CA2026693A1 - Helifoil pump - Google Patents
Helifoil pumpInfo
- Publication number
- CA2026693A1 CA2026693A1 CA 2026693 CA2026693A CA2026693A1 CA 2026693 A1 CA2026693 A1 CA 2026693A1 CA 2026693 CA2026693 CA 2026693 CA 2026693 A CA2026693 A CA 2026693A CA 2026693 A1 CA2026693 A1 CA 2026693A1
- Authority
- CA
- Canada
- Prior art keywords
- pump
- impeller
- heart
- housing
- blood
- 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.)
- Abandoned
Links
Landscapes
- External Artificial Organs (AREA)
Abstract
ABSTRACT OF THE DISCLOSURE
A temporary circulatory assist pump is disclosed for implantation in the heart of a patient through the femoral artery. The pump is driven by a flexible drive shaft extending through a catheter and being connected to a power source outside the body of the patient. The pump utilizes a helical-shaped foil impeller to pump blood at a rate of approximately three to four liters per minute through the circulatory system of the patient.
A temporary circulatory assist pump is disclosed for implantation in the heart of a patient through the femoral artery. The pump is driven by a flexible drive shaft extending through a catheter and being connected to a power source outside the body of the patient. The pump utilizes a helical-shaped foil impeller to pump blood at a rate of approximately three to four liters per minute through the circulatory system of the patient.
Description
2026~3 ATTOR~lE;Y DOCXE;T NO. 9155 2 OMBS t 9155PA/DR4 / O O 9 ~:LS~rOI~ P~lMP
~c~.r,3~)~n nF T~: DTS('T.n!;~RF~
This invention relates to blood pumps, particularly to a temporary circulatory assist pump adapted for insertion into the vascular system of a patient to provide temporary circulatory assistance for a dys~inetic left or right ventricle of the heart.
Death and disability from heart disease are most commonly due to the pumping inadequacy of an infarcted left or right ventricle. The heart of a patient suffering from this condition functions in many other respects but does not provide sufficient blood flow to keep the patient alive. Typically, a patient suffering from this condition would require major surgery to maintain the heart and provide suffic~ent blood flow for the patient.
Another area where temporary circulatory assistance may be required is in allograft cardiac replacement or heart transplants. Although one year survivals after a heart transplant now approach 80%, a great many patients die waiting for a transplant, as do many of the 20% who might be saved by circulatory assistance while immunosuppressive agents are combat~ng the body's natural rejection response of a transplanted heart. There is a great need for an effective circulatory assist pump for maintaining the life of a patient until the transplant can be accomplished and the allograft is stabilized. As the average life expectancy of the U.S. population continues to increase, coronary artery disease and chronic congestive heart failure can be expected to significantly increase the utilization of mechanical circulatory assistance. A realistic estimate of the number of potential candidates for mechanical circulatory assistance would be approximately 300,000 patients each year in 202~6~
the United States. This number will grow at a rate of 6% per year until the population of ~baby boomers" peaks around the year 2020.
~ ethods and apparatus exist ln the prlor art for circulatory ass$stance of a heart. In U.S. Patent No. 4,625,712 a hlgh capacity ~ntravascular blood pump ~ disclosed. The pump ln inserted into the heart through the femoral artery and driven via a flexible cable from an external power source. The drive cable is contained within a catheter attached to the pump. The pump is rotated in the range of 10,000 - 20,000 rpm to produce blood flow on the order of 4 liters per minute.
U.S. Patent No. 3,505,987 discloses a counterpulsation system for aiding coronary circulation. The system includes an expandable impeller located within the aorta of a patient. The impeller is expanded and contracted while simultaneously being reciprocated within the aorta and synchronized with the pumping activity of the heart for reducing aortic pressure during systole and increasing aortic pressure during diastole.
