CN204972438U - Elasticity haematodocha and pneumatic bellow drive formula artificial heart pump for artificial heart - Google Patents
Elasticity haematodocha and pneumatic bellow drive formula artificial heart pump for artificial heart Download PDFInfo
- Publication number
- CN204972438U CN204972438U CN201520697033.6U CN201520697033U CN204972438U CN 204972438 U CN204972438 U CN 204972438U CN 201520697033 U CN201520697033 U CN 201520697033U CN 204972438 U CN204972438 U CN 204972438U
- Authority
- CN
- China
- Prior art keywords
- haematodocha
- elasticity
- cystidium
- artificial heart
- liquid flow
- 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.)
- Expired - Fee Related
Links
Landscapes
- External Artificial Organs (AREA)
Abstract
(B, ) the utility model discloses an elasticity haematodocha and pneumatic bellow drive formula artificial heart pump for artificial heart, adopt a simple structure on this pneumatic bellow drive formula artificial heart pump, make convenient elasticity haematodocha for the artificial heart, with inside and outside on this elasticity haematodocha, middle two porose nipple - shaped archs, replace the extremely complicated artificial heart valve of structure, realize one -way imbibition and one -way flowing back, a rethread only trachea lets in internal gasbag formula actuating mechanism drive elasticity haematodocha work, make its alternate switching between diastole operating condition and shrink operating condition, thereby realize the process of imbibition and flowing back alternately, can the output class like pulsed blood flow cardiac naturally, working process cardiac has naturally been imitated well. Simultaneously, the elasticity haematodocha adopts be elasticity scalable material, is streamlined inside it, can not cause destruction to the cell in the blood, also is difficult for thromboses, can replace people or vertebrate work cardiac naturally well. (B, )
Description
Technical field
this utility model relates to a kind of artificial heart elasticity haematodocha and air bag driving artificial heart pump.
Background technology
heart disease is the second largest killer of human death.Human heart due to illness damage and partially or completely afunction and whole body normal circulation can not be maintained time, a kind of machinery of artificial material manufacture can be transplanted temporarily or for good and all partially or completely to replace cardiac function, promote blood circulation, this sampling device that is artificial heart, this is also that largely solving at present can not the problem of heart transplantation in time because donor is not enough for solving the effective means of heart disease in whole latter stage except heart transplantation.
at present, artificial heart mainly adopts the blood pump of two kinds of different principle, namely based on the pulsed displacement pump of Cardiac valve prosthesis, with the continuous pump of uninterrupted pump blood.But still there is such or such problem in these two kinds of artificial heart pumps at present, can not simulating nature action of the heart and function well.
the working method of pulsed volume blood pump, be very similar to natural animal hearts, its key member is Cardiac valve prosthesis, it is the check valve that control cardiac flow, its structure has close relationship with the quality of artificial heart function, its from nineteen sixty first Application in clinical, afterwards through years of researches, successively experienced by mechanical prosthetic valve, biological tissue's lobe, get involved the stage such as lobe.But Cardiac valve prosthesis is extremely complicated, and manufacturing cost is high, and easily form blood clotting, i.e. thrombosis in motive position.
such as, China Patent Publication No. is 1093005, during name is called " integral artificial heart-lung pump ", in this kind of artificial heart-lung pump, blood storing capsule is installed in pump and inserts in torso model, and such structure easily forms thrombosis in human body, and Cardiac valve prosthesis not easily manufactures.China Patent No. is 99126700.1, provides a kind of artificial heart of gas-electricity one formula in the patent that name is called " gas-electricity one formula blood pump, gas-electricity one formula artificial heart ", but its internal structure is complicated, substantially cannot realize manufacturing, and it is high to realize cost.For another example China Patent Publication No. is 103656770, and name is called " artificial heart blood pump based on minitype cylinder drives ", also there is same problem, and minitype cylinder needs the thoracic cavity on human body to connect two tracheas to external, very easily causes the discomfort of user.
