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WO2020006324A1 - Dispositif artificiel péristaltique d'assistance cardiaque et ventriculaire - Google Patents

Dispositif artificiel péristaltique d'assistance cardiaque et ventriculaire Download PDF

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Publication number
WO2020006324A1
WO2020006324A1 PCT/US2019/039634 US2019039634W WO2020006324A1 WO 2020006324 A1 WO2020006324 A1 WO 2020006324A1 US 2019039634 W US2019039634 W US 2019039634W WO 2020006324 A1 WO2020006324 A1 WO 2020006324A1
Authority
WO
WIPO (PCT)
Prior art keywords
elastomeric element
magnetic
mandrel
peristalsis
artificial heart
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/US2019/039634
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English (en)
Inventor
Steve Smith
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Individual
Original Assignee
Individual
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Filing date
Publication date
Application filed by Individual filed Critical Individual
Publication of WO2020006324A1 publication Critical patent/WO2020006324A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/247—Positive displacement blood pumps
    • A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
    • A61M60/268—Positive displacement blood pumps including a displacement member directly acting on the blood the displacement member being flexible, e.g. membranes, diaphragms or bladders
    • A61M60/279—Peristaltic pumps, e.g. roller pumps
    • A61M60/284—Linear peristaltic pumps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/247—Positive displacement blood pumps
    • A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
    • A61M60/268—Positive displacement blood pumps including a displacement member directly acting on the blood the displacement member being flexible, e.g. membranes, diaphragms or bladders
    • A61M60/279—Peristaltic pumps, e.g. roller pumps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
    • A61M60/178—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart drawing blood from a ventricle and returning the blood to the arterial system via a cannula external to the ventricle, e.g. left or right ventricular assist devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/196—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body replacing the entire heart, e.g. total artificial hearts [TAH]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/424—Details relating to driving for positive displacement blood pumps
    • A61M60/457—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being magnetic
    • A61M60/462—Electromagnetic force

Definitions

  • This invention relates generally to apparatus for sustaining and continuing life for patients having failing or failed hearts and particularly to artificial devices, known generally in the art as “Artificial Hearts” and those known as “Ventricular Assist Devices” (VADs), including ventricular assist devices such as “Left Ventricle Assist Devices” (LVADs) used to supplement the performance of weak or failing hearts.
  • Artificial Hearts and those known as “Ventricular Assist Devices” (VADs)
  • ventricular assist devices such as “Left Ventricle Assist Devices” (LVADs) used to supplement the performance of weak or failing hearts.
  • Ventricular assist devices provide an implantable mechanical pump that helps blood flow from the lower chambers of a weakened heart, the ventricles, to other parts of the body or other parts of the heart itself .
  • LVAD ventricular assist devices
  • a successful artificial heart or ventricular assist device must, above all, be long lasting and reliable. The dire consequences to the device recipient brought about by device failure make this requirement all too apparent.
  • the device must be small enough to be implantable within the recipient’s chest arid efficient enough to maintain adequate blood circulation to sustain normal life functions.
  • the device must avoid undue stress upon the recipient’s circulatory and pulmonary systems.
  • the device must also be capable of adjusting to and compensating for different recipient activity levels and stresses. Additional requirements such as avoidance of blood cell damage by the pumping apparatus and the prevention of blood clot forming stagnation regions make further demands upon ventricular assist devices.
  • a peristalsis pump comprising: an elastomeric element formed of a resilient magnetic elastomer defining a cylindrical shape having opposed ends and an interior passage therebetween; a cylindrical mandrel supported within the interior passage; a plurality of electromagnetic rings supported upon the mandrel; each of the electromagnetic rings supporting electrical windings oriented to produce radially oriented magnetic fields when energized; a multiplex controller controlling the energy in the electrical windings; and a blood flow channel formed between the interior passage and the plurality of electromagnetic rings, the controller energizing selected ones of electromagnetic rings to draw a portion of the elastomeric element into a localized constriction of the blood flow channel, and the controller sequentially energizing the selected ones of the plurality of the electromagnetic rings to advance the local ized constriction away from one of the opposed ends toward the other of the opposed ends creating a pumping action in tiie blood flow channel.
