CN111937860A

CN111937860A - Isolated organ perfusion system

Info

Publication number: CN111937860A
Application number: CN202010825552.1A
Authority: CN
Inventors: 陈静瑜; 刘强; 卫栋; 周鹏; 刘峰; 卢艳; 李伯贵; 张勃; 魏晓磊; 林祥华; 钟嘉伟; 张春虹; 吴懿苗; 何霖; 杨振坤
Original assignee: Wuxi Peoples Hospital; Guangdong Shunde Industrial Design Institute
Current assignee: Wuxi Peoples Hospital; Guangdong Shunde Industrial Design Institute
Priority date: 2020-08-17
Filing date: 2020-08-17
Publication date: 2020-11-17
Anticipated expiration: 2040-08-17
Also published as: CN111937860B

Abstract

The invention relates to an isolated organ perfusion system, which comprises a liquid storage container, a centrifugal pump, a membrane lung, a first peristaltic pump, a leukocyte filter, a hemodialyzer and a waste liquid bag. The liquid inlet end of the first peristaltic pump is communicated with the liquid storage container through a pipeline, and the liquid outlet end of the first peristaltic pump is communicated with the liquid inlet end of the hemodialyzer through a pipeline. The liquid outlet end of the hemodialyzer is communicated with the liquid storage container through a pipeline, and the waste discharge end of the hemodialyzer is communicated with the waste liquid bag through a pipeline. The liquid storage container, the first peristaltic pump and the hemodialyzer form a filtration circulation auxiliary path, and the leukocyte filter is arranged on the filtration circulation auxiliary path. When the leukocyte filter leads to the jam because of long-time work, the leukocyte filter can lead to the filtration circulation auxiliary road to take place to block up, and can not lead to the perfusion circulation main road to take place to block up, and the perfusion circulation main road still can continue to work this moment, can continuously play the guard action to isolated organ to in time change filtration circulation auxiliary road on the leukocyte filter can.

Description

Isolated organ perfusion system

Technical Field

The invention relates to the technical field of perfusion devices, in particular to an isolated organ perfusion system.

Background

Mechanical perfusion is a way of preserving and transferring organs, blood vessels of the organs are connected to an isolated organ perfusion system after the organs are obtained, and the isolated organ perfusion system continuously perfuses perfusion liquid to the isolated organs in the organ preservation and transfer stage and simultaneously supplies oxygen, nutrients and the like to the isolated organs.

In the conventional technology, an isolated organ perfusion system comprises a membrane lung, a liquid storage container, a waste liquid tank, a leukocyte filter and a dialyzer. The liquid storage container, the centrifugal pump, the leukocyte filter, the membrane lung and the isolated organ form a main path, and the liquid storage container, the peristaltic pump, the dialyzer and the waste liquid tank form a branch. Generally, before the staff do the perfusion, various required consumables need to be built and assembled together, then the isolated organ is perfused, and the on-site assembling work of various consumables not only improves the experiment or clinical difficulty, has reduced work efficiency simultaneously.

Disclosure of Invention

Based on this, it is necessary to overcome the defects of the prior art and provide an isolated organ perfusion system, which can improve the working efficiency, reduce the experiment difficulty and improve the success rate of the experiment.

The technical scheme is as follows: an ex vivo organ perfusion system, comprising: the blood dialyzer comprises an outer sleeve package, a liquid storage container, an auxiliary installation shell, a hemodialyzer and a membrane lung, wherein the liquid storage container is arranged in the outer sleeve package, the liquid storage container is used for installing perfusate, the auxiliary installation shell is detachably arranged in the outer sleeve package, and the hemodialyzer and the membrane lung are detachably arranged in the auxiliary installation shell.

Foretell isolated organ perfusion system, hemodialyzer and membrane lung all belong to the consumptive material, install hemodialyzer and membrane lung in supplementary installation shell, supplementary installation shell all installs in the overcoat package with the stock solution container, when using, directly put into the stock solution container with isolated organ and insert the filling line in can, need not the on-the-spot equipment consumptive material and carry out disinfection work after the consumptive material has been assembled, so can improve experiment work efficiency. In addition, when one of them consumptive material broke down, can wholly change supplementary installation shell with the consumptive material, also can change the consumptive material that breaks down alone, it is comparatively convenient to operate.

In one embodiment, the isolated organ perfusion system further comprises a PH monitor, a micro-plug filter and a leukocyte filter, wherein the PH monitor, the micro-plug filter and the leukocyte filter are detachably mounted in the auxiliary mounting shell.

In one embodiment, the isolated organ perfusion system further comprises a first clamp, a second clamp, a third clamp, a fourth clamp and a fifth clamp disposed on the auxiliary mounting shell; the hemodialyzer is detachably arranged on the first clamp, the membrane lung is detachably arranged on the second clamp, the pH monitor is detachably arranged on the third clamp, the micro-suppository filter is detachably arranged on the fourth clamp, and the leukocyte filter is detachably arranged on the fifth clamp.