because pulsed volume blood pump exists the technical bottleneck of Cardiac valve prosthesis aspect, the artificial heart of development in the recent period, mostly tends to the continuous pump adopting uninterrupted pump blood.Such as, China Patent Publication No. is 102019002A, name is called in the patent of " a kind of Implanted hollow minimal axial blood pump ", and China Patent Publication No. is 10237598, name is called in the patent of " compact axial-flow magnetic-levitation artificial heart pump ", both all have employed axial-flow pump, although it compares gear pump and vane pump, less can destroy the cell in blood, but running up of its component, the destructive rate of the cell in blood is still higher, and due to axial-flow pump be a kind of continuous pump, it can not the work process of simulating nature heart, can be described as the selectivity mistake of technique direction.
Summary of the invention
the purpose of this utility model is the shortcoming overcoming prior art, provides the artificial heart elasticity haematodocha that a kind of structure is simple, easily manufactured, can realize unidirectional imbibition and unidirectional discharge opeing.
for achieving the above object, the technical solution adopted in the utility model is: a kind of artificial heart elasticity haematodocha, comprise the cystidium with closed inner chamber be made up of retractable material, the end of described cystidium has the first projection recessed in described closed inner chamber, from the second projection that described closed inner chamber is outwardly, described first projection offers the first liquid flow hole, described second projection offers the second liquid flow hole, contraction duty when diastole duty when described cystidium has a side direction tension and side loaded, when described cystidium is in diastole duty, described first liquid flow hole is opened and is connected with described closed inner chamber and forms imbibition check valve, described second liquid flow hole closes, when described cystidium be in shrink duty time, described first liquid flow hole closes, and described second liquid flow hole is opened and is connected with described closed inner chamber and forms discharge opeing check valve.
preferably, described first projection and described second projection are all in nipple-like.
preferably, described first liquid flow hole is the streamlined bellmouth orifice that ecto-entad diameter diminishes gradually, the streamlined bellmouth orifice that described second liquid flow hole diminishes gradually in diameter from inside to outside.
preferably, the outside described cystidium being positioned at described first projection is provided with the feed flow portion possessed for sap cavity, and when described cystidium is in diastole duty, the described sap cavity that supplies is connected with described closed inner chamber by described first liquid flow hole; The outside described cystidium being positioned at described second projection is provided with the discharge opeing portion possessing exhaust chamber, and when described cystidium is in contraction duty, described exhaust chamber is connected with described closed inner chamber by described second liquid flow hole.
further preferably, described feed flow portion, described discharge opeing portion are all in streamlined.
another object of the present utility model is the shortcoming overcoming prior art, provides a kind of pulse blood supply positive displacement artificial heart pump that have above-mentioned artificial heart elasticity haematodocha, that drive with air bag.
for achieving the above object, the technical solution adopted in the utility model is:
a kind of air bag driving artificial heart pump, described artificial heart pump comprises two elasticity haematodocha, for the gasbag-type driving mechanism driving two described elasticity haematodocha flexible, each described elasticity haematodocha includes the cystidium with closed inner chamber be made up of retractable material, the end of described cystidium has the first projection recessed in described closed inner chamber, from the second projection that described closed inner chamber is outwardly, described first projection offers the first liquid flow hole, described second projection offers the second liquid flow hole, the outside described cystidium being positioned at described first projection is provided with the feed flow portion possessed for sap cavity, the outside described cystidium being positioned at described second projection is provided with the discharge opeing portion possessing exhaust chamber, described elasticity haematodocha has diastole duty and shrinks duty, when described cystidium side direction tension, described elasticity haematodocha is in diastole duty, described first liquid flow hole is opened and is made described being connected with described closed inner chamber for sap cavity form imbibition check valve, blood is by the described closed inner chamber entering described elasticity haematodocha for sap cavity, described second liquid flow hole closes, when described cystidium side loaded, described elasticity haematodocha is in contraction duty, described first liquid flow hole closes, described second liquid flow hole is opened and described exhaust chamber is connected with described closed inner chamber form discharge opeing check valve, blood enters described exhaust chamber by the closed inner chamber of described elasticity haematodocha
described gasbag-type driving mechanism comprises to be located between two described elasticity haematodocha and can along the air bag of self radial expansion, the radial two ends of described air bag are fixedly connected with the side of two described cystidiums respectively, the opposite side of described cystidium is fixedly installed, and described gasbag-type driving mechanism also comprises the feeder expanding for inflation in the inner chamber to described air bag or evacuation to make described bag volume or reduce.
