Transducer 168 may thus be referred to in this disclosure as a "magnetic transducer" because it converts the energy of the alternating magnetic field into electrical energy that can be used to power one or more electronic devices, such as electronic sensors and other electronic devices.

[0073] Non-limiting examples of placement of transducer 168 relative to blood pump 16 are shown in Figures 3A-3D. Specifically, transducer 168 can be positioned in operable proximity to rotor 164 and motor 162 so that transducer 168 is within an effective operable range of the alternating magnetic field generated during rotation of rotor 164, thereby enabling transducer 168 to convert energy from the changing magnetic field into usable electrical energy suitable for powering an electronic device. In some embodiments, as shown in Figure 3A, transducer 168 can be positioned on or in a housing 167 of blood pump 16, such as a cover 172 for housing 167, which can be removed and reattached to blood pump 16 by one or more fasteners 173, thereby allowing replacement of rotor 164. Cover 172, or any other portion of housing 167 to which transducer 168 is attached, is a non-magnetic material, such as plastic, so as not to interfere with the alternating magnetic field associated with rotation of rotor 164. As shown in FIG. 3A, the cover 172, or any other portion of the housing 167 to which the transducer 168 is attached, may be transparent to allow visual inspection of the rotor 164.

[0074] As shown in FIGS. 3A-3B, transducer 168 may be positioned off-center relative to the axis of rotation A of rotor 164. However, the position of transducer 168 relative to the axis of rotation A is not limited to the position shown in FIG. 3A. Rather, transducer 168 may be positioned substantially anywhere relative to the axis of rotation A, so long as transducer 168 is positioned in a location that allows it to collect magnetic energy within a changing magnetic field and convert it to electrical energy. FIG. 3B shows transducer 168 superimposed on rotor 164, including alternating north and south poles of magnets 17 (e.g., permanent magnets or electromagnets) of rotor 164, which generate an alternating magnetic field about axis of rotation A when current is applied to motor 162. When current is applied to motor 162, causing rotor 164 to rotate in direction R, transducer 168 collects energy generated by the alternating magnetic field.

[0075] 3C and 3D , in a non-limiting embodiment, magnets 17 may be attached to or embedded in rotor 164, which is magnetically coupled to motor 162 via coupling plate 20. Electric motor 162 may include motor stator 310 and motor rotor 320, which, when current is applied to motor 162, operate to generate an alternating magnetic field to rotate rotor 320, which is connected to shaft 163, thereby rotating shaft 163. For purposes of this disclosure, the alternating magnetic field associated with the operation of motor stator 310 and / or motor rotor 320 may be referred to as the alternating magnetic field of the motor.

[0076] Consistent with conventional motor designs known in the art, the motor stator 310 and motor rotor 320 can have a variety of designs. For example, the motor rotor 320 can include multiple permanent magnets, and the motor stator 310 can include multiple electromagnets that periodically change polarity to generate an alternating magnetic field that drives rotation of the magnets in the motor rotor 320. More specifically, the alternating magnetic field of the motor stator 310 can interact with the magnetic field of the motor rotor 320 to generate a torque that rotates the motor rotor 320 relative to the stator 310. Alternative embodiments of the motor stator 310 and motor rotor 320, such as those in which the motor rotor 320 includes electromagnets, the motor stator 310 includes permanent magnets, or both the motor stator 310 and the motor rotor 320 include electromagnets, will be readily apparent to those skilled in the art as conventional motor designs. As is conventionally known in the art, the motor 162 can be powered by either AC or DC power using suitable circuitry. Thus, the power motor 162 can be a direct current (DC) motor or an alternating current (AC) motor.

[0077] 3C-3D, the shaft 163 extends from the motor rotor 320 and is coupled to a coupling plate 20 including a plurality of magnets 21 (e.g., permanent magnets or electromagnets). The magnets 21 of the coupling plate 20 may be circumferentially arranged with alternating north and south poles. The number of magnets 21 of the coupling plate 20 may be the same as the number of magnets 17 of the pump rotor 164, such that the magnets 21 of the coupling plate 20 have a one-to-one relationship with the magnets 17 of the pump rotor 164. The magnets 21 of the coupling plate 20 may interact with the magnets 17 of the pump rotor 164 to form a magnetic coupling 166 (shown in FIGS. 2A-2B ) between the coupling plate 20 and the pump rotor 164. Specifically, pump rotor 164 may tend to self-align when in proximity to magnetic coupling plate 20, such that magnets 17 with north polarity on pump rotor 164 tend to face magnets 21 with south polarity on coupling plate 20, and vice versa, as shown in FIG. 3D. As shown in FIG. 3C, portion 167a of housing 167 may extend between magnets 17 on pump rotor 164 and magnets 21 on coupling plate 20 without interfering with magnetic coupling 166 between pump rotor 164 and coupling plate 20. When coupling plate 20 is rotated by shaft 163, the magnetic coupling effect between magnets 17 on pump rotor 164 and magnets 21 on coupling plate 20 causes pump rotor 164 to rotate in the same direction and at substantially the same speed as shaft 163. In other words, although the pump rotor 164 and the coupling plate 20 are not directly and securely fastened to one another by a mechanical connection, the magnetic coupling 166 that exists between the magnets 17 of the pump rotor 164 and the magnets 21 of the coupling plate 20 functions as a magnetic coupling that causes rotation of the pump rotor 164 when the coupling plate 20 is rotated by the shaft 163. When the coupling plate 20 and the pump rotor 164 are rotated by the motor 162, the magnets 17 of the pump rotor 164 and the magnets 21 of the coupling plate 20 generate an alternating magnetic field (e.g., a rotating magnetic field). For purposes of this disclosure, this alternating magnetic field associated with the rotation of the pump rotor 164 and / or the coupling plate 20 may be collectively referred to as the alternating magnetic field of the pump rotor.