  • Figure 1 sets forth a perspective view of a peristalsis artificial heart constructed in accordance with the present invention
  • Figure 2 sets forth an end view of the peristalsis artificial heart shown in Figure 1;
  • Figure 3 sets forth a section view of the present invention peristalsis artificial heart taken along section lines 3 - 3 in Figure 2;
  • FIGS. 4A through 4H set forth sequential partial section views of the peristalsis pump apparatus used in the present invention peristalsis artificial heart illustrating the operative pumping cycle thereof;
  • Figure 5 sets forth a perspective view of an illustrative magnetic ring utilized in the present invention peristalsis artificial heart
  • Figure 6 sets forth a front view of the illustrative magnetic ring shown in Figure 5;
  • Figure 7 sets forth a section view of the illustrative magnetic ring shown in Figure 6 taken along section lines 7 - 7 therein;
  • Figure 8 sets forth a section view of the present invention peristalsis artificial heart at the midpoint of a pumping cycle
  • Figure 9 sets forth a section view of the present invention peristalsis artificial heart illustrating a plurality of short duration pumping cycles
  • Figure 10 sets forth a section view of an alternate embodiment of the present invention peristalsis artificial heart utilizing externally disposed magnetic ring arrays;
  • Figure 1 1 sets forth a section view of a further alternate embodiment of the present invention peristalsis artificial heart utilizing both internally disposed and externally disposed magnetic ring arrays;
  • Figure 12 sets forth a section view of an alternate embodiment of the present invention peristalsis artificial heart utilizing a continuous element design
  • Figure 13 sets forth a section view of a still further alternate embodiment of the present invention peristalsis artificial heart illustrating a curved variation
  • Figure 14 sets forth a section view of a still further alternate embodiment of the present invention peristalsis artificial heart providing a blood flow assist device housed within a blood vessel;
  • Figures 15A and 15B set forth section views of a still further alternate embodiment of the present invention peristalsis artificial heart providing a blood flow valve device housed within a blood vessel illustrating respective open and closed va
  • Figure 16 sets forth a front view of an illustrative magnetic ring utilized in the present invention peristalsis artificial heart which utilizes a coil orientation that is the reverse of the illustrative magnetic ring shown in Figure 5.
  • FIG. 1 sets forth a perspective View of a peristalsis artificial heart constructed in accordance with the present invention and generally referenced by numeral 10.
  • artificial heart 10 utilizes a pair of pump units 11 and 12.
  • the use of a pair of pump units facilitates the actions of artificial heart 10 in pumping blood returning from tile body to the recipient’s lungs, then returning to the second pumping portion of the heart to be further pumped for circulation throughout the recipient’s body.
  • artificial heart 10 is formed of a pair of pump units 1 1 and 12.
  • Pump units 11 and 12 are substantially identical in fabrication and are combined to form a complete artificial heart.
  • Pump unit 1 1 includes a housing 40 having a generally cylindrical housing portion 40 supporting end caps 41 and 42.
  • End cap 41 includes an input coupling 20 while end cap 42 includes an output coupling 21.
  • Couplings 20 and 21 are used to connect pump unit 1 1 to the recipient’s blood vessels.
  • pump unit 12 is constructed jn the same manner and includes a housing portion 44, end caps 45 and 46, an input coupling 30 and an output coupling 31. Couplings 30 and 31 are used to connect pump unit 12 to the appropriate blood vessels of the recipient.
  • FIG. 2 sets forth an end view of artificial heart 10 which as is described above includes a pair of pump units 11 and 12 are arranged in a side- by-side relationship.
  • pump unit 1 1 includes a housing portion 40 which in turn Supports an end 41 having an input coupling 20.
  • Pump unit 12 similarly includes a housing portion 44, in the caps 45 and 46, an output coupling 31.
  • FIG. 3 sets forth a section view of artificial heart 10 taken along section lines 3 -3 in Figure 2.
  • artificial heart 10 includes a pump unit 11 having a housing portion 40 (seen in Figure 1 ) supporting a pair of end caps 41 and 42. End caps 41 and 42 support input coupling 20 and output coupling 21 respectively.
  • pump unit 11 further includes a containment tube 57 extending between end caps 41 and 42 within which a magnetic elastomeric element 55 is received.
  • containment tube 57 is generally cylindrical and preferably made of a material such as titanium or the like.
  • magnetic elastomeric element 55 is also cylindrical and is resiliently positioned against the interior of containment tube 57.
  • magnetic elastomeric element 55 is formed of an elastomeric material that has been imbued with magnetic properties. While different formulas for fabricating magnetic elastomeric element 55 may be utilized without departing from the spirit and scope of the present invention, it has been found that a fluoroelastomer material that is combined with a large amount of metal particles, such as iron, in its precured liquid state and thereafter extruded to shape and cured results in a suitable flexible magnetic elastomer that provides the desired magnetic properties and elastic properties.
  • the metal particles may take the form of grindings, micro spheres or other small particulate.
  • pump unit 1 1 further includes a radial field generator 50 supported within the interior of pump unit 11 and generally centered within magnetic elastomeric element 55
  • Radial field generator 50 includes a pair of supporting mounts 52 and 53 which secure the centered position of radial field generator 50 within the interior of pump unit 1 1
  • Radial field generator 50 includes a generally cylindrical mandrel 51 supported between mounts 52 and 53.
