fig1 illustrates the expanded impeller with the bearing element 1 and the bearing lip 3 movably coupled with the central rotating element 17 . the central rotating element is substantially configured from deformable materials such as polymers , metal alloys or carbon based elements and may be constructed by coupling modular components which allow for the change in length as the network of wires comprising the pump change in length with expansion from the constrained state to the expanded state . the impeller blades 5 are formatted in several rows which are clocked and interleaved to allow for a mixed pump configuration . the mixed axial and centrifugal configuration is defined by adjusting the shrouding elements on the inner stent as well as the leading edge 7 angle , trailing edge 9 angle , chord angle and chord length of each blade . when in the constrained configuration the impeller blades are movable coupled around the central rotating element 17 and may utilize the magnetic interaction of the magnets in the impeller blade edges in 11 a , 11 b and 11 c to either attract or repel and thus assist in constraining or expanding the blades . the magnetic are positioned by inserting through the magnet insertion opening 13 . the magnet insertion opening may be round as the blade deforms in the preparation stage to allow the insertion of the magnet and once the magnet is inserted it configures to an asymmetric shape to prevent the migration of the magnet with rotation of the blade . fig2 illustrates the cross - section of the impeller blades 5 a , 5 b and 5 c with the embedded magnets 11 c detailed in the third row of impeller blades 5 c . two other rows of blades are drawn illustrating the plurality of blades that can be used to create an optimal pump configuration . the blades are in the expanded configuration and are drawn as being single entity that includes the central rotating element 17 movably coupled to the bearing system 1 . supporting the central rotating element 17 is a central rotating element support shaft 19 is hollowed out to form a guidewire slot 20 . the guidewire slot 20 and support shaft 19 are movably coupled to the central rotating element 17 and the impeller blades 5 a , 5 b and 5 c . as exemplified , the impeller blade 5 a when expanded form a suction face 21 and a pressure face 23 with the magnet on the impeller blade edge 11 a movably coupled to the edge via the magnet insertion point 13 . fig3 is an oblique view of the expandable impeller pump in the configuration of an expandable motor substantially composed of a row of stator coil elements 25 a with associated ferromagnetic elements 27 a , closely approximated to the first row of impeller magnets 11 a . a plurality of magnets embedded on the blade edges 11 a , 11 b and 11 c are electromagnetically coupled to outer rows of stator elements . the bearing element 1 is movably coupled to the central rotating element supported by the central support shaft 19 being hollowed out to form a guidewire passage 20 . the impeller pump once expanded and rotating , forms a suction face 21 and pressure face 23 with mixed axial and centrifugal flow characteristics generated from the rotational torque derived from the electromagnetic interaction of the expandable motor elements . the electromagnetic field forces created by the passage of an alternating current within the stator coil element 25 a coupled to the magnets within the blade edges 11 a also generates a back electromagnetic force current which can be used to sense and modify the rotational speed by varying the alternating current . fig4 is an oblique view of the expanded motor and impeller with a plurality of impeller blades with magnet on the edges exemplified by 11 c closely approximated to several rows of stator coils 25 a , 25 b and 25 c which contain several ferromagnetic elements 27 a , 27 b and 27 c . the impeller blades are clocked and interleaved to allow for a folding pattern around the central rotating element 17 that compresses the impeller to a diameter that allows for minimally invasive delivery either through a peripheral artery such as the femoral artery or subclavian artery or through the left ventricular apex directly into the ascending aorta . the central rotating element support shaft 19 and hollow guidewire passage 20 allow for a central guidewire to be used to guide the device in its compressed form to the ascending aorta and adjust its position across the aortic valve such that once activated the coronaries are still perfused and sufficient pressure is generated to maintain and augment perfusion to the distal organ beds . additionally , the device can be placed in the venous system to augment right ventricular function or assist in decompressing the venous system . fig5 illustrates the inner stent main body 37 suspending the impeller at the cylindrical support elements 29 with one row of stator coils 25 a and ferromagnetic elements 27 a . the suspension of the components of a compressible pump requires a superstructure with an integrated motor that is self - expanding and will restore to a predictable configuration while allowing for full expansion of the impeller pump suspended within . a cylindrical - shaped impeller pump support structure is described in fig5 by the presence of proximal 29 a and distal 29 b cylindrical support elements . the proximal and distal support elements are two smaller cylindrical - shaped