[0078] The motor alternating magnetic field and the pump rotor alternating magnetic field each originate from a substantially different magnetic source and therefore constitute substantially different alternating magnetic fields. It is within the scope of this disclosure to position one or more transducers 168, or one or more dynamos 169, or a combination of transducers 168 and dynamos 169, in one or more locations such that these devices collect electrical energy primarily from the pump rotor alternating magnetic field, or primarily from the motor alternating magnetic field, or substantially from both the pump rotor alternating magnetic field and the motor alternating magnetic field.

[0079] 3C , in some embodiments, transducer 168 may be positioned in close proximity to alternating magnetic fields (e.g., rotating magnetic fields) generated by motor stator 310 and / or motor rotor 320, i.e., magnetic fields induced by the periodic changes in polarity of stator 310 and / or the rotation of motor rotor 320, collectively referred to as the motor's alternating magnetic field. Thus, transducer 168 may harvest energy directly from the alternating magnetic fields of motor 162. Additionally or alternatively, transducer 168 may be positioned in operable proximity to pump rotor 164 to harvest energy from alternating magnetic fields (e.g., rotating magnetic fields) generated by the rotation of magnets 17 of pump rotor 164 and magnets 21 of coupling plate 20. That is, transducer 168 may harvest energy from either or both of the alternating magnetic fields associated with motor stator 310 and motor rotor 320 and the alternating magnetic fields associated with coupling plate 20 and pump rotor 164.

[0080] In Figure 3C, such alternative locations for transducer 168 and associated converter box 170 are shown in phantom lines as integrated circuits or integrated electronic chips (identified by reference numerals 168y, 170y, and 168z, 170z), although they may be separate and electrically connected by one or more wired or wireless electrical connections. Similarly, transducer 168 and converter box 170, located on cover 172, are shown spaced apart and connected by one or more wired (not shown in Figure 3C) or wireless electrical connections (not shown in Figure 3C) so that voltage pulses generated by transducer 168 are sent to converter box 170 for processing into a usable output voltage, such as in the range of 1.2 volts to 5.0 volts or greater, although these separate structures may be integrated into an integrated circuit or integrated to form an integrated electronic chip.

[0081] Further details of the blood pump 16 shown in Figures 3A-3D are described in U.S. Patent No. 5,658,136, issued August 19, 1997, the entire contents of which are incorporated herein by reference.

[0082] 3E-3F show another non-limiting embodiment of blood pump 106 in which pump rotor 264 also functions as the motor rotor, such that rotor 264 is directly driven by the stator of motor 262; thus, this embodiment does not include shaft 163 and coupling plate 20. In this embodiment, rotor 264 may be substantially the same as that described in connection with FIGS. 3C-3D . Motor 262 includes motor stator 311, which includes one or more magnets 23 (e.g., electromagnets) operatively associated with magnets 27 of rotor 264. During operation of motor 262, which may be a DC motor or an AC motor, current is supplied to electromagnets 23, the polarity of which periodically changes. The alternating polarities of electromagnets 23 of stator 311 generate an alternating magnetic field that rotates rotor 264 about axis A. More specifically, the alternating magnetic field of the motor stator 311 may interact with the magnetic field of the magnets 27 of the rotor 264 to generate a torque that rotates the rotor 264 relative to the stator 311. The transducer 168 may be positioned in operable proximity to the stator 311 to harvest energy from the alternating magnetic field associated with the motor stator 311, i.e., the alternating magnetic field induced by the periodic changes in polarity of the magnets 23. Additionally or alternatively, the transducer 168 may be positioned in operable proximity to the rotor 264 to harvest energy from the alternating magnetic field associated with the rotation of the magnets 27 of the rotor 264.

[0083] As described above, the transducer 168 includes a Wiegand inductor that generates a series of voltage pulses of substantially uniform amplitude in response to the rotation of the alternating magnetic field associated with the rotors 164, 264. In some embodiments, the transducer 168 in the form of a Wiegand inductor may be replaced by a dynamo 169 (shown in FIGS. 2B and 4B ), which generates an AC voltage output proportional to the rotational speed of the rotors 164, 264 in response to the rotation of the alternating magnetic field associated with the rotors 164, 264. The dynamo 169 may be positioned within the alternating magnetic field associated with the rotors 164, 264 similar to the transducer 168 shown in FIGS. 3A-3B . Further details of the electrical attributes and electrical output associated with the magnetic transducer 168 in the form of a Wiegand inductor are described herein in connection with FIGS. 6A-10 , and further details of the electrical attributes and electrical output associated with the dynamo 169 are described herein in connection with FIGS. 11 and 12 .

[0084] It should be noted that a Wiegand sensor is a Wiegand inductor adapted to sense the number and timing of changes in a magnetic field. According to the present disclosure, a Wiegand inductor is a device used to harvest electrical energy from a changing magnetic field, for example, as generated by an electric motor and / or magnets in a pump rotor, in a new, inventive, and inventive manner, regardless of whether the Wiegand inductor is also used to sense the number and timing of changes in the changing magnetic field from which electrical energy is harvested. According to an embodiment of the present disclosure, although a Wiegand inductor is adapted to harvest electrical energy from a changing magnetic field, the Wiegand inductor cannot be construed as a Wiegand sensor because it is not adapted to harvest data regarding the number and timing of changes in the magnetic field.

[0085] In some embodiments of the present disclosure, the transducers 168, 169 may be positioned to collect electrical energy primarily from the changing magnetic field generated by the electric motor, or the transducers 168, 169 may be positioned to collect electrical energy primarily from the changing magnetic field generated by the magnets of the rotating rotors 164, 264, or the transducers 168, 169 may be positioned to collect electrical energy substantially from both the changing magnetic field generated by the electric motor and the changing magnetic field generated by the magnets of the rotating rotors 164, 264. In the embodiment(s) described with respect to FIGS. 3C-3D , when the transducers 168, 169 are positioned to collect electrical energy from both the changing magnetic field generated by the motor 162 and the changing magnetic field generated by the magnets of the rotating rotor 164, the two changing magnetic fields may affect the transducers 168 and 169 differently. Note that because the motor rotor 320 and the pump rotor 164 are rotating together at substantially the same speed, the two changing magnetic fields are out of phase with each other. As a result, for dynamo 169, more electrical energy is collected per rotation cycle due to the cumulative effect of the compound changing magnetic fields.