U.S. Patent No. 3,567,069 discloses an implantable jet pump for replacing or assisting the right heart. The jet pump comprlses an elongated tubular structure including an upstream driving nozzle from which a driving flow of arterial blood under pressure is ejected into a suction nozzle creating its own reduced pressure to cause venous blood to be sucked into and admlxed with the driving flow for distribution to the pulmonary circulation system. The jet pump may be powered by blood pumped from the left heart or an artificial replacement for the left heart.
U.S. Patent No. 4,051,840 discloses an aortic patch which may be surgically implanted in the thoracic aorta. The aortic patch is systematically inflated and deflated to generate pressure wave~ in the blood stream. The pressure waves assist the heart by augmenting the circulation of the blood to the body.
~2i6~93 Generally, the methods available for circulatory assistance of the heart require major surgery for the implantation of the de~ice which presents a great risk to the survival of the pat~ent. The device disclosed in U.S. Patent No. 4,6~5,712 may be introduced into the heart through the illofemoral artery thus avoid~ng major surgery and reducing the riQ~ to the patient. However, adequate blood flow requires that the pump and drive shaft be rotated at extremely high rpm through the bends and sharp curves of the iliofemoral and aortic arteries and therefore, extreme care must be taken to avoid creation of hot spots in the arteries.
Another disadvantage associated with high rpm blood pumps is the high ris~ of damaging a substantial percentage of the blood cells of the blood. Damaged blood cells are expelled by the body and new blood cells must be generated to replace them. This may create additional strain on the system of a patient who is already ~n critical condition. The prior art has thus been unable to provide an easily implanted low risk temporary circulatory assist pump capable of providing sufficient blood flow to assist a heart so that the heart ~ay heal itself or keep the patient alive while waiting for a transplant to become available.
~JMM~RY ~ ~ TUVF:N'rr~ N
- The present invention is directed to a miniature temporary circulatory assist pump adapted to be inserted in the heart of the patient for circulatory assistance. The pump in a preferred embodiment is introduced into the left ventricle of the heart by a catheter passed through the arterial system of the patient. The pump utilizes a helical-shaped foil impeller housed within a cylindrical housing to deliver large volumes of blood at relat$vely low rpm with$n a nominal physicological pressure.
2~2~3 DF!TATT.F:l) nF..C~,~TTCN ~F THF'. DRAWTl`lGS
So that the manner in which the above recited features, advantages and objects of the present invention are attained and can be underQtood in detail, more particular descriptlon of the invention, briefly summarized above, may be had by reference to the embodiments thereof which are illustrated in the appended drawings.
Xt is to be noted, however, that the appended drawings illustrate only typical embodiments of this invention and are therefore not to be considered limiting of its scope, for the invention may admit to other equally effective embodiments.
Fig. 1 is an illustrative view of a section of a human heart depicting the preferred position of the pump of the invention in the left ventricle of the heart;
Fig. 2 is a schematic view illustrating the insertion of the pump of the invention through the femoral artery of a patient;
Fig. 3 is a partial sectional view of the pump of the invention;
Fig. 4 is a sectional view of the pump o~ the invention taken along line 4-4 of Fig. 3;;
Fig. 5 is a sectional view of the pump of the invention taken along line 5-5 of Fig. 3;
Fig. 6 is an illustrative view of of the helical-shaped foil impeller of the invention depicted in a two dimensional plane; and Fig. 7 is a sectional view of the pump of the invention taken along lines 7-7 of Fig. 3.
i nF~T~T.F.n n~ t`RTPTTON ~F' T~ PREF~!RRl;~n F.MROnTMF'.NT ;
Referring first to Figs. 1 and 2 of the drawings, the blood pump of the invention is shown inserted in the left ventricle 10 of the heart 12. The blood pump is generally identified by the reference numeral 14 and is carried at the 2~2~3 forward end of a catheter 16. Acces-~ to the heart 12 is provided in the preferred embodiment through the femoral artery 18. This is the preferred insertion point, however, it is understood that the heart 12 may be accessed through other arterie~ or other su~gical means. In the prererred embodiment, the blood pump 14 is located in the left ventricle 10. However, in some circumQtances it may be desirable to locate the blood pump 14 in the right ventricle 20. Access to the right ventricle 20 may be provided through the pulmonary artery 22. In operation, the intake end of the blood pump 14 shown in Fig. 1 is located within the left ventricle 10. The outlet or discharge end of the blood pump 14 is located in the aorta 24. The blood pump 14 thus extends partially into the left ventricle 10 through the heart valve 26. Blood is pumped through the blood pump 14 from the left ventricle 10 in the direction of the arrows 28 into the aorta 24.