preferably, described first protruding with described second projection all in nipple-like, described first liquid flow hole is the streamlined bellmouth orifice that ecto-entad diameter diminishes gradually, and described second liquid flow hole is the streamlined bellmouth orifice that diminishes gradually of diameter from inside to outside.
preferably, the radial both sides of described air bag have been permanently connected pressing plate respectively, the end face outside of described pressing plate is in the cambered surface consistent with the side end face appearance profile of described cystidium, and the outer face of described pressing plate and the side end face of described cystidium bond together regularly.
preferably, the closed inner chamber of two described cystidiums forms left ventricle and the right ventricle of described artificial heart respectively, accordingly, and the left atrium and the right atrium that form described artificial heart for sap cavity respectively in two described feed flow portions.
preferably, described feeder comprises the trachea inside and outside vacuum generation cylinder, connection human or animal thoracic cavity, realizes inflation and evacuation between described trachea, described vacuum generation cylinder and air bag by electromagnetic valve commutation control.
due to the utilization of technique scheme, this utility model compared with prior art has following advantages: air bag driving artificial heart pump of the present utility model, wherein by adopting a kind of structure simple, easily manufactured artificial heart elasticity haematodocha, with inside and outside on this elasticity haematodocha, middle two porose nipple-like projections, replace the Cardiac valve prosthesis that structure is extremely complicated, realize unidirectional imbibition and unidirectional discharge opeing, again by only having the trachea gasbag-type driving mechanism passed in body to drive elasticity haematodocha to stretch, it is made alternately to change between diastole duty and contraction duty, thus alternately realize the process of imbibition and discharge opeing, can output class like the pulsed blood flow of natural heart, avoid technical side tropism's mistake of continuous blood pump, imitate the work process of natural heart well.Meanwhile, what elasticity haematodocha adopted is resilientiy stretchable material, and inside is streamlined, can not damage, also not easily form thrombosis to the cell in blood, can substitute the work of people or vertebrates nature heart well.
Accompanying drawing explanation
accompanying drawing 1, accompanying drawing 2 are used for an embodiment of Single Cardiac Ventricle for this utility model, and wherein accompanying drawing 1 is the cystidium of elasticity haematodocha schematic diagram when being in diastole duty; Accompanying drawing 2 is the schematic diagram that the cystidium of elasticity haematodocha is in when shrinking duty;
accompanying drawing 3, accompanying drawing 4 are used for a Biventricular embodiment for this utility model, and wherein, accompanying drawing 3 is the schematic diagram of artificial heart pump of the present utility model when being in diastole duty; Accompanying drawing 4 is the schematic diagram that artificial heart pump of the present utility model is in when shrinking duty.
wherein: 100, elasticity haematodocha; 1, cystidium; 10, closed inner chamber; 11, first is protruding; 12, the first liquid flow hole; 13, second is protruding; 14, the second liquid flow hole; 2, feed flow portion; 21, for sap cavity; 22, supply opening; 3, discharge opeing portion; 31, exhaust chamber; 32, leakage fluid dram;
200, gasbag-type driving mechanism; 4, air bag; 5, pressing plate; 6, vacuum generation cylinder; 7, two position three way directional control valve; 8, two-position four way change valve.