[0086] 6A-6F, the transducer 168 does not necessarily harvest more electrical energy from the combined magnetic field because the Wiegand inductor generates only constant amplitude pulses if a threshold is reached that causes a polarity shift. However, because the combined magnetic field is in phase, the combined magnetic field cannot trigger voltage pulses more frequently than if it were harvesting electrical energy from one of the single changing magnetic field sources. However, the cumulative effect of the combined changing magnetic field allows for an increased area in which the transducer 168 can be positioned to harvest electrical energy from the combined changing magnetic field.

[0087] 1A, when multiple pumps 16 are operated in a pump array, a transducer 168 can be positioned to collect electrical energy from two adjacent pumps 16 that are not operating in phase. In this case, the combined magnetic field can trigger the transducer 168 to generate voltage pulses at a frequency higher than the frequency of the changing magnetic field in either of the two adjacent pumps 16. Thus, since the faster the transducer 168 generates voltage pulses, the more power it collects from the combined changing magnetic field. By judiciously selecting where to position the transducer 168 so that it is exposed to the combined changing magnetic field of two or more changing magnetic field sources that are out of phase, the transducer 168 can be used to collect more power from the combined magnetic field.

[0088] Referring again to FIG. 2A , electrical energy generated by the transducer 168 may be used to power at least one sensor 180 operatively associated with the oxygenator 18. The transducer 168 may be in electrical communication with the at least one sensor 180 via power leads 182 that provide electrical energy from the transducer 168 to the at least one sensor 180. The at least one sensor 180 may comprise, for example, a blood pressure sensor, a blood temperature sensor, a flow rate sensor, or a distance sensor. The at least one sensor 180 may be configured to detect or measure an attribute of blood flowing into, out of, or passing through the oxygenator 18, such as blood pressure, blood temperature, or flow rate. The at least one sensor 180 may further be configured to transmit, directly or indirectly, an output data signal corresponding to the detected or measured attribute to the controller 12. In some embodiments, additional circuitry associated with the at least one sensor 180 may receive the output data signal from the at least one sensor 180 and transmit the output data signal to the controller 12, as discussed herein in connection with FIGS. 4 and 5 . The controller 12 may be programmed or configured to receive output data signals from at least one sensor 180 or from additional circuitry associated with at least one sensor 180, and display data related to the operation of the system 10 on a GUI display and / or adjust the operation of the system 10 based on the received output data signals.

[0089] Because the at least one sensor 180 is powered by the transducer 168, which is itself located on or in close proximity to the blood pump 16, neither a power cable from the controller 12 nor a separate external power source (e.g., a battery) is required to power the at least one sensor 180. This reduces setup time for the system 10 and eliminates the possibility of improper power connections to the at least one sensor 180.

[0090] In some embodiments, the at least one sensor 180 may be configured to transmit the output data signal wirelessly to the controller 12. Thus, there is no need to provide a signal cable between the at least one sensor 180 and the controller 12. This reduces the setup time of the system 10 and eliminates the possibility of making an improper signal connection between the controller 12 and the at least one sensor 180. The wireless output data signal, indicated by reference numeral 200 in FIG. 2A, may be transmitted via any conventional wireless protocol, such as Wi-Fi, near-field communication (NFC), or Bluetooth®.

[0091] 2A , a converter box 170 is provided between the transducer 168 and the at least one sensor 180 to store and condition the electrical energy generated by the transducer 168. The converter box 170 includes circuitry for converting the electrical energy output by the transducer 168 into a form of power usable by the at least one sensor 180. For example, the converter box 170 may include circuitry for limiting the voltage received by the at least one sensor 180 to prevent damage to the at least one sensor 180. The specific circuitry provided within the converter box 170 may vary depending on the specifications of the transducer 168 and the at least one sensor 180. For example, in embodiments in which transducer 168 is a Wiegand inductor, converter box 170 may include at least one rectifier that rectifies voltage pulses generated by transducer 168 and at least one capacitor that stores the rectified pulses of energy generated by transducer 168 and outputs the stored energy as a power output voltage to at least one sensor 180 (or other circuit component). Converter box 170 may further include protection circuitry that limits the output voltage to a predetermined threshold suitable for safe operation of at least one sensor 180. In some embodiments, converter box 170 may output a DC voltage of about 1.2 volts to about 5.0 volts, or about 1.8 volts to about 5.0 volts, or about 3.3 volts to about 5.0 volts.

[0092] 3C and 3E , in some embodiments, the transducer 168, the converter box 170, and the at least one sensor 180 may all be disposed on a portion of the housing 167 of the blood pump 16, such as the cover 172. Thus, the rotor 164, the housing 167, the cover 172, the transducer 168, the converter box 170, and the at least one sensor 180 may form a module (i.e., a disposable module) that can be easily replaced as a single unit at regular maintenance intervals consistent with established hygiene practices. This is possible because the transducer 168, as described herein, eliminates the need for external power connections to supply the converter box 170 and the at least one sensor 180. Furthermore, wireless data transfer of the at least one sensor 180 eliminates the need for a signal cable between the at least one sensor 180 and the heart-lung machine controller 12. Thus, in contrast to conventional systems, a healthcare provider is not required to make any electrical disconnections to remove the transducer 168, the transducer box 170, and the at least one sensor 180 from the blood pump 16. Providing the rotor 164, the housing 167, the cover 172, the transducer 168, the transducer box 170, and the at least one sensor 180 as a single modular unit reduces the likelihood and severity of operator error that may be associated with replacing these components individually.