non - compressible elements that are movably coupled to the main body of the inner stent 37 by proximal vane struts 31 and distal vane struts 35 that are varied in dimensions , preferably in diameter and height to accommodate the requirements of the pump . the proximal 29 a and distal 29 b cylindrical - shaped support elements of fig5 are attached and movably coupled to the central stent by struts that are fashioned by laser cutting one single tube of material . fig6 demonstrates an expanded embodiment of the inner main stent body with the cylindrical support elements 29 a and 29 b , expanded proximal vane struts 31 , and distal vane strut 35 , movably coupled to the expanded but unfolded proximal vane elements 33 a and unfolded distal vane elements 33 b . the unfolded vane elements 33 a and 33 b are movably coupled to the main body of the inner stent 37 . fig7 embodies the expanded inner main stent body which substantially has the inward folded proximal vane elements 33 a and outward folded distal vane elements 33 b movably coupled to the expanded proximal vane struts 31 and distal vane struts 35 . the inward folding vane elements 33 a assist in directing the inflow of fluid as well as assisting the augmentation of impeller flow . the outward folding distal vane elements 33 b assist in straightening the flow of fluid as well as augmenting the pressure head of the impeller rotation . fig8 is an embodiment of an expandable motor that substantially incorporates the expandable impeller pump with magnets on blade edges illustrated in 11 a , 11 b and 11 c . the expandable motor is further defined by the stator coil row 25 a with the integrated ferromagnetic elements 27 a supported on the inner stent main body 37 . the application of an alternating electromagnetic current within the stator coil 25 a creates a magnetic flux interaction with the embedded blade magnets 11 a , 11 b and 11 c with a resultant an electromagnetic torque force . the expanded impeller blade 5 of the third row embodies the plurality of blades that rotate about the central support elements 29 as the electromagnetic torque force translates to rotation about the central axis . the inner main stent 37 is movably coupled to the inward folding vane element 33 a by the proximal vane strut 31 and distal vane strut 35 which expands to a preset formation on expansion , similarly , the outward folding vane element 33 b expands to a predetermined angulation that straightens and redirects the fluid exiting the pump so as to maximize the pressure augmentation while minimizing blood trauma and shear . notably , the inner stent main body 37 has position slots as illustrated by 39 a and 39 b that assist in positioning and locking the inner main stent to an outer nested stent . fig9 is an embodiment of the nested stent and the inner main stent . the nested stent is substantially described by a proximal annular flare 45 , a sinus expansion 47 , sino - tubular contact support 49 and a distal aortic flare 51 . the interlocking of the two stent systems is embodied in the interaction of the paired distal position slots 39 b of the inner main stent with the distal position strut of the nested stent 43 b and further exemplified by the proximal position struts 41 b of the nested stent . the paired distal position slots 39 b are movably coupled to the single position strut 43 b which allows for the extraction and reimplantation of the inner expandable motor and impeller pump by constraining the inner main stent 37 , vanes 33 a and 33 b , impeller 5 , the motor coil elements 25 a , 25 b and 25 c and motor ferromagnetic elements 27 a , 27 b and 27 c . fig1 is a cross - section of the nested outer stent components 45 , 47 , 49 , 51 , inner main stent 37 , expanded motor 25 a , 27 a and expanded impeller 5 a and 5 c . the impeller blades edged with the embedded magnets 11 a , 11 b and 11 c are movably coupled around the central rotating element 17 . a central rotating element support shaft 19 is hollowed out to facilitate the passage of a guidewire 20 which in turns allows for accurate positioning and deployment within the arterial tree or venous system . the impeller blades 5 a and 5 c represent a plurality of blades that are clocked and interleaved , each with a suction face 21 and a pressure face 23 that are configured upon the operational expansion of the constrained system . the cylindrical support elements 29 are movably coupled with the bearing system 1 at each end of the central rotating element 17 . the interlocking and stabilization of the inner stent 37 and the nested outer stent interaction is embodied in the proximal position strut 41 a of the outer nested stent and the single distal position strut 43 c of the nested stent . fig1 is a magnified cross - section of the impeller blade 5 , stator coils 25 a , inner stent 37 and nested inner stent 45 , 47 and 49 . the proximity of the impeller blade edge 55 to the stator coils 25 a allows for the electromagnetic flux lines to be formed across the air gap 53 between the embedded ferromagnetic elements 27 a , stator coils 25 a and blade magnets . the cross - section also demonstrates the interlocking of the paired distal position slots of the inner stent 39 b and the distal position strut of the nested outer stent 43 b which stabilizes for axial and radial displacement . in one embodiment , the elastic deformation of the distal position strut with axial