Detailed description of the invention
below in conjunction with accompanying drawing and specific embodiment, the technical solution of the utility model is further elaborated.
see Fig. 1, Figure 2 shows that the embodiment of elasticity haematodocha 100 for Single Cardiac Ventricle.This elasticity haematodocha 100 comprises the cystidium 1 with closed inner chamber 10 be made up of retractable material, the end of this cystidium 1 to have in closed inner chamber 10 the second projection 13 that the first recessed projection 11, self-enclosed inner chamber 10 are outwardly, first projection 11 offers the first liquid flow hole 12, second projection 13 offers the second liquid flow hole 14, wherein on cystidium 1, the first protruding 11 and second projection 13 is located at the two ends of cystidium 1 respectively.When cystidium 1 is subject to lateral force, its internal capacity is expanded, cystidium 1 inside will produce so-called " negative pressure ", namely elasticity haematodocha 100 bears the effect of environmental stress, as shown by the arrows in Figure 1, under the effect of this pressure, second liquid flow hole 14 at the outwardly second protruding 13 places closes, and open to first liquid flow hole 12 at the projecting inward first protruding 11 places, it is inner that blood stream flows into cystidium 1 by outside.When cystidium 1 is subject to lateral pressure, its internal capacity shrinks, cystidium 1 internal pressure will be greater than external environment condition pressure, internal pressure distribution as shown by the arrows in Figure 2, under the effect of this pressure, the first liquid flow hole 12 to the projecting inward first protruding 11 places closes, and second liquid flow hole 14 at the outwardly second protruding 13 places is opened, and blood stream flows to outside by cystidium 1 inside.
see Fig. 3, Figure 4 shows that the biventricular artificial heart pump that air bag drives, this artificial heart pump mainly comprise two elasticity haematodocha 100 and for ordering about the flexible gasbag-type driving mechanism 200 of this elasticity haematodocha 100.
as shown in Figure 3, Figure 4, these two elasticity haematodocha 100 include the cystidium 1 with closed inner chamber 10 be made up of retractable material, the end of this cystidium 1 to have in closed inner chamber 10 the second projection 13 that the first recessed projection 11, self-enclosed inner chamber 10 are outwardly, first projection 11 offers in the first liquid flow hole 12, second projection 13 and offer the second liquid flow hole 14.When cystidium 1 is subject to the pulling force of side direction, cystidium 1 diastole and cause internal capacity to expand, the first liquid flow hole 12 can be opened and be connected with closed inner chamber 10, and now the second liquid flow hole 14 closes; When cystidium 1 is subject to the pressure of side direction, cystidium 1 shrinks and causes internal capacity to reduce, and the first liquid flow hole 12 closes, and now the second liquid flow hole 14 is opened and is connected with closed inner chamber 10.
shown in Fig. 3, Fig. 4, outside cystidium 1 being positioned at the first projection 11 is provided with the feed flow portion 2 possessed for sap cavity 21, and outside cystidium 1 being positioned at the second projection 13 is provided with the discharge opeing portion 3 possessing exhaust chamber 31.Feed flow portion 2 has the supply opening 22 be communicated with for sap cavity 21, discharge opeing portion 3 has the leakage fluid dram 32 be connected with exhaust chamber 31.
elasticity haematodocha 100 has diastole duty and shrinks duty, when the tension diastole of cystidium 1 side direction, namely elasticity haematodocha 100 is in diastole duty and causes internal capacity to expand, now the first liquid flow hole 12 is opened and makes to be connected with closed inner chamber 10 by the first liquid flow hole 12 for sap cavity 21, and the second liquid flow hole 14 is closed, now liquid stream can enter from supply opening 22 and enter the closed inner chamber 10 of cystidium 1 through the first liquid flow hole 12 for sap cavity 21 again, realizes feed flow; When cystidium 1 side loaded is shunk, namely elasticity haematodocha 100 is in and shrinks duty and cause internal capacity to reduce, now the first liquid flow hole 12 is closed, second liquid flow hole 14 is opened and exhaust chamber 31 is connected with closed inner chamber 10 by the second liquid flow hole 14, now liquid stream can enter exhaust chamber 31 from closed inner chamber 10 by the second liquid flow hole 14, discharge through leakage fluid dram 32 again, realize discharge opeing.
