CN1239209C - Magnetic-driven axial-flow auxiliary pump for heart - Google Patents
Magnetic-driven axial-flow auxiliary pump for heart Download PDFInfo
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- CN1239209C CN1239209C CN 03156564 CN03156564A CN1239209C CN 1239209 C CN1239209 C CN 1239209C CN 03156564 CN03156564 CN 03156564 CN 03156564 A CN03156564 A CN 03156564A CN 1239209 C CN1239209 C CN 1239209C
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Abstract
The present invention discloses a magnetism driven axial flow auxiliary pump for hearts, which is composed of a stator, a rotor and a DC stabilized power supply, wherein the stator is composed of a stator winding and a stator casing; the rotor is composed of a cylindric magnetic body with high energy levels, and a propulsion device; the propulsion device is composed of a rotor inner sleeve, a center shaft, and two sets of single impeller blades which are arranged on the center shaft and mutually form an angle of 180 DEG C to be in integration structure, and a spiral and sealed blood propulsion passage is formed. The rotor is placed in a tapered shaft sleeve of a stator suspension arm through two conic shaft ends of the center shaft; the stator winding can generate a magnetic field through electric current to drive the permanent magnet rotor to drive spiral propulsion blades to rotate at a high speed; blood is driven to flow in one way to assist or completely replace the heat to pump heart; the stator winding is connected with the DC stabilized power supply, and the blood flow quality can be regulated according to requirements. The present invention can assist hearts for a short term or a long term, and is suitable for patients of acute cardiac function failure or cardiopathy in the late stage.
Description
Technical field
The present invention relates to a kind of heart assisting pump.
Background technology
In the research process of nearly half a century of heart-assist device, aspects such as its material, structure, processing technology, function and service life are constantly being improved, are being developed, different driving modes such as pneumatic, electronic, electric hydraulic pressure occurred, the blood flow that is produced is also more near the physiology heart.Heart-assist device is the important means that the critical patient earns a bare living.Be divided into finally and substitute, wait for transplanting and reduce cardiac load, three kinds of modes of promotion functional rehabilitation.
Along with medical science applied continuous development, can not break away from cardiopulmonary bypass unit behind acute heart failure, the operation on heart and wait for that the patient of heart transplantation is more and more, be badly in need of heart assistance short-term transition or keep long period wait heart donor.Therefore, require auxiliary device not only favorable durability will be arranged, minimum blood destructiveness also will have characteristics such as low noise, low power consuming, miniaturization, portability.Axial-flow pump has above-mentioned advantage just, generally is placed on outside the heart, and at left ventricle apex and ascending aorta or descending aorta, right superior pulmonary vein inserts left room and ascending aorta is set up path, aorta is squeezed in left chamber or left room blood, to keep the systemic blood supply.Heart-assist device commonly used has axial-flow pump and centrifugal pump, and axial-flow pump is slighter than centrifugal pump to the destructiveness of blood, and it is little to have a volume, advantage such as easy to carry, therefore, in the research implantable, with the ventricular assist device that axial-flow pump drives, become the hot subject of present research.The application of magnetic suspension theory in axial-flow pump further promoted the research and development of axial-flow pump, and heart-assist device is progressively improved becomes possibility.
Axial-flow pump commonly used at present has the Micro DeBakey type heart chamber auxiliary pump of designs such as (1) DeBakey and Noon, is used to wait for the patient of heart transplantation, clinical existing 5 years experience; (2) the HeartMate II of Nimbus company design; (3) Jarvik 2000 of Jarvik design in clinical practice, has obtained good effect; (4) in zoopery, obtained satisfied progress by the axial-flow pump of the Akamatsu development and design of Japanese Terumo company; (5) design such as Yamazaki is placed on intraventricular axial-flow pump.(6) begin design by Wampler in nineteen eighty-two, be applied to clinical in 1988.With the hemodynamics of improving the cardiogenic shock patient with alleviate left chamber load, promote axial-flow pump-hemopump that cardiac function recovers.Described traditional axial-flow pump can't solve in the blade rotation process, and cutting blood causes the destruction problem to blood and clotting mechanism.
Normally used heart-assist device can cause the infection of various antibacterials even fungus, thrombosis, and the destruction of blood and blood vessel is reduced immunologic function.The prolonged application axial-flow pump carries out the advection perfusion and still has certain dispute, experiment showed, that prolonged application ripple disable blood flow can cause attenuation of aorta structural pipe wall and vasoconstriction function reduction.And the collar of axial-flow pump and the wearing and tearing of blood flow, moving blade all cause the destruction of blood and the formation of thrombosis to the cutting of blood.And the small axial flow pump of application magnetic levitation technology, by the rotor magnetic suspension, the axle with blood flow have the minimum contact the scheme that rotating vane and rotor design for one, can obviously reduce in the rotation the dissection of blood, further reduce the destruction of blade blood and clotting mechanism.