  • a plurality of magnetic rings 56 are arranged in a stacked array upon mandrel 51 and are secured by mounts 52 and 53.
  • Radial field generator 50 further includes a multiplex controller circuit 60 supported within the interior of mandrel 51 and coupled to an external power and control systems (not shown) by a plurality of connecting wires 61.
  • magnetic rings 56 each include a plurality of radially oriented electro magnets and electromagnetic coils to facilitate the control of the magnetic fields produced by the electro magnets.
  • Each magnetic ring within magnetic rings 56 is independently controlled by multiplex controller circuit 60. While not shown in Figure 3, multiplex controller circuit 60 will be understood to be operatively coupled to each of the magnets within magnetic rings 56 in order to provide independent activation of the electro magnets described below.
  • magnetic rings 56 are not activated and thus are not creating radial magnetic fields.
  • magnetic elastomeric element 55 assumes the generally cylindrical shape illustrated in Figure 3 in which its natural resilience causes magnetic elastomeric element 55 to be urged outwardly against the interior surface of containment tube 57. Under these conditions, an unobstructed blood flow path is formed between elastomeric sheath 54 and the interior surface of magnetic elastomeric element 55.
  • magnetic rings 56 are activated in accordance with a predetermined sequence to impart a peristalsis pumping action.
  • Figures 4A through 4H set forth partial section views of a peristalsis artificial heart constructed in accordance with the present invention and generally referenced by numeral 100.
  • Figures 4 A through 4H are the sequential stages of an illustrative peristalsis pumping cycle, A critical aspect of this inventive pumping action is found in understanding the operation in which selecti ve electromagnets within the stacked array of electromagnets are energized to produce a localized constriction of the magnetic elastomeric element against the outer surface of the radial field generator. This localized constriction creates a localized seal of the blood flow passage at the point of constriction.
  • Figures 4A through 4H illustrate a basic pumping cycle in which a single constricting seal is moved across the magnetic ring array during the cycle. It will be understood that more complex pumping cycles may be implemented by moving multiple constricting seals across the magnetic ring array simultaneously.
  • Figure 9 sets forth an example of a multiple constricting seal pumping action.
  • Figures 4A through 4H each set forth a partial section view of peristalsis artificial heart 100 illustrating a radial field generator 65 supported between end caps 41 and 42, Radial field generator 65 includes a generally cylindrical mandrel 66 supported by a pair of mounts 62 and 63.
  • a multiplex controller circuit 60 is supported within the interior of mandrel 66.
  • a plurality of magnetic rings 70 through 99 are supported upon mandrel 66 and are secured in place by mounts 62 and 63. Suitable electric signal coupling (not shown) will be understood to be provided between the electromagnets of magnetic rings 70 through 79 (seen in Figure 6) and multiplex controller circuit 60 which allow independent activation of each of magnetic rings 70 through 99.
  • Radial field generator 65 further includes an elastomeric sheath 69 which encloses and seals the outer surfaces of magnetic rings 70 through 99.
  • a generally cylindrical containment tube 67 extends between end caps 41 and 42 and a generally cylindrical magnetic elastomeric element 64 is contained within containment tube 67.
  • magnetic elastomeric element 64 exerts an outward force against the interior surface of containment tube 67 sufficient to maintain the position of magnetic elastomeric element 64 in the configuration shown.
  • a blood flow channel 68 is formed between elastpmeric sheath 69 and the interior surface of magnetic elastomeric element 64.
  • artificial heart 100 is shown in its "relaxed" condition resulting from the absence of activation of the electromagnets within magnetic rings 70 through 99. Accordingly, radial field generator 65 does not create radial magnetic fields and thus does not exert a magnetic force against magnetic elastomeric element 64.
  • Figure 4B shows artificial heart 100 following the initiation of a peristalsis pumping cycle.
  • the electromagnets within magnetic rings 72 through 80 have been activated to produce radial magnetic fields characterized by an activation profile.
  • the relative levels of magnetic field activation of the electromagnets of magnetic rings 72 through 80 is selected to provide the desired localized constriction of magnetic elastomeric element 64.
  • the electromagnets of magnetic rings 74 through 78 have been activated to a level sufficient to create a localized constricting seal at position 32 which closes blood flow channel 68 at that location.
  • Figure 4C shows artificial heart 100 as the peristalsis pumping cycle continues.
  • the activation of the electromagnets has been shifted from magnetic rings 72 through 80 to magnetic rings 75 through 83.
  • the position of the resulting localized constricting seal of magnetic elastomeric element 64 has moved to position 33.