force could result in the displacement of the inner stent thus allowing for its removal and interchange should the unit become dysfunctional , in another embodiment , the inner main stent could be equipped with a tri - leaflet valve , such that if there is recovery of the heart after a period of support from the ventricular assist device , then normal valvular function can reestablished . the interchange of the pump unit for a valve unit can be performed by current percutaneous aortic valve replacement techniques . fig1 illustrates the cross - sectional view of the nested outer stent proximal and distal ends . the distal aortic flare 51 is seen with the distal position struts 43 a , 43 b and 43 c . the proximal position struts 41 a , 41 b and 41 c are clocked at an offset to the distal position struts , the two strut system provide restraint against the rotational and radial forces of the impeller of the inner main stent . the two strut systems also provide restraint against the radial compressive and expansive forces of the aortic annular and sino - tubular motion during the systolic and diastolic phases of the cardiac cycle . fig1 reinforcement of the inner main stent body radial diameter can also be provided by shroud elements 57 stationed at various positions along the length of the inner stent . energy transfer coils 61 can also be patterned within medical textiles to collapse with constraint of the system and expand on deployment or on activation and these also serve as additional reinforcement mechanisms . in another embodiment of the inner stent body expands circumferentially 59 at various points along its length to different radial dimensions to allow for better seating of the stent within the aortic wall and more specifically into the coronary sinus of the aortic valve and outflow tract . these areas of circumferential expansion 59 along with the shrouding elements 57 and the energy transfer elements 61 create augmented flow patterns to both the systemic and coronary system if the unit is deployed so as a replacement for the native aortic valve . the most optimal deployment strategy may vary with the native heart function however , the impeller pump blades 5 rotating about the central element 17 when deployed at the aortic root does serve to replace the native aortic valve , while being in line with the flow of blood , thus augmenting systolic flow and limiting diastolic regurgitation . additional flow straightening and diffusing is supplied by the proximal vane elements 33 a and distal vane elements 33 b . fig1 illustrates a woven medical textile fabric 63 with insulated wire coils 65 woven in . the inner stent main body 37 , distal vane elements 33 b and cylindrical support element 29 are also illustrated . the integration of a motor design onto a stent that is compressible requires flexible elements . motor design requires the integration of magnetic and electromagnetic elements . the placement of electromagnetic elements onto a stent requires a platform upon which stator coils are configured . in one embodiment the stator coil base material is a woven fabric 63 such as polyester or polyethylene . finely woven medical textiles are compressible and of low profile and can allow the attachment of insulated wire coils 65 in patterns that produce magnetic lines of flux . the integration of woven medical fabrics onto the stent main body network of wires 37 can be onto the inner or outer aspect or , as an integral component of the stent design such that the fabric and wire network are interwoven . in another embodiment the attachment of the fabric can be with permanent material wound in a spiral pattern or individual attachment windings or knots . in another embodiment the winding of electromagnetic coils can be without a fabric backing and as an interwoven coil that expands along with the expansion of the stent into a prearranged configuration and pattern that allows for magnetic field alignment . in another embodiment the woven fabric can be placed in a pattern to match the pattern of magnets within the impeller pump blades for example , to configure the compressible motor as a brushless dc motor . in another embodiment , the pattern of the stator coils and medical textile configures to a circular iris of an even number of stator coils that are circumferentially arranged and typically overlap when in the compressed state . this embodiment of stator coils woven into a medical textile can be patterned to follow the magnetic flux lines created by the magnetic material within the impeller blades . fig1 illustrates a cross - sectional image of the inner stent and the energy transfer coil . the relative position of the energy transfer coils 61 a and 61 b to inner stent components illustrated . the area of circumferential expansion 59 , the cylindrical support element 29 , central rotating element 17 , central rotating element support shaft 19 , hollow guidewire passage 20 , proximal vane strut and distal vane struts 35 are shown . the energy transfer coils is demonstrated in one embodiment as two layers of wire coils 61 a and 61 b in a compressible configuration , insulated with a medical textile 63 a and 63 b . the medical textile can be interwoven within the wire frame or layered on the outer or inner surface . fig1 illustrates a powering scheme that utilizes wireless energy transfer . the powering of the electromagnetic coils requires an external