Referring now to Fig. 3, the pump 14 is shown in greater detail. The pump 14 is driven by a flexible drive shaft 30 which extends through the catheter 16. The drive shaft 30 is driven by a motor 31 located outside the patient's body, as best shown ~n Fig. 2. The pump 14 is secured to the distal end of the catheter 16. The pump 14 and catheter 16 are guided through the femoral artery to the left ventricle 10. When the left ventricle 10 is reached, the pump 14 is positioned in the left ~entricle 10 of the heart. Ut~lizing known insertion techniques, the pump 14 is positioned so that the intake end 32 extends through the heart valve 26 into the left ventricle 10. The discharge end 34 of the pump 14 is positioned outside the left ventricle 10 so that pumped blood is discharged into the aorta 24 as shown in Fig. 1.
In the embodiment of the invention shown in Fig. 3, the pump 14 comprises a substantially cylindrical elongate housing 36. The intake end 32 of the housing 36 is blunted so that it may be easily inserted into the left ventricle 10 past the heart valve Z6 without damaging the heart valve or any of the heart tissue. The inta~e end 32 is open so that blood collected in the 2~26~
left ventricle 10 may flow freely into the pump 14. Hou~ed within the housing 36 is a helical-shaped foil impeller 38. The impeller 38 is connected to the drive ~haft 30. The drlve shaft 30 i3 centrally po~$tloned within the discharge end 34 of the housing 36 by a shaft stabilizer 40.
In the preferred embodiment as shown in Fig. 1, the pump 14 ix positioned in the left ventricle 10 of the heart 12 and blood from the left ventricle 10 is pumped into the aorta 24 upon rotation of the lmpeller 38. The impeller 38 functions in much the same fashion as an airfoil moving through a liquid medium. Blasius' first equation of fluid forces on a body in motion describes forces on a submerged body. The forces may be resolved into components in directions perpendicular to the motion (Y-axis) and parallel to the motion (X-axis). These forces are known as "lift" and "drag" respectively. In fluid mechanics, lift and drag are equal to the component of thrust.
~otation of the helical-shaped foil impeller 38 within the cylindrical housing 36 produces characteristics similar to the lift and drag forces produced by an airflow. That is, both high and low pressure forces are produced on either side of the rotating helical impeller 38 within the cylinder 36 which produces a thrust force to energize fluid motion within the cylinder 36.
Referring now to Fig. 6, impeller 38 is shown ~n a two dimensional plane. It will be observed that the profile of the impeller 38 is similar to that of an airfoil and includes a forward or leading end 42 and a trailing end 44. ~he impeller 38 tapers from th~ leading end 42 to the trailing end 44. As the impeller 38 is rotated, high and low pressure forces are created on either æide of the rotating impeller. The high pressure side is defined by the surface 46 and the low pressure side is defined by the surface 48. The cord line 49 defines the angle of attack of the impeller 38 which is optimized to provide maximum flow rate at the physiological pressure level.