like this, that is be provided with the first protruding 11 formation imbibition check valves of the first liquid flow hole 12, be provided with the second liquid flow hole 14 second protruding 13 then forms discharge opeing check valve.On each elasticity haematodocha 100, the closed inner chamber 10 of cystidium 1 forms the ventricle of artificial heart, and feed flow portion 2 then forms atrium for sap cavity 21.
in the above-described embodiments, first protruding 11 and second projection 13 is all in nipple-like, the streamlined bellmouth orifice that first liquid flow hole 12 diminishes gradually in ecto-entad aperture, the streamlined bellmouth orifice that second liquid flow hole 14 diminishes gradually in aperture from inside to outside, so just, can when cystidium 1 be subject to lateral force, first protruding 11 place's tensions and the first liquid flow hole 12 is opened, second protruding 13 place's tensions and the second liquid flow hole 14 is closed; When cystidium 1 is subject to lateral pressure, first protruding 11 place's pressurizeds and the first liquid flow hole 12 is closed, second protruding 13 place's pressurizeds and the second liquid flow hole 14 is opened.Feed flow portion 2 and discharge opeing portion 3 are all arranged to streamlined.When specifically arranging, cystidium 1 and feed flow portion 2, discharge opeing portion 3 are wholely set, and feed flow portion 2 and discharge opeing portion 3 are positioned at same one end of cystidium 1.
this elasticity haematodocha 100 adopts resilientiy stretchable material to make, and it can not damage the cell in blood in the course of the work, not easily in human body or animal body, forms thrombosis, and can export the liquid stream of pulse by natural imitation heart.
shown in Fig. 3, Fig. 4, gasbag-type driving mechanism 200 comprises to be located between two elasticity haematodocha 100 and can along the air bag 4 of self radial expansion, the radial two ends of this air bag 4 are fixedly connected with the side of two cystidiums 1 respectively, and the opposite side of cystidium 1 is fixedly installed.Herein, the radial both sides of this air bag 4 have been permanently connected pressing plate 5 respectively, and the end face outside of this pressing plate 5 is in the cambered surface consistent with the side end face appearance profile of cystidium 1, and the outer face of pressing plate 5 and the side end face of cystidium 1 bond together regularly.Like this, just can pull cystidium 1 or laterally pressure holding cystidium 1 when air bag 4 radially occurs flexible, thus make cystidium 1 diastole or contraction and cause its internal capacity expand or reduce.
two elasticity haematodocha 100 are similar to left part and the right part of people or vertebrates nature heart respectively, the closed inner chamber of two cystidiums 1 forms left ventricle and the right ventricle of artificial heart respectively, accordingly, the left atrium and the right atrium that form artificial heart for sap cavity 21 respectively in two feed flow portions 2.
this gasbag-type driving mechanism 200 also comprises for inflation or evacuation in the inner chamber to air bag 4 to make air bag 4 cubical expansion or to reduce thus the feeder making it radially stretch.This feeder comprises vacuum generation cylinder 6, be communicated with trachea (not shown) inside and outside human or animal, between trachea, vacuum generation cylinder 6 and air bag 4 by inflation from solenoid directional control valve control realization to air bag 4 inner chamber with bleed.