[0093] Referring now to FIG. 2B, another embodiment of an extracorporeal circulation system 10 according to the present disclosure is shown. The embodiment of FIG. 2B is substantially similar to the embodiment of FIG. 2A, and only the differences will be described. The embodiment of FIG. 2B utilizes a transducer 169 in the form of a dynamo, as opposed to the Wiegand inductor transducer 168 of FIG. 2A. The dynamo 169 of FIG. 2B can generate an AC voltage output proportional to the rotational speed of the rotor 164 in response to the rotation of an alternating magnetic field associated with the rotor 164. Further details of the electrical attributes and electrical outputs associated with various forms of magnetic transducers 169 in the form of dynamos are described herein in conjunction with FIGS. 11-12.

[0094] Because the output of dynamo 169 differs from Wiegand inductor 168 of FIG. 2A , in the embodiment of FIG. 2B , converter box 170 of FIG. 2A is replaced with converter box 171. Converter box 171 may include one or more inductors for storing AC energy generated by dynamo 169, one or more rectifiers for rectifying voltages flowing into or out of the one or more inductors, and one or more components (e.g., circuits or subcircuits) for converting the AC voltage generated by dynamo 169 to a DC voltage suitable for powering one or more electronic components, such as at least one sensor 180. Such components for converting AC voltage to DC voltage, which may include, for example, rectifying the AC voltage, may comprise conventional commercially available units. In some embodiments, converter box 171 may output a DC voltage between about 1.2 volts and about 5.0 volts, or between about 1.8 volts and about 5.0 volts, or between about 3.3 volts and about 5.0 volts.

[0095] 2A and 2B illustrate non-limiting, exemplary circuit embodiments for powering the at least one sensor 180 via the transducers 168, 169; however, the system 10 may include additional circuitry to facilitate and / or improve the performance of the transducers 168, 169 and / or the at least one sensor 180, as shown in FIGS. 4A, 4B, and 5. Referring to FIG. 4A, the output of the transducer 168 may be in electrical communication with a converter box 170, substantially in the manner shown in FIG. 2A. As described herein in connection with FIG. 2A, the converter box 170 converts the pulsed electrical energy output from the transducer 168 into a form (e.g., a suitable DC voltage) suitable for powering the at least one sensor 180. Additionally, the converter box 170 may convert the pulsed electrical energy output from the transducer 168 into a form (e.g., a suitable DC voltage) suitable for powering various other electrical components, such as the at least one sensor processor 185 and the at least one transmitter 190. Specifically, the converter box 170 can output a DC voltage of about 1.2 volts to about 5.0 volts, or about 1.8 volts to about 5.0 volts, or about 3.3 volts to about 5.0 volts.

[0096] At least one sensor processor 185 may be in electronic communication with at least one sensor 180 via a wired or wireless data connection 187. The sensor processor 185 may be configured to receive output data signals (e.g., analog output signals) from the at least one sensor 180 via the data connection 187 and convert the output data signals into sensor data signals (e.g., digital signals) for transmission to at least one transmitter 190. The sensor processor 185 may include a processor, as conventionally known in the art, configured to execute algorithms for converting the output data signals from the sensors 180 into sensor data signals that are output from the sensor processor 185. The transmitter 190 may be in electronic communication with the at least one sensor processor 185 via a wired or wireless data connection 189. The at least one transmitter 190 may be configured to transmit the sensor data signals to the heart-lung machine controller 12.

[0097] In some embodiments, the at least one transmitter 190 may transmit the sensor data signal to the controller 12 wirelessly. Thus, there is no need to provide a signal cable between the at least one transmitter 190 and the controller 12. This reduces the setup time of the system 10 and eliminates the possibility of making an improper signal connection between the controller 12 and the at least one transmitter 190. The at least one transmitter 190 may output the data signal 200 wirelessly using any conventional wireless protocol, such as Wi-Fi, near field communication (NFC), or Bluetooth®.

[0098] FIG. 4B illustrates another non-limiting exemplary circuit embodiment that is substantially the same as FIG. 4A , except that the Wiegand inductor 168 and associated converter box 170 are replaced with a dynamo 169 and associated converter box 171, as described herein in connection with FIG. 2B . Thus, the embodiment illustrated in FIG. 4B uses the dynamo 169 to collect energy from an alternating magnetic field and power one or more of at least one sensor 180, at least one sensor processor 185, and at least one transmitter 190. The converter box 171 converts the AC electrical energy output from the transducer 169 into a form (e.g., a suitable DC voltage) suitable for powering one or more of the at least one sensor 180, at least one sensor processor 185, and at least one transmitter 190. Specifically, the converter box 171 may output a DC voltage of approximately 1.2 volts to approximately 5.0 volts, or approximately 1.8 volts to approximately 5.0 volts, or approximately 3.3 volts to approximately 5.0 volts. The at least one sensor 180, the at least one sensor processor 185, and the at least one transmitter 190 may be identical in form and function to those described in connection with FIG. 4A.

[0099] 4A and 4B depict at least one sensor 180, at least one sensor processor 185, and at least one transmitter 190 as separate components for clarity of illustration. However, those skilled in the art will understand that any or all of these components may be integrated into a single physical device without departing from the scope of this disclosure, which is powered with electrical energy harvested from an alternating magnetic field using at least one magnetic transducer 168 or dynamo 169. Of course, it is within the scope of this disclosure to use multiple magnetic transducers 168, or multiple dynamos 169, or a mixture thereof, to harvest electrical energy from an alternating magnetic field generated by a pump motor or other electric motor to power and energize a single physical device, which may be an integrated circuit or computer chip.