2~2~93 Referring now to Fig. 3, it will be observed that the impeller 38 is wrapped or twisted to form a helical profile. The forward end of the lmpeller 38 as best shown in Fig. 5 presents a leading edge 50 which extends across the housing 36. From the leadlng edge 50, the impeller 38 defines a continuous contour to the tralllng end 44 a~ shown in Fig. 4. The contour deflnes a continuous rotat~ng passage for transform~ng the blood flow from a simple mass displacement at the inlet 32 to transformational blood flow producing a thrust and a streamline shape at the discharge end 34 of the pump 14. Tha transformational flow may be calculated and graphically described utilizing the Joukowsky transformation. Thus, the Joukowsky transformation may be used to calculate the thrust generated by the rotational motion of the impeller 38 within the housing 36. The rotational motion of the impeller 38 creates a thrust force which draws blood into the cylindrical housing 36 and discharges the blood through apertures 52 extending through the shaft stabilizer 40 and through ports in the discharge end 34 i~to the aorta 24 for circulation through the patient's vascular system. ~he trailing end 44 of the lmpeller 38 is enlarged slightly at the central portion thereof for connect~on to the drive shaft 30. ~he enlarged portion 39 however tapers outwardly to the trailing end 44 of the impeller 38 such that it does not interfere with the blood flow to the discharge end 34 of the housing 36.
The helical-shaped foil prof~le of the impeller 38 is designed to maximize blood flow through the housing 36 while minim~zing the potential damage to blood cells. The impeller 38 is rotated in the range of 6,000 to 10,000 rpm to produce a blood flow of approximately 3 to 4 liters per minute. Turbulence however is minimized by the continuous contour of the flow passage defined by the impeller 38. The thrust generated by the high pressure side of the impeller 38 draws the blood through the pump 14 while minimizing the turbulence in the blood flow. The impeller 38 cooperates with the cylindrical housing 36 to form a continuous, smooth, rotating passage to transform the blood flow 2 0 ~ 3 from a simple mass displacement at the inlet end 32 of the pump 14 to a transformational flow at the trailing end 44 of the $mpeller 38. In this manner, trauma to the blood cells is minimized, yet ~ufficient blood flow is developed to sustain the patient.
Wh~le the foregoing i~ directed to the preferred embodl~ent of the present lnvention, other and further embodiments of the invention may be devised without departing from the ba3ic scope thereof, and the scope thereof is determined by the claims which follow.
W~T lS t`T.ATMl;:n TS-
~c~.r,3~)~n nF T~: DTS('T.n!;~RF~
This invention relates to blood pumps, particularly to a temporary circulatory assist pump adapted for insertion into the vascular system of a patient to provide temporary circulatory assistance for a dys~inetic left or right ventricle of the heart.
Death and disability from heart disease are most commonly due to the pumping inadequacy of an infarcted left or right ventricle. The heart of a patient suffering from this condition functions in many other respects but does not provide sufficient blood flow to keep the patient alive. Typically, a patient suffering from this condition would require major surgery to maintain the heart and provide suffic~ent blood flow for the patient.
Another area where temporary circulatory assistance may be required is in allograft cardiac replacement or heart transplants. Although one year survivals after a heart transplant now approach 80%, a great many patients die waiting for a transplant, as do many of the 20% who might be saved by circulatory assistance while immunosuppressive agents are combat~ng the body's natural rejection response of a transplanted heart. There is a great need for an effective circulatory assist pump for maintaining the life of a patient until the transplant can be accomplished and the allograft is stabilized. As the average life expectancy of the U.S. population continues to increase, coronary artery disease and chronic congestive heart failure can be expected to significantly increase the utilization of mechanical circulatory assistance. A realistic estimate of the number of potential candidates for mechanical circulatory assistance would be approximately 300,000 patients each year in 202~6~
the United States. This number will grow at a rate of 6% per year until the population of ~baby boomers" peaks around the year 2020.
~ ethods and apparatus exist ln the prlor art for circulatory ass$stance of a heart. In U.S. Patent No. 4,625,712 a hlgh capacity ~ntravascular blood pump ~ disclosed. The pump ln inserted into the heart through the femoral artery and driven via a flexible cable from an external power source. The drive cable is contained within a catheter attached to the pump. The pump is rotated in the range of 10,000 - 20,000 rpm to produce blood flow on the order of 4 liters per minute.