Axial flow blood pump makes much progress the ventricle slave side.As Jarvik 2000 axial-flow pumps; Cleveland Clinic centrifugal pump; Streamliner mixing blood pump.These blood pumps all are the impeller driven blood flows by high speed rotating, and play the auxiliary effect of ventricle.With regard to Jarvik 2000, axle contacts with the close of blood, may produce blood and destroy and thrombosis.Use maglev axle and be the noncontact axle, can produce minimum blood and destroy.Axle is wrapped in a very little space, for the miniaturization of axial-flow pump provides probability.Countershaft the washing away of mobile blood in the axle reduced thrombotic chance.When the magnet rotor high speed rotating, rotor is suspended, produce " virtually zero power (VZP) ", obviously reduce energy expenditure.
Summary of the invention
The purpose of this invention is to provide the magnetic suspension of a kind of application rotor, rotating vane and rotor are the design of one, can obviously reduce in the rotation the dissection of blood, further reduce the axial-flow type heart assisting pump that rotating vane drives blood and the destructive magnetic of clotting mechanism.
The axial-flow type heart assisting pump that a kind of magnetic of the present invention drives, it comprises: stator, rotor and D.C. regulated power supply; The stator of being made up of stator winding and stator case places rotor exterior; Described rotor comprises the magnet and the propulsion plant of tubular high level, its propulsion plant is made up of the one or more screw propulsion blade integrative-structure on cover, central shaft and the central shaft in the rotor, described screw propulsion blade shroud is around in central shaft, its inboard joins with central shaft, and overlapping in the outside and the rotor joins and form a spiral seals close blood propelling passage; Described central shaft two conical axle heads are inserted in the tapered hub of stator cantilever, and to satisfy the needs of rotor suspended state, the two ends of described rotor are respectively the entrance and exit of pump.
The axial-flow type heart assisting pump that aforesaid magnetic drives between stator case and rotor sidewall, has a seal washer that plays the blood buffer action.
The axial-flow type heart assisting pump that aforesaid magnetic drives, its helical blade is formed by two that are mutually 180 °, presses uniform pitch and arranges, and is fixed between the interior cover of central shaft and rotor; The design of its pitch and blade angle is to satisfy the requirement that blood is produced minimized friction resistance and minimum eddy currents.
The axial-flow type heart assisting pump that aforesaid magnetic drives is positioned at stator cover two ends, and the cantilever of the tapered shaft end of fixed center axis is formed by being mutually 180 ° two or three supporting structures of 120 °.
The axial-flow type heart assisting pump that aforesaid magnetic drives, the cylinder-like structure in the rotor is radially bonding by the permanent magnetism of four or eight or ten halves, presses N-S and arranges formation, is arranged as the best with eight equal portions.
The axial-flow type heart assisting pump that aforesaid magnetic drives all is coated with biological coating on the surface of cover, helical blade and central shaft in described rotor.
The axial-flow type heart assisting pump that aforesaid magnetic drives has a D.C. regulated power supply to be connected with described stator winding, regulates rotor speed.
Advantage of the present invention and positive effect are as follows;
1. the invention provides the magnetic suspension of a kind of application rotor, rotating vane and rotor are the design of one, can obviously reduce in the rotation the dissection of blood, further reduce the axial-flow type heart assisting pump that rotating vane drives blood and the destructive magnetic of clotting mechanism.
2. according to the result of study of Most scholars, the blood destruction that produces after auxiliary device implants can make body produce new compensation, and both body can be strengthened hemopoietic function to remedy the haemolysis loss of increase.But this is compensatory certain limit is arranged.It is generally acknowledged: every day haemolysis cause free hemoglobin 10 grams when following both can by physiological system compensatory.Preliminary analysis as a result according to this research is found: the blood destruction when utilizing device of the present invention to assist is less, and free hemoglobin is below the 9.5 gram/skies.