[0100] Referring to FIG. 5, another embodiment of circuitry associated with transducers 168, 169, each in the form of either a Wiegand inductor or a dynamo, and at least one sensor 180 is shown, where additional circuitry facilitates and / or improves the performance of transducers 168, 169 and / or at least one sensor 180.

[0101] The circuit of FIG. 5 includes an energy collector 250, which may include, in a first embodiment, a combination of a Wiegand inductor 168 and its associated converter box 170, or, in a second embodiment, a combination of a dynamo 169 and its associated converter box 171. In either embodiment, the energy collector 250 provides a power source in the form of a DC voltage suitable for powering one or more of the electronic components shown in FIG. 5. The output of the energy collector 250 may be in electrical communication with an energy storage component 184. The energy storage component 184 may receive the electrical energy generated by the energy collector 250 and provide the electrical energy in a suitable form (e.g., a suitable DC voltage) for powering one or more electrical components. Specifically, the energy storage component 184 may output a DC voltage of approximately 1.2 volts to approximately 5.0 volts, or approximately 1.8 volts to approximately 5.0 volts, or approximately 3.3 volts to approximately 5.0 volts. One or more outlets of the energy storage component 184 may be in electrical communication with one or more of the at least one sensor 180, the at least one signal processor 186 associated with the at least one sensor 180, the at least one data processor 188, and the at least one transmitter 190, and may supply them with power within the aforementioned voltage ranges. Each of these components will be described in turn. The at least one signal processor 186 may be in electronic communication with the at least one sensor 180 via a wired or wireless data connection 187. The at least one signal processor 186 may be configured to receive output data signals (e.g., analog output signals) from the at least one sensor 180 via the data connection 187 and convert the output data signals into sensor data signals (e.g., digital signals) for transmission to the at least one data processor 188. The at least one signal processor 186 may include a signal processing unit, as conventionally known in the art, configured to execute an algorithm for converting the output data signals into sensor data signals.

[0102] The at least one data processor 188 may be in electronic communication with the at least one signal processor 186 via a wired or wireless data connection 191. The at least one data processor 188 may be configured to receive sensor data signals from the at least one signal processor 186 and transmit the sensor data signals to the at least one transmitter 190. In some embodiments, the at least one data processor 188 may be configured to filter or otherwise convert the sensor data signals in an appropriate manner before transmitting the sensor data signals to the at least one transmitter 190. Furthermore, the at least one data processor 188 may be configured to receive a verification signal from the at least one transmitter 190. The verification signal may include, for example, a handshake or checksum communication to verify the authenticity of data transmitted between the at least one data processor 188 and the at least one transmitter 190. The at least one data processor 188 may include a microprocessor, conventionally known in the art, configured to execute algorithms for transmitting sensor data signals and receiving verification signals from the at least one transmitter 190.

[0103] The at least one transmitter 190 may be in electronic communication with the at least one data processor 188 via a wired or wireless data connection 189. The at least one transmitter 190 may be configured to transmit sensor data signals to the controller 12 of the heart-lung machine. Additionally, the at least one transmitter 190 may be configured to receive a verification signal from the controller 12. The verification signal may include, for example, a handshake or checksum communication to verify the authenticity of data transmitted between the at least one transmitter 190 and the controller 12. In some embodiments, the at least one transmitter 190 may be configured to communicate a sensor fault signal to the controller 12 and / or to communicate signal instructions from the controller 12 to the at least one data processor 188.

[0104] In some embodiments, the at least one transmitter 190 may transmit the sensor data signal to the controller 12 wirelessly. Thus, there is no need to provide a signal cable between the at least one transmitter 190 and the controller 12. This reduces the setup time of the system 10 and eliminates the possibility of making an improper signal connection between the controller 12 and the at least one transmitter 190. The at least one transmitter 190 may output the data signal 200 wirelessly using any conventional wireless protocol, such as Wi-Fi, near field communication (NFC), or Bluetooth®.

[0105] 5 depicts at least one sensor 180, energy storage component 184, at least one signal processor 186, at least one data processor 188, and at least one transmitter 190 as separate components for clarity of illustration. However, those skilled in the art will understand that any or all of these components may be integrated into a single physical device, such as an integrated computer chip, powered with electrical energy harvested from an alternating magnetic field using at least one magnetic transducer 168 or dynamo 169, without departing from the scope of this disclosure. Of course, it is within the scope of this disclosure to use multiple magnetic transducers 168, or multiple dynamos 169, or a mixture thereof, to harvest electrical energy from an alternating magnetic field generated by a pump motor or other electric motor to power a single physical device, which may be an integrated computer chip.

[0106] 6A-6F, there is shown the principles of energy collection and energy output by a transducer 168 in the form of a Wiegand inductor. While Figures 6A-6F show a reasonable theoretical model for describing the voltage generation characteristics of a Wiegand inductor, it should be noted that this model cannot explain all of the experimentally measured voltage generation characteristics, as is evident from Figures 9 and 10.

[0107] According to the theoretical model shown in Figures 6A-6F, a Wiegand inductor includes a Wiegand wire having an inner core 302 and an outer shell 304. The outer shell 304 has a higher coercivity than the inner core 302, and therefore, to induce a polarity change, the outer shell 304 must be exposed to a relatively strong magnetic field. Wiegand wire may be constructed from low-carbon Vicalloy (e.g., a ferromagnetic alloy of cobalt, iron, and vanadium), which undergoes a series of twisting and untwisting operations to cold-work the outer shell 304. This cold-working renders the outer shell 304 magnetically hard, while the inner core 302 remains magnetically soft. Following this cold-working, the Wiegand wire may be aged. A specific example of a Vicalloy suitable for Wiegand wire includes an alloy of substantially 52% cobalt, 10% vanadium, trace amounts of elements such as carbon and manganese, and the balance (~37%) iron. A pickup coil 306 is wrapped around the Wiegand wire and has two terminals 308 between which a voltage is generated. Such a voltage is generated between the terminals 308 when the Wiegand inductor is exposed to a changing magnetic field. More specifically, a first voltage pulse p1 is generated between the terminals 308 when the Wiegand inductor is exposed to a magnetic field large enough to reverse the polarity of the inner core 302, and subsequently a second voltage pulse p2 is generated between the terminals 308 when the Wiegand inductor is exposed to a magnetic field large enough to reverse the polarity of the outer shell 304.