  • the movement of the constricting seal produces a corresponding flow of blood within the blood flow channel 68 in the direction indicated by arrow 58.
  • Figure 4D shows artificial heart 100 as the peristalsis pumping cycle continues.
  • the activation of the electromagnets has been shifted from magnetic rings 75 through 83 to magnetic rings 78 through 86.
  • the position of the resulting localized constricting seal of magnetic elastomeric element 64 has moved to position 34.
  • the movement of the constricting seal produces a further flow of blood within the blood flow channel 68 in the direction indicated by arrow 58.
  • Figure 4E shows artificial heart 100 as the peristalsis pumping cycle continues.
  • the activation of the electromagnets has been shifted from magnetic rings 78 through 86 to magnetic rings 81 through 89.
  • the position of the resulting localized constricting seal of magnetic elastomeric element 64 has moved to position 35.
  • the movement of the constricting seal produces a further flow of blood within the blood flow channel 68 in the direction indicated by arrow 58.
  • Figure 4F shows artificial heart 100 as the peristalsis pumping cycle continues.
  • the activation of the electromagnets has been shifted from magnetic rings 81 through 89 to magnetic rings 84 through 92.
  • the position of the resulting localized constricting seal of magnetic elastomeric element 64 has moved to position 36.
  • the movement of the constricting seal produces a further flow of blood within the blood flow channel 68 in the direction indicated by arrow 58.
  • Figure 4G shows artificial heart 100 as the peristalsis pumping cycle continues.
  • the activation of the electromagnets has been shifted from magnetic rings 84 through 92 to magnetic rings 87 through 95.
  • the position of the resulting localized constricting seal of magnetic elastomeric element 64 has moved to position 37.
  • the movement of the constricting seal produces a further flow of blood within the blood flow channel 68 in the direction indicated by arrow 58.
  • Figure 4H shows artificial heart 100 as the peristalsis pumping cycle continues.
  • the activation of the electromagnets has been shifted from magnetic rings 87 through 95 to magnetic rings 90 through 98.
  • the position of the resulting localized constricting seal of magnetic elastomeric element 64 has moved to position 38.
  • the movement of the constricting seal produces a further flow of blood within the blood flow channel 68 in the direction indicated by arrow 58.
  • FIG. 4H illustrates a basic peristalsis pumping cycle in which a single constricting seal is repetitively moved across the array of magnetic rings.
  • FIG. 9 illustrates a basic peristalsis pumping cycle in which a single constricting seal is repetitively moved across the array of magnetic rings.
  • each localized constricting seal such as constricting seal 32 seen in Figure 4B, presses against elastomeric sheath 69 upon the outer surfaces of magnetic rings 70 through 99 supported upon mandrel 66.
  • This provides a positive displacement pumping action as constricting seal 32 is forced into blood flow channel 68.
  • the constricting seal is moved, a positive displacement pumping action is provided.
  • the anticipated width of blood flow channel 68 is a small dimension in the order of 1/8 of an inch, or the like. As a result, the flexing of the constricting seal from its relaxed position to a constricting position is a relatively small movement distance.
  • the flexing of magnetic elastomeric element 64 defines a gradual curvature. This short distance movement and gradual curvature avoids undue stress upon magnetic elastomeric element 64 thereby avoiding fatiguing of the elastomeric material.
  • the avoidance of elastomeric material fatiguing is critical to providing long operative life and high reliability for the present invention pump.
  • FIG. 5 sets forth a perspective view of a magnetic ring generally referenced by numeral 1 10.
  • Magnetic ring 1 10 is illustrative of magnetic rings 56 utilized in artificial heart 10 shown in Figure 3 and is illustrative of magnetic rings 70 through 99 of artificial heart 100 shown in Figures 4A through 4H as well as other figures set forth below.
  • Magnetic ring 1 10 includes a metal desk 1 1 1 formed of a magnetic metal such as iron, steel or the like and defining surfaces 1 15 and 1 16 (surface 1 16 seen in Figure 7).
  • disk 111 may be fabricated of a magnetic ceramic material. The important factor in selecting tile material from which disk 1 1 1 is formed is the material's ability to function as an electromagnetic core material.
  • Magnetic ring 1 10 further includes a plurality of slots 1 12 which extend radially into disk 1 1 1 and which are equally spaced around the interior of disk 1 1 1. The presence of slots 112 forms a plurality of inwardly extending core elements 1 13 radially oriented and equally spaced about disk 1 1 1. Magnetic ring 1 10 further includes a plurality of conductive windings 114 each of which is wound about a core element 1 13. Windings 1 14 are interconnected by a plurality of connecting wires (not shown) which are utilized in coupling windings 1 14 of magnetic ring 1 10 to a source of electric current through multiplex controller circuit 60 (seen in Figure 3).