as shown in Figure 3, Figure 4, solenoid directional control valve comprises two position three way directional control valve 7 and two-position four way change valve 8 herein.As shown in Figure 3, two position three way directional control valve 7 is in right position and two-position four way change valve 8 when being in the work of left position, the piston rod that Compressed Gas promotes vacuum generation cylinder 6 moves to rodless cavity one end, its piston rod front end intracavity produces negative pressure because of volume enlargement, the gas of air bag 4 inner chamber just enters the piston rod front end intracavity of vacuum generation cylinder 6 through two position three way directional control valve 7, make also to produce negative pressure in air bag and be in contraction state, thus pull two pressing plates 5 to move to center position simultaneously, the cystidium 1 of elasticity haematodocha 100 is subject to the pulling force of side direction and diastole, internal capacity is caused to expand, now, second liquid flow hole 14 is closed, and the first liquid flow hole 12 is opened, outside liquid stream is entered by supply opening 22 and enters in the closed inner chamber 10 of cystidium 1 through the first liquid flow hole 12 again for sap cavity 21, then, two position three way directional control valve 7 and switch valve with two-position and five-pass 8 commutation work, two position three way directional control valve 7 is switched to the work of left position and two-position four way change valve 8 is switched to right position, as shown in Figure 4, Compressed Gas enters the rodless cavity of vacuum generation cylinder 6 and orders about piston rod to rod chamber side and move, and its chamber, piston rod front end communicates with air, Compressed Gas enters through two position three way directional control valve 7 in the inner chamber of air bag 4 simultaneously, air bag 4 internal volume is made to expand and expand, thus two pressing plates 5 are moved simultaneously laterally, the pressure of side direction is applied to cystidium 1 and makes elasticity haematodocha 100 be converted to contraction duty, first liquid flow hole 12 is closed, and the second liquid flow hole 14 is opened, the liquid stream in cystidium 1 closed inner chamber 10 enters exhaust chamber 31 by the second liquid flow hole 14, and discharges through leakage fluid dram 32 and supply blood to health.Then, two position three way directional control valve 7 and switch valve with two-position and five-pass 8 commutation work again, elasticity haematodocha 100 is converted to again diastole duty, so two elasticity haematodocha 100 of this artificial heart pump are at diastole duty and contraction duty part checker, thus realize the alternately continuous firing of imbibition and discharge opeing.
to sum up, air bag driving artificial heart pump of the present utility model, wherein by adopting a kind of structure simple, easily manufactured artificial heart elasticity haematodocha 100, with inside and outside on this elasticity haematodocha 100, middle two porose nipple-like projections, replace the Cardiac valve prosthesis that structure is extremely complicated, realize unidirectional imbibition and unidirectional discharge opeing, again by only having the trachea gasbag-type driving mechanism passed in body to drive elasticity haematodocha 100 to work, it is made alternately to change between diastole duty and contraction duty, thus alternately realize the process of imbibition and discharge opeing, can output class like the pulsed blood flow of natural heart, avoid technical side tropism's mistake of continuous blood pump, imitate the work process of natural heart well.Meanwhile, what elasticity haematodocha 100 adopted is resilientiy stretchable material, and it is inner is streamlined, can not damage, also not easily form thrombosis to the cell in blood, can substitute the work of people or vertebrates nature heart well.
above-described embodiment, only for technical conceive of the present utility model and feature are described, its object is to person skilled in the art can be understood content of the present utility model and implement according to this, can not limit protection domain of the present utility model with this.All equivalences done according to this utility model spirit change or modify, and all should be encompassed within protection domain of the present utility model.
Claims (10)
1. an artificial heart elasticity haematodocha, it is characterized in that: comprise the cystidium with closed inner chamber be made up of retractable material, the end of described cystidium has the first projection recessed in described closed inner chamber, from the second projection that described closed inner chamber is outwardly, described first projection offers the first liquid flow hole, described second projection offers the second liquid flow hole, contraction duty when diastole duty when described cystidium has a side direction tension and side loaded, when described cystidium is in diastole duty, described first liquid flow hole is opened and is connected with described closed inner chamber and forms imbibition check valve, described second liquid flow hole closes, when described cystidium be in shrink duty time, described first liquid flow hole closes, and described second liquid flow hole is opened and is connected with described closed inner chamber and forms discharge opeing check valve.
2. artificial heart elasticity haematodocha according to claim 1, is characterized in that: described first projection and described second projection are all in nipple-like.
3. artificial heart elasticity haematodocha according to claim 1 and 2, is characterized in that: described first liquid flow hole is the streamlined bellmouth orifice that ecto-entad diameter diminishes gradually, the streamlined bellmouth orifice that described second liquid flow hole diminishes gradually in diameter from inside to outside.