[0108] Referring now to FIG. 6A, the transducer 168 is shown in the absence of an external magnetic field, with the respective polarities of both the inner core 302 and the outer shell 304 aligned in the same direction, as indicated by arrow B. In the state shown in FIG. 6A, no voltage is generated by the pickup coil 306. Referring now to FIG. 6B, the transducer 168 is shown exposed to an external magnetic field M that is large enough to reverse the polarity of the inner core 302, but insufficient to reverse the polarity of the outer shell 304. The switching of polarity of the inner core 302 generates a first voltage pulse p1 across the terminals 308 of the pickup coil 306. Referring now to FIG. 6C, the magnitude of the external magnetic field M is increased as compared to FIG. 6B, such that the magnetic field M has sufficient magnitude to reverse the polarity of the outer shell 304. The switching of polarity of the outer shell 304 generates a second voltage pulse p2 across the terminals 308 of the pickup coil 306. The polarity of the inner core 302 and the polarity of the outer shell 304 are again aligned. The first voltage pulse p1 and the second voltage pulse p2 may have substantially different amplitudes, but they have the same polarity. Specifically, in some cases, the amplitude of the second voltage pulse p2 may be so small as to result in negligible energy output compared to the first voltage pulse p1, and thus no appreciable energy is collected from the second voltage pulse p2.

[0109] Referring now to FIG. 6D, the external magnetic field M is removed or at least reduced to zero, while the polarity of the inner core 302 and outer shell 304 remains the same as in FIG. 6C. No voltage is generated by the coil 306. Referring now to FIG. 6E, the external magnetic field M exists at a similar magnitude but in the opposite direction compared to FIG. 6B. The external magnetic field M is large enough to reverse the polarity of the inner core 302, but insufficient to reverse the polarity of the outer shell 304. The change in polarity of the inner core 302 generates a third voltage pulse p3 across the terminals 308 of the pickup coil 306. Referring next to FIG. 6F, the magnitude of the external magnetic field M is increased compared to FIG. 6E so that the external magnetic field M has sufficient magnitude to reverse the polarity of the outer shell 304. The change in polarity of the outer shell 304 generates a fourth voltage pulse p4 across the terminals 308 of the pickup coil 306. The polarity of the inner core 302 and the polarity of the outer shell 304 are again aligned. When the magnetic field M is removed, or at least reduced to zero, the Wiegand inductor returns to the state of Figure 6A, and the cycle of varying the external magnetic field M can be repeated.

[0110] The third voltage pulse p3 and the fourth voltage pulse p4 may have substantially different amplitudes but the same polarity. Specifically, in some cases, the amplitude of the fourth voltage pulse p4 may be so small that the energy output is negligible compared to the third voltage pulse p3, and therefore no appreciable energy is collected from the fourth voltage pulse p4. The polarities of the third voltage pulse p3 and the fourth voltage pulse p4 are opposite to the polarities of the first voltage pulse p1 and the second voltage pulse p2. The voltage pulse p1 and the voltage pulse p3 have substantially the same amplitude but opposite polarities. The voltage pulse p2 and the voltage pulse p4 have substantially the same amplitude but opposite polarities.

[0111] An alternating magnetic field M of varying magnitude and direction, as shown in FIGS. 6A-6F, is generated by the rotation of the rotor 164 of the blood pump 16 (see FIGS. 2A, 3A, and 3B). That is, as the rotor 164 rotates, an alternating magnetic field is generated, which exposes the transducer 168 to periodic changes in magnitude and direction of the magnetic field M, as shown in FIGS. 6A-6F. The terminals 308 of the pickup coil 306 are attached to the power leads 182 (see FIG. 2A) so that primarily the first voltage pulse p1 and the third voltage pulse p3 are collected and stored in the transducer box 170 and / or the energy storage component 184. This is because the amplitudes of the second voltage pulse p2 and the fourth voltage pulse p4 are negligibly small compared to the first voltage pulse p1 and the third voltage pulse p3, and therefore the second voltage pulse p2 and the fourth voltage pulse p4 do not appreciably contribute to the amount of energy collected and stored.

[0112] The number of voltage pulses p1, p2, p3, and p4 generated per unit time increases with the rate at which the magnetic field M alternates; i.e., the faster the rotor 164 rotates, the more energy per unit time is collected by the transducer 168 because the generation of voltage pulses p1, p2, p3, and p4 occurs at a faster rate. However, the amplitude and polarity of voltage pulse p1 remains constant, the amplitude and polarity of voltage pulse p2 remains constant, the amplitude and polarity of voltage pulse p3 remains constant, and the amplitude and polarity of voltage pulse p4 remains constant. As can be seen from FIG. 9, each of the voltage pulses p1, p2, p3, and p4 appears as a series of oscillations. However, for ease of depiction and explanation in FIGS. 6A-6F, each of the voltage pulses p1, p2, p3, and p4 is shown as a single spike of voltage. For purposes of this disclosure, this pattern of voltage pulse generation of voltage pulses p1, p2, p3, and p4 illustrated by FIGS. 6A-6F is the result of exposing the Wiegand inductor to an alternating magnetic field (such as the rotating magnetic field generated by the rotation of rotor 164) and is referred to as the "Wiegand inductor voltage pulse generation pattern."