U.S. Patent No. 3,505,987 discloses a counterpulsation system for aiding coronary circulation. The system includes an expandable impeller located within the aorta of a patient. The impeller is expanded and contracted while simultaneously being reciprocated within the aorta and synchronized with the pumping activity of the heart for reducing aortic pressure during systole and increasing aortic pressure during diastole.
U.S. Patent No. 3,567,069 discloses an implantable jet pump for replacing or assisting the right heart. The jet pump comprlses an elongated tubular structure including an upstream driving nozzle from which a driving flow of arterial blood under pressure is ejected into a suction nozzle creating its own reduced pressure to cause venous blood to be sucked into and admlxed with the driving flow for distribution to the pulmonary circulation system. The jet pump may be powered by blood pumped from the left heart or an artificial replacement for the left heart.
U.S. Patent No. 4,051,840 discloses an aortic patch which may be surgically implanted in the thoracic aorta. The aortic patch is systematically inflated and deflated to generate pressure wave~ in the blood stream. The pressure waves assist the heart by augmenting the circulation of the blood to the body.
~2i6~93 Generally, the methods available for circulatory assistance of the heart require major surgery for the implantation of the de~ice which presents a great risk to the survival of the pat~ent. The device disclosed in U.S. Patent No. 4,6~5,712 may be introduced into the heart through the illofemoral artery thus avoid~ng major surgery and reducing the riQ~ to the patient. However, adequate blood flow requires that the pump and drive shaft be rotated at extremely high rpm through the bends and sharp curves of the iliofemoral and aortic arteries and therefore, extreme care must be taken to avoid creation of hot spots in the arteries.
Another disadvantage associated with high rpm blood pumps is the high ris~ of damaging a substantial percentage of the blood cells of the blood. Damaged blood cells are expelled by the body and new blood cells must be generated to replace them. This may create additional strain on the system of a patient who is already ~n critical condition. The prior art has thus been unable to provide an easily implanted low risk temporary circulatory assist pump capable of providing sufficient blood flow to assist a heart so that the heart ~ay heal itself or keep the patient alive while waiting for a transplant to become available.
~JMM~RY ~ ~ TUVF:N'rr~ N
- The present invention is directed to a miniature temporary circulatory assist pump adapted to be inserted in the heart of the patient for circulatory assistance. The pump in a preferred embodiment is introduced into the left ventricle of the heart by a catheter passed through the arterial system of the patient. The pump utilizes a helical-shaped foil impeller housed within a cylindrical housing to deliver large volumes of blood at relat$vely low rpm with$n a nominal physicological pressure.
2~2~3 DF!TATT.F:l) nF..C~,~TTCN ~F THF'. DRAWTl`lGS
So that the manner in which the above recited features, advantages and objects of the present invention are attained and can be underQtood in detail, more particular descriptlon of the invention, briefly summarized above, may be had by reference to the embodiments thereof which are illustrated in the appended drawings.
Xt is to be noted, however, that the appended drawings illustrate only typical embodiments of this invention and are therefore not to be considered limiting of its scope, for the invention may admit to other equally effective embodiments.
Fig. 1 is an illustrative view of a section of a human heart depicting the preferred position of the pump of the invention in the left ventricle of the heart;
Fig. 2 is a schematic view illustrating the insertion of the pump of the invention through the femoral artery of a patient;
Fig. 3 is a partial sectional view of the pump of the invention;
Fig. 4 is a sectional view of the pump o~ the invention taken along line 4-4 of Fig. 3;;
Fig. 5 is a sectional view of the pump of the invention taken along line 5-5 of Fig. 3;
Fig. 6 is an illustrative view of of the helical-shaped foil impeller of the invention depicted in a two dimensional plane; and Fig. 7 is a sectional view of the pump of the invention taken along lines 7-7 of Fig. 3.