  • FIG. 6 sets forth a front view of magnetic ring 110.
  • magnetic ring 1 10 includes a metal desk 1 1 1 formed of a magnetic metal such as iron, steel or the like and defining surfaces 1 15 and 1 16 (surface 1 16 seen in Figure 7).
  • disk 1 1 1 may be fabricated of a magnetic ceramic material.
  • Magnetic ring 1 10 further includes a plurality of slots 1 12 which extend radially into disk 1 1 1 and which are equally spaced around the interior of disk 1 1 1. The presence of slots 1 12 forms a plurality of inwardly extending core elements 113 radially oriented and equally spaced about disk 1 1 1 , Magnetic ring 1 10 further includes a plurality of conductive windings 1 14 each of which is wound about a core element 1 13.
  • windings 1 14 are interconnected by a plurality of connecting wires (not shown) which are utilized in coupling windings 1 14 of magnetic ring 110 to a source of electric current through multiplex controller circuit 60 (seen in Figure 3).
  • Figure 7 sets forth a section view of magnetic disk 1 10 taken along section lines 7 - 7 m Figure 6.
  • magnetic ring i 10 includes a metal desk 11 1 formed of a magnetic metal such as iron, steel or the like.
  • disk 1 1 1 may be fabricated of a magnetic ceramic material.
  • Magnetic ring 110 further includes a plurality of slots 1 12 which extend radially into disk 111 and which are equally spaced around the interior of disk 111. The presence of slots 112 forms a plurality of inwardly extending core elements 113 radially oriented and equally spaced about disk 11 1. Magnetic ring 110 further includes a plurality of conductive windings 1 14 each of which is wound about a core element 1 13. As is also mentioned above, windings 114 are interconnected by a plurality of connecting wires (not shown) which are utilized in coupling windings 114 of magnetic ring 110 to a source of electric current through multiplex controller circuit 60 (seen in Figure 3).
  • disk 1 1 1 defines surfaces 1 15 and 1 16. It will be noted that core elements 113 are substantially thinner than the remainder of disk 111. As a result, windings 1 14 are recessed inwardly from surfaces 1 15 and 116. The recessing of windings 114 and the thinner width of core elements 113 maintains surfaces 115 and 116 outside of and beyond windings 114. This, in turn, facilitates the stacking of a plurality of magnetic rings upon a supporting mandrel in the manner set forth above in Figures 3 and 4A through 4H, as well as Figures 8 through 12, to form a cylindrical array having a generally continuous outer cylindrical surface.
  • the outer surface of the magnetic ring array is covered by an elastomeric sheath (see for example elastomeric sheath 54 shown in Figure 3). This provides a smooth boundary surface for the blood flow channel within the pump unit (see for example blood flow channel 68 shown in Figure 4A).
  • FIGS 8 and 9 set forth section views of an artificial heart 120 which are provided to facilitate a comparison between a single constricting seal pump cycle (Figure 8) and a multiple constricting seal pump cycle (Figure 9).
  • Artificial heart 120 which is shown filled with a quantity of blood 101, is substantially identical to artificial heart 10 shown above in Figure 3 apart from tiie use of angled mount supports 123 and 124.
  • artificial heart 120 includes a pump unit 11 having a housing portion 40 (seen in Figure 1) supporting a pair of end caps 41 and 42. End caps 41 and 42 support input coupling 20 and output coupling 21 respectively.
  • Pump unit 11 further includes a containment tube 57 extending between end caps 41 and 42 within which a magnetic elastomeric element 55 is received.
  • Containment tube 57 is generally cylindrical and, correspondingly, magnetic elastomeric element 55 is also cylindrical and is resiliently positioned against the interior of containment tube 57.
  • Magnetic elastomeric element 55 is formed of an elastomeric material that has been imbued with magnetic properties.
  • Pump unit 11 further includes a radial field generator 50 supported within the interior of pump unit 11 by supports 123 and 124 and is generally centered within magnetic elastomeric element 55.
  • Radial field generator 50 includes a pair of supporting mounts 52 and 53 which further secure the centered position of radial field generator 50 within the interior of pump unit 11.
  • Radial field generator 50 includes a generally cylindrical mandrel 51 supported between mounts 52 and 53.
  • Radial field generator 50 further includes a multiplex controller circuit 60 supported within the interior of mandrel 51 and coupled to an external power and control systems (not shown) by a plurality of connecting wires 61.
  • magnetic rings 56 each include a plurality of radially oriented electro magnets and electromagnetic coils to facilitate the control of the magnetic fields produced by the electro magnets.
  • Each magnetic ring within magnetic rings 56 is independently controlled by multiplex controller circuit 60.