[0113] 7, a magnetic hysteresis diagram 700 of the Wiegand wire (i.e., inner core 302 and outer shell 304) of FIGS. 6A-6B is shown, in accordance with a non-limiting embodiment of the present disclosure. In diagram 700, the magnetic field H is plotted on the x-axis in amperes per centimeter (A / cm), and the magnetic flux density B of the Wiegand wire is plotted on the y-axis in tesla. As can be seen from diagram 700, Wiegand wire has a high coercivity, i.e., the ability to withstand an external magnetic field without being demagnetized, which facilitates the generation of voltage pulses p1, p2, p3, and p4 described in connection with FIGS. 6A-6F.

[0114] FIG. 8 shows a graphical representation of the pulsed voltage output of the transducer 168 in the form of a Wiegand inductor in FIGS. 6A-6F. Graph 810 shows the magnetic flux B plotted against time t. Graph 820 shows the voltage V plotted against time t. Graph 810 depicts two different magnetic flux curves J and K, representing two different rates of change of the alternating magnetic field. Curve J exhibits a relatively slower magnetic flux change over time than curve K. Graph 820 illustrates the voltage pulse generation over time associated with the magnetic field changes of curves K and J depicted in graph 810. As described herein with reference to FIGS. 6A-6F, when the alternating magnetic field causes a change in polarity of the inner core 302 and outer shell 304, a voltage pulse p is generated by the Wiegand inductor. The time interval at which pulse p occurs depends on the rate of change of the magnetic field, in this case the rotational speed of the rotor 164. Thus, the voltage pulse p associated with curve J J occurs every time the polarity of curve J changes, and the voltage pulse p associated with curve K K occurs every time the polarity of curve K changes. Therefore, as shown in graph 810, curve K has a faster rate of change of magnetic flux compared to curve J, and therefore curve K has a faster rate of change of magnetic flux compared to curve J. J generates a voltage pulse p K However, since the amplitude of the pulse generated by a Wiegand inductor does not depend on the rate of change of the alternating magnetic field, the voltage pulse p associated with curve K K is the voltage pulse p associated with curve J JNote that the amplitude of

[0115] Graphs 810 and 820 can be used to conceptualize how a transducer 168 can generate voltage pulses when placed simultaneously in two rotating magnetic fields having substantially different rotational frequencies (i.e., in two rotating magnetic fields generated from different magnetic sources, such as two adjacent power motors 162 in two adjacent pumps 16 in a pump array). A transducer 168 positioned to harvest electrical energy from magnetic fields represented by both curves J and K, which are out of phase, will generate a voltage pulse p J and p K To generate a voltage pulse p J and p K , and thus the transducer 168 generates more pulses per unit time in the combined magnetic field than when placed in just one of the changing magnetic fields J or K. This equates to generating more voltage power in the combined magnetic field. On the other hand, as explained above with reference to FIGS. 6A-6F, since the transducer 168 generates a constant pulse amplitude when subjected to a polarity shift, when the transducer 168 is placed in two changing magnetic fields that are in phase, for example, the rotating magnetic field J generated by the electric motor 162 and the rotating magnetic field J' generated by its associated magnet in the pump rotor 164, the generated voltage pulses p J is the same as if the transducer 168 were placed in only a single rotating magnetic field. Thus, the transducer 168 will produce the same voltage power output when present in multiple, in-phase rotating, changing magnetic fields as it would in a single changing magnetic field, provided the magnetic field(s) are strong enough to create a voltage that causes a polarity shift in the transducer 168.

[0116] Graph 830 shows the pulse energy of each pulse p plotted against the rotational speed of the changing magnetic field, i.e., the rotational speed of rotor 164. As can be seen from graph 830, the pulse energy of each pulse p J , p KThe pulse energy of each pulse p remains constant over all rotation speeds of the magnetic field. J , p K This means that the voltage amplitude of the pulse p is not affected by the rotation speed of the magnetic field. However, as mentioned above, an increase in the rotation speed of the magnetic field J , p K is generated over a shorter time interval, so that as the rotational speed of the rotor 164 increases, more power is generated because more harvestable energy in the form of voltage pulses is generated per unit time from the Wiegand inductor. It should be understood that graphs 810, 820, and 830 shown in Figure 8 are intended to illustrate the general concepts only and are not intended to convey the actual values ​​of the various attributes plotted thereon.

[0117] FIG. 9 shows a graph of experimental data collected from an actual non-limiting Wiegand inductor embodiment in response to a rotating magnetic field. The data was collected using an oscilloscope. Note that the voltage generated by the Wiegand inductor is shown directly, before any voltage adjustments are made. That is, the voltage output by transducer 168 (as shown in FIGS. 2A and 4A) is shown before adjustments are made by converter box 170. Time is plotted on the x-axis in milliseconds (each vertical line represents 1.000 milliseconds), and voltage is plotted on the y-axis in volts (each horizontal line represents 2.00 volts). The graph shows three voltage pulses p1, p3, and p1 of the second cycle generated by the Wiegand inductor, as shown in FIGS. 6A-6C. As discussed herein in connection with FIGS. 6A-6F, in this case, the second voltage pulse p2 and the fourth voltage pulse p4 do not register on the aforementioned voltage scale on the oscilloscope because they unintentionally generate negligibly small energy. Pulse p1 of the first cycle has a maximum amplitude of approximately 6 volts. The next pulse p3 has a maximum amplitude of approximately (-6) volts, which becomes negative in value as a result of the change in direction of the magnetic field shown in FIG. 6E. Pulse p1 of the second cycle has a maximum amplitude of approximately 6 volts, which becomes positive in value as a result of the change in direction of the magnetic field shown in FIG. 6B. As can be seen from FIG. 9, each voltage pulse p1, p3 includes an initial spike that reaches a maximum amplitude, followed by a series of oscillations that gradually decrease to zero voltage. FIG. 10 shows a close-up view of pulse p1 of the first cycle of FIG. 9 illustrating these oscillations (enlarged so that each vertical line represents 50.00 microseconds). The initial spike s1 reaches the maximum voltage of the first pulse p1, approximately 6.0002 volts. Subsequent spikes s2 through s11 oscillate around zero volts, successively decreasing in amplitude until the signal stabilizes at zero volts.