i nF~T~T.F.n n~ t`RTPTTON ~F' T~ PREF~!RRl;~n F.MROnTMF'.NT ;
Referring first to Figs. 1 and 2 of the drawings, the blood pump of the invention is shown inserted in the left ventricle 10 of the heart 12. The blood pump is generally identified by the reference numeral 14 and is carried at the 2~2~3 forward end of a catheter 16. Acces-~ to the heart 12 is provided in the preferred embodiment through the femoral artery 18. This is the preferred insertion point, however, it is understood that the heart 12 may be accessed through other arterie~ or other su~gical means. In the prererred embodiment, the blood pump 14 is located in the left ventricle 10. However, in some circumQtances it may be desirable to locate the blood pump 14 in the right ventricle 20. Access to the right ventricle 20 may be provided through the pulmonary artery 22. In operation, the intake end of the blood pump 14 shown in Fig. 1 is located within the left ventricle 10. The outlet or discharge end of the blood pump 14 is located in the aorta 24. The blood pump 14 thus extends partially into the left ventricle 10 through the heart valve 26. Blood is pumped through the blood pump 14 from the left ventricle 10 in the direction of the arrows 28 into the aorta 24.
Referring now to Fig. 3, the pump 14 is shown in greater detail. The pump 14 is driven by a flexible drive shaft 30 which extends through the catheter 16. The drive shaft 30 is driven by a motor 31 located outside the patient's body, as best shown ~n Fig. 2. The pump 14 is secured to the distal end of the catheter 16. The pump 14 and catheter 16 are guided through the femoral artery to the left ventricle 10. When the left ventricle 10 is reached, the pump 14 is positioned in the left ~entricle 10 of the heart. Ut~lizing known insertion techniques, the pump 14 is positioned so that the intake end 32 extends through the heart valve 26 into the left ventricle 10. The discharge end 34 of the pump 14 is positioned outside the left ventricle 10 so that pumped blood is discharged into the aorta 24 as shown in Fig. 1.
In the embodiment of the invention shown in Fig. 3, the pump 14 comprises a substantially cylindrical elongate housing 36. The intake end 32 of the housing 36 is blunted so that it may be easily inserted into the left ventricle 10 past the heart valve Z6 without damaging the heart valve or any of the heart tissue. The inta~e end 32 is open so that blood collected in the 2~26~
left ventricle 10 may flow freely into the pump 14. Hou~ed within the housing 36 is a helical-shaped foil impeller 38. The impeller 38 is connected to the drive ~haft 30. The drlve shaft 30 i3 centrally po~$tloned within the discharge end 34 of the housing 36 by a shaft stabilizer 40.
In the preferred embodiment as shown in Fig. 1, the pump 14 ix positioned in the left ventricle 10 of the heart 12 and blood from the left ventricle 10 is pumped into the aorta 24 upon rotation of the lmpeller 38. The impeller 38 functions in much the same fashion as an airfoil moving through a liquid medium. Blasius' first equation of fluid forces on a body in motion describes forces on a submerged body. The forces may be resolved into components in directions perpendicular to the motion (Y-axis) and parallel to the motion (X-axis). These forces are known as "lift" and "drag" respectively. In fluid mechanics, lift and drag are equal to the component of thrust.
~otation of the helical-shaped foil impeller 38 within the cylindrical housing 36 produces characteristics similar to the lift and drag forces produced by an airflow. That is, both high and low pressure forces are produced on either side of the rotating helical impeller 38 within the cylinder 36 which produces a thrust force to energize fluid motion within the cylinder 36.
Referring now to Fig. 6, impeller 38 is shown ~n a two dimensional plane. It will be observed that the profile of the impeller 38 is similar to that of an airfoil and includes a forward or leading end 42 and a trailing end 44. ~he impeller 38 tapers from th~ leading end 42 to the trailing end 44. As the impeller 38 is rotated, high and low pressure forces are created on either æide of the rotating impeller. The high pressure side is defined by the surface 46 and the low pressure side is defined by the surface 48. The cord line 49 defines the angle of attack of the impeller 38 which is optimized to provide maximum flow rate at the physiological pressure level.