  • Multiplex Controller circuit 60 will be understood to be operatively coupled to each of the magneto within magnetic rings 56 in order to provide independent activation of the electro magnets described below.
  • magnetic rings 56 are activated so as to create a localized radial magnetic fields acting upon magnetic elastomeric element 55 to produce a localized constriction 121 thereof.
  • the magnetic fields produced by magnetic rings 56 draw magnetic elastomeric element 55 against elastomeric sheath 54 creating a constricting seal 122.
  • constricting seal 122 is moved in the direction indicated by arrow 58 to push blood into and outwardly from end cap 42 ultimately flowing blood in the direction indicated by arrow 23.
  • Figure 9 shows the response of artificial heart 120 to electrical signals applied to magnetic rings 56 in a manner whereby multiple groups of magnetic rings are activated so as to create a plurality of localized radial magnetic fields acting upon magnetic elastomeric element 55.
  • This plurality of activated magnetic ring groups produces a plurality of localized constrictions 131 through 135.
  • Each localized constriction of elastomeric element 55 against elastomeric sheath 54 creates a constricting seal against elastomeric sheath 54.
  • localized constrictions 131 through 135 create constricting seals 141 through 145 respectively.
  • constricting seals 141 through 145 are moved in the direction indicated by arrow 58 to push successive quantities of blood into and through end cap 42 ultimately flowing blood in the direction indicated by arrow 23.
  • FIG. 10 sets forth a section view of a still further alternate embodiment of the present invention artificial heart generally referenced by numeral 150.
  • Artificial heart 150 differs from the previously described embodiments of the present invention it produces a peristalsis pumping action by expanding the magnetic elastomeric element rather than constricting it.
  • artificial heart 150 is similar to artificial heart 10 set forth above in Figure 3 in that a generally cylindrical tube 156 ports and caps 41 and 42 to form an artificial heart enclosure.
  • a mandrel 153 is supported by a pair of mounts 157 and 158 within the interior of artificial heart 150.
  • a multiplex controller circuit 60 is situated within mandrel 153 and is operative to control the activation of a plurality of magnetic rings 151.
  • the dispositions of magnetic rings 151 and magnetic elastomeric element 152 differ from the dispositions of magnetic rings 56 and magnetic elastomeric element 55 of artificial heart 10 shown in Figure 3 in that magnetic elastomeric element 152 is supported upon mandrel 153 and magnetic rings 151 are supported on the outside of magnetic elastomeric element 152, In essence, the operation of artificial heart 150 is "reversed" from the operation of artificial heart 10 described above.
  • multiplex controller circuit 60 activates magnetic rings 151 to create a localized expansion 154 of magnetic elastomeric element
  • magnetic rings 151 are sequentially activated to move localized expansion 154 and localized expansion seal 155 in the direction indicated by arrow 58.
  • the action by which localized expansion 154 is created in response to activation of magnetic rings 151 requires that magnetic elastomeric element 152 be imbued with a polarized magnetic property. This polarized magnetic property is provided by combining the material of magnetic elastomeric element 152 with a quantity of micro spherical magnets rather than metal particles or grindings as utilized in the above described embodiments.
  • FIG 11 sets forth a section view of a still further alternate embodiment of the present invention peristalsis artificial heart generally referenced by numeral 160.
  • Artificial heart 160 combines the structures of artificial heart 10, shown in Figure 3, and artificial heart 150, shown in Figure 10, to produce a peristalsis pumping action which subjects the magnetic elastomeric element to simultaneous’’push and pull" forces. These simultaneous forces cooperate to provide the localized constricting seal which is moved across the magnetic ring array during the peristalsis pumping action.
  • artificial heart 160 utilizes radial field generator 50 in the above described manner in which multiplex controller circuit 60 is operative upon magnetic rings 56 to draw a portion of magnetic elastomeric element 161 and form a localized constriction 162. Simultaneously, multiplex controller circuit 60 activates the appropriate magnetic rings 151 to provide a repelling magnetic force upon localized constriction 162 and thereby enhances the force applied to localized constricting seal 163. In accordance with the peristalsis pumping action described above, the respective magnets within magnetic rings 151 and 56 are sequentially activated to move localized constriction 162 and localized constricting seal 163 in the direction indicated by arrow 58.
  • FIG 12 sets forth a still further alternate embodiment of the present invention peristalsis artificial heart generally referenced by numeral 170.
  • Peristalsis artificial heart 170 is substantially identical to peristalsis artificial heart 10 set forth above in Figure 3 with the difference being found in the use of a continuous element design to fabricate a blood flow path contained within a single continuous unit. Accordingly, artificial heart 170 includes an input coupling 171 and an end 172 together with an end 174 and an output coupling 175.