[0118] 11 provides a graphical illustration of the root mean square (RMS) voltage output of a transducer 169 in the form of a dynamo, which may be used as an alternative inductor embodiment to the Wiegand inductors described herein. Graph 910 shows magnetic flux B plotted against time t. Two different magnetic flux curves L and M are shown, representing two different rates of alternating magnetic field change. Curve L has a relatively slower magnetic flux change over time compared to curve M. Graph 920 shows the root mean square voltage V associated with curve L, plotted against time t. L and the root mean square voltage V associated with curve M M Graph 920 shows the root mean square voltage generation over time for a changing magnetic field as compared to graph 910. As can be seen from graph 920, the voltage V L , V M is output with a nearly constant root-mean-square value, in contrast to the series of voltage pulses p output by a Wiegand inductor (shown in FIG. 8). The AC voltage output of dynamo 169 and the corresponding root-mean-square voltage output depend on the rate of change of the magnetic field, so the output voltage V associated with curve L L is the output voltage V associated with curve M M This is because the pulse p J , p KThis contrasts with the pulse output of Wiegand inductor 168 (see FIG. 8), where the amplitude of the AC voltage is independent of the rate of change of the magnetic field, but the number of pulses produced per unit time is affected by the rate of change of the magnetic field. Graph 930 shows the energy of the AC voltage plotted against the rotational speed of the magnetic field, i.e., the rotational speed of rotor 164. As can be seen from graph 930, the amplitude and frequency of the AC voltage produced by dynamo 169 increase linearly in proportion to increasing rotational speed of rotor 164, and therefore the average electrical energy increases approximately linearly with the rotational speed of the magnetic field. That is, increasing the rotational speed of the changing magnetic field increases the amplitude of the root-mean-square voltage output of dynamo 169 linearly. This is in contrast to the Wiegand inductor of Figure 8, in which the voltage amplitude of each pulse p remains constant regardless of the rotation rate of the magnetic field, i.e., in the Wiegand inductor of Figure 8, as the rotation rate of the changing magnetic field increases, the amplitude of pulse p1 remains constant, the amplitude of pulse p2 remains constant, the amplitude of pulse p3 remains constant, and the amplitude of pulse p4 remains constant. It should be understood that graphs 910, 920, and 930 shown in Figure 11 are intended to illustrate the general concepts only, and are not intended to convey the actual values ​​of the various attributes plotted therein.

[0119] When dynamo 169 is exposed to multiple changing magnetic fields simultaneously, such as when the magnetic fields of curves L and M are imposed on dynamo 169, dynamo 169 generates more voltage power in the form of a larger RMS voltage output. This occurs whether or not the magnetic fields of curves L and M are phase-changing.

[0120] FIG. 12 shows a graph of experimental data collected from an actual, non-limiting dynamo embodiment in response to a rotating magnetic field. The data was collected using an oscilloscope. Note that the voltage generated by the dynamo inductor is shown directly, before any voltage adjustments are made. That is, the voltage output by transducer 169 (as shown in FIGS. 2B and 4B) is shown before adjustments are made by converter box 171. Time is plotted on the x-axis in milliseconds (each vertical line represents 10 milliseconds), and voltage is plotted on the y-axis in volts (each horizontal line represents 2.00 volts). In contrast to the periodic pulses p1, p3, p1 exhibited by the Wiegand inductor of FIGS. 8-10, the graph shows that the output voltage follows a substantially uniform waveform w. In the illustrated embodiment, the wavy curve w has an amplitude of approximately 5.7 volts and a frequency of approximately 51.962 Hz, and the root-mean-square voltage corresponding to this AC output is 1.839 volts. As discussed in connection with Figure 11, the amplitude of the RMS voltage depends on the speed of the rotating magnetic field, and thus the wave-like curve w shown in Figure 12 represents only specific rotational speeds of the magnetic field. Magnetic fields having different rotational speeds cause the dynamo 169 to generate root-mean-square voltages of different amplitudes. More specifically, magnetic fields having rotational frequencies faster than about 52 Hz generate higher root-mean-square voltages, and magnetic fields having rotational frequencies slower than about 52 Hz generate lower root-mean-square voltages.

[0121] While the foregoing description primarily relates to medical devices, specifically extracorporeal circulation system 10, those skilled in the art will appreciate that the principles described herein may be applied to other technical fields as well. For example, the electrical circuitry shown in FIGS. 2, 4, and 5, including transducer 168 and associated components, may be implemented in various fluid flow systems other than extracorporeal circulation by removing oxygenator 18 and replacing blood pump 16 with a fluid pump suitable for the desired system that pumps fluids other than blood. Similarly, at least one sensor 180 may include any sensor or other low-power electronic component of the desired system. For example, the electrical circuitry shown in FIGS. 2, 4, and 5, including transducer 168 and associated components, may be implemented in a hemodialysis machine having transducer 168 that provides power to sensors associated with the dialyzer. Those skilled in the art will understand that it is within the scope of this disclosure to more generally use a transducer 168 in the form of a Wiegand inductor or dynamo to harvest energy from an electric motor that induces a rotating or changing magnetic field and use the harvested energy to power sensors and other electronic components.

[0122] While the foregoing description provides various examples of the present disclosure, those skilled in the art may make changes and modifications to these examples without departing from the scope and spirit of the present disclosure. For example, it should be understood that features of various embodiments described herein may be adapted to other embodiments described herein. Accordingly, the foregoing description is intended to be illustrative rather than limiting. The disclosure set forth hereinabove is defined by the appended claims, and all changes to the disclosure that come within the meaning and range of equivalency of the claims are embraced therein.

Claims

[Claim 1] The invention described in this specification.

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