Shape memory alloys are used in aerospace structures, orthodontics, cardiovascular prosthetic devices, sensors and controllers, and many other engineering, technology, science, and other fields. The methods are described in the case of a temporary heart assist pump to illustrate the concepts, but the method applies to many other fields. The properties of shape memory alloys are used to fold or collapse and implant in the human body a device without breaking the device as it reaches body temperature or without reaching permanent plastic deformation. The properties of nitinol are also used to describe intended explantation of the device, at body temperature, from the body without breaking it. Such planned explantation may be needed in cases where the device is designed for temporary use, such as mechanical circulatory support devices intended for temporary use and then removal of all components of the device from the body. The same method can be used for devices that have not been initially designed for removal, such as stents or valves, that must later be explanted for reasons unanticipated when they were installed. The methods ensure that the devices stay within stress-strain-temperature conditions so they remain elastic, or under the upper stress plateau, or remain plastic, but always under the breaking strain, of shape memory alloys at: room or environmental conditions; cooler than environmental conditions; and at a higher temperature, or body temperature. The methods described may also be applied to other industrial applications, where shape memory alloys may be installed and removed at different temperatures. Applications in other industries, include aerospace, civil structures, mechanical structures are contemplated.

Shape memory alloys are used in aerospace structures, orthodontics, cardiovascular prosthetic devices, sensors and controllers, and many other engineering, technology, science, and other fields. The methods are described in the case of a temporary heart assist pump to illustrate the concepts, but the method applies to many other fields. The properties of shape memory alloys are used to fold or collapse and implant in the human body a device without breaking the device as it reaches body temperature or without reaching permanent plastic deformation. The properties of nitinol are also used to describe intended explantation of the device, at body temperature, from the body without breaking it. Such planned explantation may be needed in cases where the device is designed for temporary use, such as mechanical circulatory support devices intended for temporary use and then removal of all components of the device from the body. The same method can be used for devices that have not been initially designed for removal, such as stents or valves, that must later be explanted for reasons unanticipated when they were installed. The methods ensure that the devices stay within stress-strain-temperature conditions so they remain elastic, or under the upper stress plateau, or remain plastic, but always under the breaking strain, of shape memory alloys at: room or environmental conditions; cooler than environmental conditions; and at a higher temperature, or body temperature. The methods described may also be applied to other industrial applications, where shape memory alloys may be installed and removed at different temperatures. Applications in other industries, include aerospace, civil structures, mechanical structures are contemplated.

This invention is directed to a corrosion-resistant permanent magnet, to a method for producing a corrosion-resistant permanent magnet, and to an intravascular blood pump comprising the magnet. The magnet is corrosion resistant due to a composite coating comprising a first layer structure and optionally a second layer structure on the first layer structure, each layer structure comprising an inorganic layer, a linker layer on the inorganic layer, and an organic layer formed from poly(2-chloro-p-xylylene) on the linker layer. The inorganic layers comprise aluminum and/or aluminum oxide.

This invention is directed to a corrosion-resistant permanent magnet, to a method for producing a corrosion-resistant permanent magnet, and to an intravascular blood pump comprising the magnet. The magnet is corrosion resistant due to a composite coating comprising a first layer structure and optionally a second layer structure on the first layer structure, each layer structure comprising an inorganic layer, a linker layer on the inorganic layer, and an organic layer formed from poly(2-chloro-p-xylylene) on the linker layer. The inorganic layers comprise aluminum and/or aluminum oxide.

Mechanical circulatory supports configured to operate in series with the native heart are disclosed. In an embodiment, an intravascular propeller is installed into the descending aorta and anchored within via an expandable anchoring mechanism. The propeller and anchoring mechanism may be foldable so as to be percutaneously deliverable to the aorta. The propeller may have foldable blades. The blades may be magnetic and may be driven by a concentric electromagnetic stator circumferentially outside the magnetic blades. The stator may be intravascular or may be configured to be installed around the outer circumference of the blood vessel. The support may create a pressure rise between about 20-50 mmHg, and maintain a flow rate of about 5 L/min. The support may have one or more pairs of contra-rotating propellers to modulate the tangential velocity of the blood flow. The support may have static pre-swirlers and or de-swirlers. The support may be optimized to replicate naturally occurring vortex formation within the descending aorta.

Mechanical circulatory supports configured to operate in series with the native heart are disclosed. In an embodiment, an intravascular propeller is installed into the descending aorta and anchored within via an expandable anchoring mechanism. The propeller and anchoring mechanism may be foldable so as to be percutaneously deliverable to the aorta. The propeller may have foldable blades. The blades may be magnetic and may be driven by a concentric electromagnetic stator circumferentially outside the magnetic blades. The stator may be intravascular or may be configured to be installed around the outer circumference of the blood vessel. The support may create a pressure rise between about 20-50 mmHg, and maintain a flow rate of about 5 L/min. The support may have one or more pairs of contra-rotating propellers to modulate the tangential velocity of the blood flow. The support may have static pre-swirlers and or de-swirlers. The support may be optimized to replicate naturally occurring vortex formation within the descending aorta.

The present disclosure relates to a motor for an extracorporeal blood pump, an extracorporeal blood pump, and an extracorporeal blood pump system. The motor for an extracorporeal blood pump comprises: a housing; an actuator located in the housing and used for driving an impeller in a pump head of the extracorporeal blood pump; at least one sensor located in the housing; and a motor driving-control assembly located in the housing and used to control operation of the motor. Integrating the motor driving-control assembly into the housing of the motor can significantly reduce the dependence of the motor on the control host of the extracorporeal blood pump, the risk of communication failure between the motor and the control host, and the risk of malfunction of the motor driving-control assembly, thereby greatly improving the safety and reliability of the extracorporeal blood pump.

The present disclosure relates to a motor for an extracorporeal blood pump, an extracorporeal blood pump, and an extracorporeal blood pump system. The motor for an extracorporeal blood pump comprises: a housing; an actuator located in the housing and used for driving an impeller in a pump head of the extracorporeal blood pump; at least one sensor located in the housing; and a motor driving-control assembly located in the housing and used to control operation of the motor. Integrating the motor driving-control assembly into the housing of the motor can significantly reduce the dependence of the motor on the control host of the extracorporeal blood pump, the risk of communication failure between the motor and the control host, and the risk of malfunction of the motor driving-control assembly, thereby greatly improving the safety and reliability of the extracorporeal blood pump.

The invention includes three flushing channels each having a flushing channel longitudinal axis oriented parallel to the rotary shaft, which are distributed evenly around a rotary shaft with each flushing channels including a flushing channel cross-section oriented orthogonally to the rotary shaft. The cross-sections are each kidney-shaped and surround the rotary shaft in sectors.

The invention includes three flushing channels each having a flushing channel longitudinal axis oriented parallel to the rotary shaft, which are distributed evenly around a rotary shaft with each flushing channels including a flushing channel cross-section oriented orthogonally to the rotary shaft. The cross-sections are each kidney-shaped and surround the rotary shaft in sectors.