3. the left heart assosting effect to device of the present invention has carried out acute zoopery, to observe the load removal effect of axial-flow pump to natural heart.Laboratory animal is a dog, opens breast behind the general anesthesia.Carry out " end to side " at ascending aorta with artificial blood vessel and coincide, then, the end openings of micro axial flow pump by artificial blood vessel is inserted in the ascending aorta, the opening of axial-flow pump is positioned at the top of nature aortic valve, then the pump housing is fixed.Artificial blood vessel met close the thoracic cavity after closing, body outer driving device is affixed on thoracic wall and starts driving device.The leading indicator of observing is: left ventricle peak systolic pressure (LVPSP), aorta peak systolic pressure (PSAP) is observed above two indexs down in the different velocity of rotation of axial-flow pump (RS) respectively, to determine axial-flow pump influence to the left heart when varying strength is worked.Experimental result has been determined the left heart load removal effect of axial-flow pump.Following table is left ventricle and the aortic pressure value that records.
| RS(rpm) | 0 | 3000 | 6000 | 9000 |
| LVPSP(mmHg) | 145±21 | 107±24 | 74±19 | 28±14 |
| PSAP(mmHg) | 114±17 | 123±12 | 121±15 | 126±18 |
Result in last table shows: along with the rotating speed increase of axial-flow pump, the peak systolic pressure of left ventricle (LVPSP) progressively descends, the peak systolic pressure (LVPSP) of left ventricle drops to 28mmHg when the axial-flow pump rotating speed reaches per minute 9000 commentaries on classics, fully shows the load removal effect of axial-flow pump.The meaning of this experiment is that the intra-arterial micro axial flow pump can have definite left heart load removal effect.
The discovery that this zoopery has needs to pay attention to: this device does not make arterial pressure rise significantly when left ventricular pressure is fully descended, it can be seen from the table: when the axial-flow pump rotating speed is 9000 commentaries on classics/min, the left ventricle peak systolic pressure drops to 28mmHg by normal 145mmHg, fall reaches 117mmHg, and aorta peak systolic pressure (PSAP) only rises to 126mmHg by original 114mmHg, the rising degree is extremely slight, and learning by statistics to handle does not have notable difference.This result does not all have report at home and abroad, and its physiological significance need deeply be inquired into.
Description of drawings
Fig. 1 is a structural representation of the present invention;
Fig. 2 is a stator winding structure sketch map of the present invention;
Fig. 3 is a stator winding structure of the present invention right side diagrammatic sketch;
Fig. 4 is the structural representation of stator case of the present invention and both sides cantilever;
Fig. 5 is the right side diagrammatic sketch of stator case of the present invention and both sides cantilever;
Fig. 6 is a cylindric permanent magnet rotor structure sketch map of the present invention;
Fig. 7 is a cylindric p-m rotor right side view of the present invention;
Fig. 8 is a nested structure sketch map in the rotor of the present invention;
Fig. 9 is a cover right side view in the rotor of the present invention;
Figure 10 is a propulsion plant structural representation of the present invention;
Figure 11 is the right side view of propulsion plant of the present invention;
Figure 12 is the structural representation of central shaft of the present invention.
The specific embodiment
Magnetic of the present invention drives axial flow blood pump, comprising: (1) stator winding be wrapped in the cylinder shape stator shell around; The cylindrical rotor of (2) central, enlarged is positioned at the central authorities of axial-flow pump; (3) p-m rotor is made up of the magnetic material of 8 arranged radiallys.(4) the Double helix vanes fixed is in the inner surface of p-m rotor; (5) central shafts are fixed in whole rotor central authorities; (6) p-m rotor and shell separate with seal washer and blood, form minimal air gap.(7) axle sleeve at central shaft both ends and stator cantilever center cooperates, and forms magnetic suspension rotor.