  • a magnetic elastomeric element 173 is continuous with and extends between ends 172 and 174.
  • the entire blood path of peristalsis artificial heart 170 which comprises input coupling 171 , end 172, magnetic elastomeric element 173, end 174 and output coupling 175 is formed as a single continuous blood flow element.
  • a housing 176 supports this continuous blood low element and a radial field generator 50 is supported within the interior thereof.
  • FIG. 13 sets forth a still further alternate embodiment of the present invention peristalsis artificial heart generally referenced by numeral 180.
  • artificial heart 180 is a "curved" embodiment of artificial heart 10 which, apart from the curved structure, provides the same basic embodiment as artificial heart 10.
  • artificial heart 180 includes an input coupling 181 and an output coupling 182.
  • a curved containment tube 184 extends between input coupling 181 and output coupling 182 to complete the enclosure of artificial heart 180.
  • a curved magnetic elastomeric element 185 is contained within containment tube 184.
  • a curved radial field generator 183 includes a curved mandrel 187 supporting a plurality of magnetic rings 186. Radial field generator 183 is supported within the interior of artificial heart 180.
  • Multiplex controller circuit 60 is supported within curved mandrel 187,
  • FIG 14 sets forth a section view of a still further alternate embodiment of the present invention which provides a supplemental blood pump for assisting circulation generally referenced by numeral 190.
  • Supplemental blood pump 190 fills many of the functions of a ventricular assist device as well as other functions and advantages not available in the prior art.
  • Supplemental blood pump 190 may be imp lanted into a portion of the recipient's circulatory system such as an aorta 189.
  • Supplemental blood pump 190 includes a peristalsis pump described above in an "miniaturized" embodiment.
  • the structure and operation of supplemental blood pump 190 is substantially identical to the structure and operation of artificial heart 10 set forth above ih Figure 3 with the exception of its smaller size and its accommodation of implant within the recipient's blood vessel.
  • Supplemental blood pump 190 includes a radial field generator 191 operative upon a magnetic elastomeric element 192 in the identical manner as set forth above.
  • Supplemental blood pump 190 further includes a pair of soft resilient O-rings 193 and 194 which Support the body of supplemental blood pump 190 within the interior of aorta 189.
  • Supplemental blood pump 190 further inc ludes a pl urality of attachments 195 and 196 at opposite ends there of which are similar to the attachments utilized in conventional blood vessel stents.
  • supplemental blood pump 190 operates to further pump the flowing blood by the above described peristalsis pumping action to enhance blood flow.
  • supplemental blood pump 190* in addition to the blood pumping action provided by supplemental blood pump 190* it also is able to function as a valve providing an open free-flowing configuration or a closed configuration. While this secondary use of supplemental blood pump 190 functions quite well, the present invention may also be configured to provide a single purpose aortic valve by small modifications to supplemental blood pump 190 such as aortic valve 200 shown in Figures 15A and 15B below.
  • Figures 15A and 15B set forth section views of a still further alternate embodiment of the present invention peristalsis artificial heart providing a blood flow valve device housed within a blood vessel illustrating respective open and closed valve configurations.
  • Figure 15A sets forth an aortic valve constructed in accordance with the present invention in an open configuration while Figure 15B sets forth the same aortic valve in a closed configuration. It will be apparent to those skilled in the art by comparison of Figures 14 and 15A and 15B that the valve structure of Figures 15A and 15B is substantially identical to supplemental blood pump 190 in Figure 14 with the difference being found in a reduced number of magnetic rings.
  • Figure 15A sets forth a section view of a still further alternate embodiment of the present invention which provides an aortic valve generally referenced by numeral 200.
  • Aortic valve 200 may be implanted into a portion of the recipient's circulatory system such as an aorta 189.
  • Aortic valve 200 includes a three element peristalsis device as described above in an "miniaturized" embodiment.
  • the structure and operation of aortic valve 200 is substantially similar to the structure and operation of supplemental blood pump 190 set forth above in Figure 14 with the exception of its reduced number of magnetic rings.
  • aortic valve 200 includes a radial field generator 201 operative upon a magnetic elastomeric element 202 in the identical manner as set forth above.
  • Aortic valve 200 further includes a pair of soft resilient O-rings 203 and 204 which support the body of aortic valve 200 within the interior of aorta 189.
  • Aortic valve 200 further includes a plurality of attachments 205 and 206 at opposite ends thereof which are similar to the attachments utilized in
  • aortic valve 200 In operation, with blood flowing in the direction indicated by arrow 197 within aorta 189, aortic valve 200 operates to blood flow m the directions Indicated by arrows 197 and 198 when aortic valve 200 is in the open configuration of Figure 15 A. Conversely, aortic valve 200 operates to prevent blood flow when elastomeric element 202 is constricted in the manner shown in Figure 15B. Accordingly, as radial field generator 201 is stimulated by heart the signals created within the recipient's heart, aortic valve 200 is operated between open and closed configuration's to perform the heart valve function for the recipient.