2~2~93 Referring now to Fig. 3, it will be observed that the impeller 38 is wrapped or twisted to form a helical profile. The forward end of the lmpeller 38 as best shown in Fig. 5 presents a leading edge 50 which extends across the housing 36. From the leadlng edge 50, the impeller 38 defines a continuous contour to the tralllng end 44 a~ shown in Fig. 4. The contour deflnes a continuous rotat~ng passage for transform~ng the blood flow from a simple mass displacement at the inlet 32 to transformational blood flow producing a thrust and a streamline shape at the discharge end 34 of the pump 14. Tha transformational flow may be calculated and graphically described utilizing the Joukowsky transformation. Thus, the Joukowsky transformation may be used to calculate the thrust generated by the rotational motion of the impeller 38 within the housing 36. The rotational motion of the impeller 38 creates a thrust force which draws blood into the cylindrical housing 36 and discharges the blood through apertures 52 extending through the shaft stabilizer 40 and through ports in the discharge end 34 i~to the aorta 24 for circulation through the patient's vascular system. ~he trailing end 44 of the lmpeller 38 is enlarged slightly at the central portion thereof for connect~on to the drive shaft 30. ~he enlarged portion 39 however tapers outwardly to the trailing end 44 of the impeller 38 such that it does not interfere with the blood flow to the discharge end 34 of the housing 36.
The helical-shaped foil prof~le of the impeller 38 is designed to maximize blood flow through the housing 36 while minim~zing the potential damage to blood cells. The impeller 38 is rotated in the range of 6,000 to 10,000 rpm to produce a blood flow of approximately 3 to 4 liters per minute. Turbulence however is minimized by the continuous contour of the flow passage defined by the impeller 38. The thrust generated by the high pressure side of the impeller 38 draws the blood through the pump 14 while minimizing the turbulence in the blood flow. The impeller 38 cooperates with the cylindrical housing 36 to form a continuous, smooth, rotating passage to transform the blood flow 2 0 ~ 3 from a simple mass displacement at the inlet end 32 of the pump 14 to a transformational flow at the trailing end 44 of the $mpeller 38. In this manner, trauma to the blood cells is minimized, yet ~ufficient blood flow is developed to sustain the patient.
Wh~le the foregoing i~ directed to the preferred embodl~ent of the present lnvention, other and further embodiments of the invention may be devised without departing from the ba3ic scope thereof, and the scope thereof is determined by the claims which follow.
W~T lS t`T.ATMl;:n TS-
Claims (7)
1. A temporary circulatory assist pump, comprising:
(a) an elongate, cylindrical housing having at least one intake port and at least one discharge port, said housing being sized for passage through a human blood vessel and insertion into a heart;
(b) pump means within said housing for assisting the heart of a patient to pump blood, said pump means including impeller means for pumping blood therethrough;
(c) wherein said housing includes discharge means for discharging blood into the vascular system of the patient;
(d) extravascular power means connected to said pump means for driving said impeller means; and (e) drive shaft means connecting said pump means to said power means.
(a) an elongate, cylindrical housing having at least one intake port and at least one discharge port, said housing being sized for passage through a human blood vessel and insertion into a heart;
(b) pump means within said housing for assisting the heart of a patient to pump blood, said pump means including impeller means for pumping blood therethrough;
(c) wherein said housing includes discharge means for discharging blood into the vascular system of the patient;
(d) extravascular power means connected to said pump means for driving said impeller means; and (e) drive shaft means connecting said pump means to said power means.
2. The pump of Claim 1 wherein said impeller means comprises a helical-shaped foil impeller positioned within said housing and cooperating with said housing to form a continuous rotating fluid passage.
3. The pump of Claim 2 wherein said impeller includes an airfoil profile defining a low and high pressure area upon rotation of said impeller.
4. The pump of Claim 3 including drive shaft stabilizer means for centrally supporting said drive shaft means within said cylindrical housing.
5. The pump of Claim 1 wherein said cylindrical housing carrying said pump means is mounted to the distal end of a catheter and guided to the heart of a patient by said catheter.