The specific embodiment of the invention can be referring to Fig. 1 to Figure 12.Fig. 1 is a structural representation of the present invention, and it comprises: stator 1, rotor and three ingredients of D.C. regulated power supply.Wherein the structure of stator can be referring to Fig. 2,3,4,5, and the coil windings that it is arranged by stator case 2 and by the brushless electric machine requirement etc. is partly formed.The concrete structure of rotor can be referring to Fig. 6,7, and it is by the magnet 13 of high level eight equal parts radially, and forms the rotor of a tubular by extremely adjacent the arranging of N-S, can select the N50 magnetic material of Japan for use.The revolution of this device is scalable in 3000-10000 rev/min of scope.Described stator case is placed on outside the rotor, keeps minimum gap between rotor and the stator.The structure of stator case 2 can be referring to Fig. 4,5, and the two ends that are positioned at stator case 2 are cantilever 3, and cantilever 3 is for being mutually 120 ° of structure arranged, and its center is the axle sleeve 14 of a taper.Be positioned at the blood entrance and exit 4,10 of the two ends of tapered hub for this device.Be fixed with in the rotor inboard and overlap 11 in the rotor, its structure can be referring to Fig. 8,9.Interior cover 11 of rotor and central shaft 8 and the Double helix propelling blade 7 common compositions of arranging along central shaft 8 and the incorporate blood propulsion plant of rotor.Described Double helix advances blade 7 to be mutually 180 °, inboardly is connected with central shaft 8, and the outside connects in the rotor overlaps 11, makes propulsion plant and the rotor structure that fuses, the screw propulsion blood channel 6 of a sealing of formation.The structure of this part can be referring to Figure 10,11.All be coated with biological coating on the inner wall surface of the screw propulsion blood channel 6 in the described propulsion plant.As 12 carbon coatings.The both ends 9 of described central shaft 8 are conical, and place in the axle sleeve 14 of cantilever 3, and keep the gap of 1-1.5mm, to satisfy the state that rotor is in suspension.The structure of described central shaft 8 can be referring to Figure 12.In two adjacent sideshakes of rotor 13 and stator case 2, be provided with seal washer 12, this packing ring is a soft material, plays sealing, isolation blood flow.The described central shaft 8 outer axle sleeves 15 that are with.
The propulsion plant of traditional axial flow pump is when high speed rotating, produce local eddy currents, vacuum formation, spray blood flow, blood flow acceleration, the shearing force of rotating vane and the viscous flow of raised surface and blood, the destruction that all can cause blood formed element, free hemoglobin increase obstacle with clotting mechanism.Cause blood coagulation and thrombosis, finally influence the function of pump, harm patient life.
The key issue that magnetic drives the axial-flow pump design is the problem that concerns of air gap and efficient, effectively suspends and angle of rake rotation, and the air gap of liquid must be less relatively, and like this, rotor could obtain enough magnetomotive, promotes the impeller high speed rotating.One of characteristic of the design is minimum air gap, best magnetic effect.We use the material of high magnetic energy level, and cylindrical high-performance magnetic material is 8 parts of five equilibriums (N-S-N-S-N-S-N-S) radially, form the p-m rotor of hollow, rotating vane is fixed in rotor central authorities, rotates synchronously with rotor, and blade is little to the blood dissection, and blood flow area ratio is big, and eddy current is little.Stator winding produces magnetic field by electric current, acts on p-m rotor, produces magnetic suspension, and the resistance of reducing friction produces optimum efficiency.Adopt thick coil windings in the design, can reduce coil heating.In order to make rotor energy stable suspersion, we have designed the rotor center axle, and three supporting cantilever become 120 ° to be fixed on the stator casing, form an axle center, hold the taper spindle nose of armature spindle, satisfy the rotor magnetic suspension, the high efficiency drive blood flow.Helical blade is a twayblade, is mutually 180 ° with central shaft, be fixed on central shaft overcoat and the p-m rotor inwall, has increased the stability that advances blade, reasonably advances blade angle, high efficiency drive blood flow and prevent thrombosis.The rotor part of packing makes simple, the easy row of assembling.
Claims (7)
1. the axial-flow type heart assisting pump that drives of a magnetic, it comprises: stator, rotor and D.C. regulated power supply; It is characterized in that: the stator of being made up of stator winding and stator case places rotor exterior; Described rotor comprises the magnet and the propulsion plant of tubular high level, its propulsion plant is made up of the one or more screw propulsion blade integrative-structure on cover, central shaft and the central shaft in the rotor, described screw propulsion blade shroud is around in central shaft, its inboard joins with central shaft, and overlapping in the outside and the rotor joins and form a spiral seals close blood propelling passage; Described central shaft two conical axle heads are inserted in the tapered hub of stator cantilever, and to satisfy the needs of rotor suspended state, the two ends of described rotor are respectively the entrance and exit of pump.
2. the axial-flow type heart assisting pump that magnetic as claimed in claim 1 drives is characterized in that: between stator case and rotor sidewall, a seal washer that plays the blood buffer action is arranged.
3. the axial-flow type heart assisting pump that magnetic as claimed in claim 1 drives, it is characterized in that: helical blade is formed by two that are mutually 180 °, presses uniform pitch and arranges, and is fixed between the interior cover of central shaft and rotor; The design of its pitch and blade angle is to satisfy the requirement that blood is produced minimized friction resistance and minimum eddy currents.
4. the axial-flow type heart assisting pump that magnetic as claimed in claim 1 drives, it is characterized in that: be positioned at the stator case two ends, the cantilever of the tapered shaft end of fixed center axis is formed by being mutually 180 ° two or three supporting structures of 120 °.