  • Figure 16 sets forth a front view of an illustrative magnetic ring, generally referenced by numeral 210 that utilizes a coil orientation that is the reverse of the illustrative magnetic ring shown in Figure 5.
  • Magnetic ring 210 includes a metal desk 211 formed of a magnetic metal such as iron, steel or the like and defining surfaces 215 and 216 (surface 216 not seen).
  • disk 210 is a metal desk 211 formed of a magnetic metal such as iron, steel or the like and defining surfaces 215 and 216 (surface 216 not seen).
  • disks such as iron, steel or the like
  • Magnetic ring 210 further includes a plurality of slots 212 which extend radially out from disk 21 1 and which are equally spaced around the exterior of disk 21 1. The presence of slots
  • Magnetic ring 210 forms a plurality of outwardly extending core elements 213 radially oriented and equally spaced about disk 211.
  • Magnetic ring 210 further includes a plurality of conductive windings 214 each of which is wound about a core element 213.
  • windings 214 are interconnected by a plurality of connecting wires (not shown) which are utilized in coupling windings 214 of magnetic ring 210 to a source of electric current through multiplex controller circuit 60 (seen in Figure 3).

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Cardiology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Mechanical Engineering (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Physics & Mathematics (AREA)
  • Electromagnetism (AREA)
  • External Artificial Organs (AREA)
  • Prostheses (AREA)

Abstract

Selon l'invention, un réseau empilé d'électroaimants est excité pour produire une constriction localisée d'un élément élastomère magnétique qui renferme un passage de flux sanguin. La constriction localisée crée un joint d'étanchéité localisé du passage de flux sanguin au niveau du point de constriction. Le mouvement de cette constriction localisée du passage de flux sanguin est obtenu par mise sous tension séquentielle des électroaimants à travers le réseau de bagues magnétiques d'une extrémité à l'autre. Ceci, à son tour, "pousse" une quantité de sang au sein du passage de flux sanguin en avant de celui-ci, ce qui permet d'obtenir une action de pompage péristaltique.
PCT/US2019/039634 2018-06-27 2019-06-27 Dispositif artificiel péristaltique d'assistance cardiaque et ventriculaire Ceased WO2020006324A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US201862690815P 2018-06-27 2018-06-27
US62/690,815 2018-06-27

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN112915310A (zh) * 2021-01-26 2021-06-08 浙江清华柔性电子技术研究院 体内植入式蠕动泵、蠕动泵控制器及体液转运系统

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4702675A (en) * 1984-08-07 1987-10-27 Hospal A.G. Peristaltic pump provided with a pressure measurement device
US5286176A (en) * 1993-05-06 1994-02-15 The United States Of America As Represented By The Secretary Of The Navy Electromagnetic pump
US20090053084A1 (en) * 2007-08-21 2009-02-26 Klein Jeffrey A Roller pump and peristaltic tubing with atrium
US20120275929A1 (en) * 2011-04-27 2012-11-01 Aptina Imaging Corporation Ferrofluid control and sample collection for microfluidic application
US20160045654A1 (en) * 2014-08-14 2016-02-18 Medibotics Llc Implanted Extracardiac Device for Circulatory Assistance
US20160250401A1 (en) * 2013-11-07 2016-09-01 Eth Zurich Peristaltic pump and pumping method, in particular for use as implant

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4702675A (en) * 1984-08-07 1987-10-27 Hospal A.G. Peristaltic pump provided with a pressure measurement device
US5286176A (en) * 1993-05-06 1994-02-15 The United States Of America As Represented By The Secretary Of The Navy Electromagnetic pump
US20090053084A1 (en) * 2007-08-21 2009-02-26 Klein Jeffrey A Roller pump and peristaltic tubing with atrium
US20120275929A1 (en) * 2011-04-27 2012-11-01 Aptina Imaging Corporation Ferrofluid control and sample collection for microfluidic application
US20160250401A1 (en) * 2013-11-07 2016-09-01 Eth Zurich Peristaltic pump and pumping method, in particular for use as implant
US20160045654A1 (en) * 2014-08-14 2016-02-18 Medibotics Llc Implanted Extracardiac Device for Circulatory Assistance

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN112915310A (zh) * 2021-01-26 2021-06-08 浙江清华柔性电子技术研究院 体内植入式蠕动泵、蠕动泵控制器及体液转运系统

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