power source . recent advances in wireless telemetry within the human body have made it possible to consider continuously powering of a collapsible pump . fig1 illustrates power coils 67 that are described on the outside of the aorta 69 that is connected to a battery source 71 a and 71 b by a coaxial cable 73 . in one embodiment the power coils 67 are an integrated onto a polygonal shape of flexible or semi - rigid material 75 . this is positioned on the outside of the aorta 69 in the ascending or descending portion or on the surface of the heart 77 , taking care to avoid the epicardial arteries 79 . the placement of this wireless power coil 67 on the outer aspect of the ascending aorta allows for wireless energy transmission to an inner stent coil 61 located at the level of the ascending aorta and aortic root . in one embodiment , the energy coil outside of the aorta 67 is a coil in a polygonal shape preferably rectangular or square with several loops that are insulated wires , typically copper or of another conductive material . these loops are formed on a mandrel and sewn onto a medical fabric which is in turn attached to a delivery system . in one embodiment the coils and fabric are compressed into a tubular fashion and introduced by a port into the pleural cavity and delivered by minimally invasive means to the outer aortic wall . a certain maximum and minimum distance can be achieved based on the anatomical factors which reflect the patients past medical and surgical history . these loops can be delivered prior to the implantation of the stent carrying the pick - up coils for the energy transmission . the size and orientation of the transmission coil patch is matched to the size and orientation of the pick - up coils on the inner stent 61 so that the magnetic fields align to optimize energy transmission efficiency . in another embodiment the coils are layered on an insulating material or medical textile 63 a and 63 b and are constructed of overlapping and connected wires . an alternative embodiment describes a direct energy cable 81 to power the expandable motor and pump that traverses the aortic wall or runs the length of the aorta and exits via a peripheral vessel . fig1 illustrates a transvalve stent impeller design that allows for preservation of the aortic valve . the system is designed around a collapsible stent main body that is described as a network of wires 89 with integrated energy coils 61 . the central shaft 99 supports a cylindrical support element 83 that is movably coupled to a plurality of distal vane elements 87 a , 87 b and 87 c . the ability to traverse the aortic valve and maintain the function of the pump is derived by constraining the network of wires 89 for passage through the valve orifice . once the proximal and distal components are expanded , the constraining element 91 at the level of the valve allow for closure of the native valve and maintenance of its function . a proximal subannular expansion of the wire network forms an annular shroud 93 which is again supported by a plurality of proximal vane elements 101 a , 101 b and 101 c . the expandable impeller 95 is supported by the proximal cylindrical support 97 . fig1 illustrates an oblique view of the transvalve stent impeller . the embodiment described has a network of wire elements 89 that are initially constrained for passage across the cardiac valve then expanded . the proximal component forms an annular shroud 93 that surrounds the collapsible impeller 95 . the distal component forms a wire network that is cylindrical and conforms to the ascending aorta . the wire network may embody a plurality of integrated energy coils 61 for energy transfer and support as well as independently functioning as stator coils for an expandable motor . the distal support elements include a plurality of distal vane elements 87 a , 87 b , and 87 c that are movably coupled to a central shaft 99 . fig1 a illustrates a monorail delivery system that is constrained . the guidewire 111 is alongside the outer catheter sheath 105 and passes through a small slot 107 at the tip of the catheter sheath . the wire extends through the protective tip sheath 109 to exit at the center - point of the delivery system . fig1 b illustrates the expansion of the stent from the restraining outer sheath 105 . an inner sheath 103 is used to apply axial force to the distal portion of the restrained stent . the stent on expansion 115 has a constrained area 113 that remains within the sheath until final positioning is confirmed . the impeller 117 shown is unexpanded . the proximal vane 119 is expanded and provides initial support for the expanded proximal portion of the stent . while the foregoing details what is felt to be the preferred embodiment of the invention , no material limitations to the scope of the claimed invention are intended . further , features and design alternatives that would be obvious to one of ordinary skill in the art are considered to be incorporated herein . the scope of the invention is set forth and particularly described in the claims hereinbelow .
an apparatus with a compressible construction having a wireless power source structured around a cylindrical - shaped support that suspends a motor within the vascular system while also supporting an impeller pump that can be made to be collapsible . the whole system allows for a minimally invasive pump implantation and augmentation of flow .