6. The pump of Claim 3 wherein said helical-shaped foil impeller defines a profile which tapers from a leading end to a trailing end.
7. The pump of Claim 2 wherein said helical-shaped foil impeller is driven at a rotational speed in the range of 4,000 to 10,000 rpm.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CA 2026693 CA2026693A1 (en) | 1990-10-02 | 1990-10-02 | Helifoil pump |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CA 2026693 CA2026693A1 (en) | 1990-10-02 | 1990-10-02 | Helifoil pump |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2026693A1 true CA2026693A1 (en) | 1992-04-03 |
Family
ID=4146082
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA 2026693 Abandoned CA2026693A1 (en) | 1990-10-02 | 1990-10-02 | Helifoil pump |
Country Status (1)
| Country | Link |
|---|---|
| CA (1) | CA2026693A1 (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US11368081B2 (en) | 2018-01-24 | 2022-06-21 | Kardion Gmbh | Magnetic coupling element with a magnetic bearing function |
| US11754075B2 (en) | 2018-07-10 | 2023-09-12 | Kardion Gmbh | Impeller for an implantable, vascular support system |
| US11944805B2 (en) | 2020-01-31 | 2024-04-02 | Kardion Gmbh | Pump for delivering a fluid and method of manufacturing a pump |
| US12005248B2 (en) | 2018-05-16 | 2024-06-11 | Kardion Gmbh | Rotor bearing system |
-
1990
- 1990-10-02 CA CA 2026693 patent/CA2026693A1/en not_active Abandoned
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US11368081B2 (en) | 2018-01-24 | 2022-06-21 | Kardion Gmbh | Magnetic coupling element with a magnetic bearing function |
| US11804767B2 (en) | 2018-01-24 | 2023-10-31 | Kardion Gmbh | Magnetic coupling element with a magnetic bearing function |
| US12005248B2 (en) | 2018-05-16 | 2024-06-11 | Kardion Gmbh | Rotor bearing system |
| US11754075B2 (en) | 2018-07-10 | 2023-09-12 | Kardion Gmbh | Impeller for an implantable, vascular support system |
| US11944805B2 (en) | 2020-01-31 | 2024-04-02 | Kardion Gmbh | Pump for delivering a fluid and method of manufacturing a pump |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US4969865A (en) | Helifoil pump | |
| US5112292A (en) | Helifoil pump | |
| EP0480101B1 (en) | Heart assist pump | |
| US4080958A (en) | Apparatus for aiding and improving the blood flow in patients | |
| US7229402B2 (en) | Minimally invasive ventricular assist technology and method | |
| US6974436B1 (en) | Integrated pump and cannula system and related methods | |
| CA2367469C (en) | Heart assist system | |
| AU760773B2 (en) | Blood pump using cross-flow principles | |
| US6508787B2 (en) | System for actively supporting the flow of body fluids | |
| EP1066066B1 (en) | Closed chest intra-aortic balloon based ventricular assist device | |
| EP0157871B1 (en) | High-capacity intravascular blood pump utilizing percutaneous access | |
| US6395026B1 (en) | Apparatus and methods for beating heart bypass surgery | |
| US4985014A (en) | Ventricular venting loop | |
| JP3265650B2 (en) | Blood circulation assist device | |
| US20040024285A1 (en) | Blood pump with impeller | |
| EP2833939B1 (en) | Ambulatory lung assist device with implanted blood pump and oxygenator | |
| WO1998014225A3 (en) | Circulatory support system | |
| JP2003520611A (en) | Implantable heart assist device | |
| JPH11514251A (en) | Heart assist system | |
| EP1035880A1 (en) | Heart assist system with cannula pump | |
| JPH04176471A (en) | Circulation auxiliary pump | |
| CA2026693A1 (en) | Helifoil pump | |
| CA2026692A1 (en) | Heart assist pump | |
| JPH04156856A (en) | Pump for circulatory assistance | |
| RU2763416C1 (en) | Device and method for mechanical support of the lymphatic system |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FZDE | Dead |