4. artificial heart elasticity haematodocha according to claim 1, it is characterized in that: the outside described cystidium being positioned at described first projection is provided with the feed flow portion possessed for sap cavity, when described cystidium is in diastole duty, the described sap cavity that supplies is connected with described closed inner chamber by described first liquid flow hole; The outside described cystidium being positioned at described second projection is provided with the discharge opeing portion possessing exhaust chamber, and when described cystidium is in contraction duty, described exhaust chamber is connected with described closed inner chamber by described second liquid flow hole.
5. artificial heart elasticity haematodocha according to claim 4, is characterized in that: described feed flow portion, described discharge opeing portion are all in streamlined.
6. an air bag driving artificial heart pump, it is characterized in that: described artificial heart pump comprises two elasticity haematodocha, for the gasbag-type driving mechanism driving two described elasticity haematodocha flexible, each described elasticity haematodocha includes the cystidium with closed inner chamber be made up of retractable material, the end of described cystidium has the first projection recessed in described closed inner chamber, from the second projection that described closed inner chamber is outwardly, described first projection offers the first liquid flow hole, described second projection offers the second liquid flow hole, the outside described cystidium being positioned at described first projection is provided with the feed flow portion possessed for sap cavity, the outside described cystidium being positioned at described second projection is provided with the discharge opeing portion possessing exhaust chamber, described elasticity haematodocha has diastole duty and shrinks duty, when described cystidium side direction tension, described elasticity haematodocha is in diastole duty, described first liquid flow hole is opened and is made described being connected with described closed inner chamber for sap cavity form imbibition check valve, blood is by the described closed inner chamber entering described elasticity haematodocha for sap cavity, described second liquid flow hole closes, when described cystidium side loaded, described elasticity haematodocha is in contraction duty, described first liquid flow hole closes, described second liquid flow hole is opened and described exhaust chamber is connected with described closed inner chamber form discharge opeing check valve, blood enters described exhaust chamber by the closed inner chamber of described elasticity haematodocha
Described gasbag-type driving mechanism comprises to be located between two described elasticity haematodocha and can along the air bag of self radial expansion, the radial two ends of described air bag are fixedly connected with the side of two described cystidiums respectively, the opposite side of described cystidium is fixedly installed, and described gasbag-type driving mechanism also comprises the feeder expanding for inflation in the inner chamber to described air bag or evacuation to make described bag volume or reduce.
7. a kind of air bag driving artificial heart pump according to claim 6, it is characterized in that: described first projection and described second projection are all in nipple-like, described first liquid flow hole is the streamlined bellmouth orifice that ecto-entad diameter diminishes gradually, the streamlined bellmouth orifice that described second liquid flow hole diminishes gradually in diameter from inside to outside.
8. a kind of air bag driving artificial heart pump according to claim 6, it is characterized in that: the radial both sides of described air bag have been permanently connected pressing plate respectively, the end face outside of described pressing plate is in the cambered surface consistent with the side end face appearance profile of described cystidium, and the outer face of described pressing plate and the side end face of described cystidium bond together regularly.
9. a kind of air bag driving artificial heart pump according to claim 6, it is characterized in that: the closed inner chamber of two described cystidiums forms left ventricle and the right ventricle of described artificial heart respectively, accordingly, the left atrium and the right atrium that form described artificial heart for sap cavity respectively in two described feed flow portions.