5. the axial-flow type heart assisting pump that magnetic as claimed in claim 1 drives is characterized in that: the cylinder-like structure in the rotor, and radially bonding by the permanent magnetism of four or eight or ten halves, press N-S and arrange formation, be arranged as the best with eight equal portions.
6. the axial-flow type heart assisting pump that magnetic as claimed in claim 1 drives is characterized in that: all be coated with biological coating on the surface of cover, helical blade and central shaft in described rotor.
7. the axial-flow type heart assisting pump that magnetic as claimed in claim 1 drives is characterized in that: have a D.C. regulated power supply to be connected with described stator winding, regulate rotor speed.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 03156564 CN1239209C (en) | 2003-09-09 | 2003-09-09 | Magnetic-driven axial-flow auxiliary pump for heart |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 03156564 CN1239209C (en) | 2003-09-09 | 2003-09-09 | Magnetic-driven axial-flow auxiliary pump for heart |
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| Publication Number | Publication Date |
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| CN1488409A CN1488409A (en) | 2004-04-14 |
| CN1239209C true CN1239209C (en) | 2006-02-01 |
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| CN 03156564 Expired - Fee Related CN1239209C (en) | 2003-09-09 | 2003-09-09 | Magnetic-driven axial-flow auxiliary pump for heart |
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| US11185677B2 (en) | 2017-06-07 | 2021-11-30 | Shifamed Holdings, Llc | Intravascular fluid movement devices, systems, and methods of use |
| US11511103B2 (en) | 2017-11-13 | 2022-11-29 | Shifamed Holdings, Llc | Intravascular fluid movement devices, systems, and methods of use |
| US11654275B2 (en) | 2019-07-22 | 2023-05-23 | Shifamed Holdings, Llc | Intravascular blood pumps with struts and methods of use and manufacture |
| US11724089B2 (en) | 2019-09-25 | 2023-08-15 | Shifamed Holdings, Llc | Intravascular blood pump systems and methods of use and control thereof |
| US11964145B2 (en) | 2019-07-12 | 2024-04-23 | Shifamed Holdings, Llc | Intravascular blood pumps and methods of manufacture and use |
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| CN103821727A (en) * | 2014-02-28 | 2014-05-28 | 浙江创美机电有限公司 | High-speed axial flow pump |
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| CN106620912A (en) * | 2016-12-27 | 2017-05-10 | 吴中区穹窿山德毅新材料技术研究所 | Permanent magnet brushless direct current motor type artificial heart pump |
| CN107456617B (en) * | 2017-08-08 | 2023-11-14 | 长治市久安人工心脏科技开发有限公司 | Implanted axial flow blood pump without rear guide vane |
| CN107834734A (en) * | 2017-11-27 | 2018-03-23 | 苏州惠琪特电子科技有限公司 | A kind of permanent-magnet DC brushless formula motor |
| NL2021401B1 (en) * | 2018-07-27 | 2020-01-31 | Stichting Katholieke Univ | Heart support device with directional flow assist |
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2003
- 2003-09-09 CN CN 03156564 patent/CN1239209C/en not_active Expired - Fee Related
Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US11185677B2 (en) | 2017-06-07 | 2021-11-30 | Shifamed Holdings, Llc | Intravascular fluid movement devices, systems, and methods of use |
| US11717670B2 (en) | 2017-06-07 | 2023-08-08 | Shifamed Holdings, LLP | Intravascular fluid movement devices, systems, and methods of use |
| US11511103B2 (en) | 2017-11-13 | 2022-11-29 | Shifamed Holdings, Llc | Intravascular fluid movement devices, systems, and methods of use |
| US10722631B2 (en) | 2018-02-01 | 2020-07-28 | Shifamed Holdings, Llc | Intravascular blood pumps and methods of use and manufacture |
| US11229784B2 (en) | 2018-02-01 | 2022-01-25 | Shifamed Holdings, Llc | Intravascular blood pumps and methods of use and manufacture |
| US11964145B2 (en) | 2019-07-12 | 2024-04-23 | Shifamed Holdings, Llc | Intravascular blood pumps and methods of manufacture and use |
| US11654275B2 (en) | 2019-07-22 | 2023-05-23 | Shifamed Holdings, Llc | Intravascular blood pumps with struts and methods of use and manufacture |
| US11724089B2 (en) | 2019-09-25 | 2023-08-15 | Shifamed Holdings, Llc | Intravascular blood pump systems and methods of use and control thereof |
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| CN1488409A (en) | 2004-04-14 |
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