10. a kind of air bag driving artificial heart pump according to claim 6, it is characterized in that: described feeder comprises the trachea inside and outside vacuum generation cylinder, connection human or animal thoracic cavity, realizes inflation and evacuation between described trachea, described vacuum generation cylinder and air bag by electromagnetic valve commutation control.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201520697033.6U CN204972438U (en) | 2015-09-10 | 2015-09-10 | Elasticity haematodocha and pneumatic bellow drive formula artificial heart pump for artificial heart |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201520697033.6U CN204972438U (en) | 2015-09-10 | 2015-09-10 | Elasticity haematodocha and pneumatic bellow drive formula artificial heart pump for artificial heart |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN204972438U true CN204972438U (en) | 2016-01-20 |
Family
ID=55106864
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201520697033.6U Expired - Fee Related CN204972438U (en) | 2015-09-10 | 2015-09-10 | Elasticity haematodocha and pneumatic bellow drive formula artificial heart pump for artificial heart |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN204972438U (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105268041A (en) * | 2015-09-10 | 2016-01-27 | 苏州大学张家港工业技术研究院 | Elastic haematodocha for artificial heart and air-bag-driven artificial heart pump |
| CN112972886A (en) * | 2021-02-02 | 2021-06-18 | 北京工业大学 | Single-slider volumetric blood pump |
-
2015
- 2015-09-10 CN CN201520697033.6U patent/CN204972438U/en not_active Expired - Fee Related
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105268041A (en) * | 2015-09-10 | 2016-01-27 | 苏州大学张家港工业技术研究院 | Elastic haematodocha for artificial heart and air-bag-driven artificial heart pump |
| CN112972886A (en) * | 2021-02-02 | 2021-06-18 | 北京工业大学 | Single-slider volumetric blood pump |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN103656770B (en) | Based on the artificial heart blood pump that minitype cylinder drives | |
| CA2916350C (en) | Artificial ventricles | |
| MY179795A (en) | A device and a method to controllably assist movement of a mitral valve | |
| CN105251068A (en) | Electromagnetic-permanent magnetism bidirectional driving type artificial heart pump | |
| CN208607807U (en) | A kind of blood circulation system modeling and simulating auxiliary device | |
| US11324941B2 (en) | Intraventricular pulsating blood pump | |
| AR036548A1 (en) | BODY IMPLANT DEVICE FOR BLOOD CIRCULATORY ASSISTANCE AND VENTRICULAR CARDIACA | |
| CN105268041A (en) | Elastic haematodocha for artificial heart and air-bag-driven artificial heart pump | |
| CN204972438U (en) | Elasticity haematodocha and pneumatic bellow drive formula artificial heart pump for artificial heart | |
| CN104346987A (en) | Heart chamber simulator driving mechanism | |
| CN107456616A (en) | Heart analog machine | |
| US20160310651A1 (en) | Artificial heart | |
| JPS58500793A (en) | Hydraulically operated cardiac prosthesis | |
| US20200009305A1 (en) | Saccular Cavopulmonary Assist Device | |
| US7066874B2 (en) | Devices and methods for blood flow assistance | |
| CN204972442U (en) | Twin columns stopper cylinder drive formula artificial heart pump | |
| CN204972440U (en) | Two -way drive formula artificial heart pump of electromagnetism - permanent magnetism | |
| US20180064864A1 (en) | Artificial Ventricles | |
| CN105107038A (en) | Double-plunger cylinder driving artificial heart pump | |
| CN102247218A (en) | Animal cardiac failure induction device | |
| CN204972441U (en) | Motor - two -way spiral drive formula artificial heart pump | |
| CN207693993U (en) | Cryptomere chamber lung auxiliary circulating equipment | |
| CN206777567U (en) | A kind of pneumatic heart auxiliary pump blood device | |
| CN211628544U (en) | Heart blood circulation demonstration device | |
| CN203122681U (en) | Tricuspid valve mechanical valve with two different-sized leaflets |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| TR01 | Transfer of patent right |
Effective date of registration: 20170807 Address after: Suzhou City, Jiangsu province 215137 Xiangcheng District Ji Road No. 8 Patentee after: Soochow University Address before: Zhangjiagang mayor Jingyang Road Suzhou City, Jiangsu province 215600 No. 10 Patentee before: Zhangjiagang Institute of Industrial Technologies Soochow University |
|
| TR01 | Transfer of patent right | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20160120 Termination date: 20180910 |
|
| CF01 | Termination of patent right due to non-payment of annual fee |