In one embodiment, the first clamp comprises two first clamping plates which are oppositely arranged on the auxiliary mounting shell, and the first clamping plates are provided with first arc-shaped surfaces which are matched with the side wall of the hemodialyzer; the second clamp comprises two second clamping plates which are oppositely arranged on the auxiliary mounting shell, and the second clamping plates are provided with second arc-shaped surfaces which are matched with the side walls of the membrane lungs; the third clamp comprises two third clamping plates which are oppositely arranged on the auxiliary mounting shell, and the third clamping plates are provided with third arc-shaped surfaces which are matched with the side walls of the PH monitor; fourth anchor clamps including set up in backup pad on the supplementary installation shell, be equipped with relative and coaxial two arc holes in the backup pad, and with the via hole of the tip correspondence intercommunication in arc hole, two first latch structures and two on the micro-bolt filter bottom surface the via hole one-to-one sets up, first latch structure can pass the via hole can along the arc hole removes, the buckle area size of first latch structure is greater than the width in arc hole.

In one embodiment, the isolated organ perfusion system further comprises a centrifugal pump, a first peristaltic pump, and a waste fluid bag; the liquid inlet end of the centrifugal pump is communicated with the liquid storage container through a pipeline, the liquid outlet end of the centrifugal pump is communicated with the liquid inlet end of the membrane lung through a pipeline, the liquid outlet end of the membrane lung is used for being connected with an isolated organ through a pipeline, and the liquid storage container, the centrifugal pump, the membrane lung and the isolated organ form a perfusion circulation main path;

the liquid inlet end of the first peristaltic pump is communicated with the liquid storage container through a pipeline, the liquid outlet end of the first peristaltic pump is communicated with the liquid inlet end of the hemodialyzer through a pipeline, the liquid outlet end of the hemodialyzer is communicated with the liquid storage container through a pipeline, the waste discharge end of the hemodialyzer is communicated with the waste liquid bag through a pipeline, the liquid storage container, the first peristaltic pump and the hemodialyzer form a filtration circulation auxiliary path, the leukocyte filter is arranged on the perfusion circulation main path or the filtration circulation auxiliary path, and the micro-suppository filter is arranged on the perfusion circulation main path or on the filtration circulation auxiliary path.

In one embodiment, the leukocyte depletion filter is disposed on tubing between the first peristaltic pump and the hemodialyzer.

In one embodiment, the isolated organ perfusion system further comprises a first pressure sensor and a second pressure sensor, wherein the first pressure sensor is arranged at the outlet end or the inlet end of the leukocyte filter, and the second pressure sensor is arranged at the outlet end of the membrane lung.

In one embodiment, the isolated organ perfusion system further comprises a first sensor clamp and a second sensor clamp; the first sensor clamp is arranged on the auxiliary mounting shell or the outer side wall of the liquid storage container, and the first pressure sensor is detachably arranged on the first sensor clamp; the second sensor clamp is arranged on the outer side wall of the liquid storage container, and the second pressure sensor is detachably arranged on the second sensor clamp.

In one embodiment, the first sensor clamp comprises a base plate and two L-shaped limiting plates connected to two opposite sides of the base plate; the bottom plate is arranged on the auxiliary mounting shell or on the outer side wall of the liquid storage container, a strip-shaped opening is formed in the L-shaped limiting plate, the L-shaped limiting plate is in limiting fit with the seat plate of the first pressure sensor to prevent the seat plate from moving in the direction perpendicular to the surface of the bottom plate, the seat plate can slide along the surface of the bottom plate, a mounting hole corresponding to the strip-shaped opening is formed in the seat plate, and the seat plate penetrates through the strip-shaped opening through a mounting piece and is arranged on the L-shaped limiting plate.

In one embodiment, a wall of the auxiliary mounting shell is provided with a second locking structure, a wall of the outer bag is provided with a locking hole corresponding to the second locking structure, and the second locking structure is arranged in the locking hole; the isolated organ perfusion system further comprises a support and a second cover body, the support is arranged on the inner wall of the liquid storage container, and the support is used for supporting and placing an isolated organ; the second cover body is arranged at the opening part of the liquid storage container in an openable way; isolated organ perfusion system still includes communicating pipe and level sensor, communicating pipe is located outside the stock solution container, the bottom of communicating pipe with the stock solution container is linked together, level sensor set up in communicating pipe is last, level sensor is used for acquireing liquid level height on communicating pipe.

Drawings

FIG. 1 is a schematic diagram of an isolated organ perfusion system according to an embodiment of the present invention;

FIG. 2 is a schematic view of an isolated organ perfusion system with a first cover omitted according to an embodiment of the present invention;

FIG. 3 is an exploded view of an isolated organ perfusion system according to an embodiment of the present invention;

FIG. 4 is a view of one embodiment of the auxiliary mounting housing of the isolated organ perfusion system;

FIG. 5 is a view illustrating another perspective of an auxiliary mounting housing of an isolated organ perfusion system according to an embodiment of the present invention;

FIG. 6 is a view of one of the auxiliary mounting shell-packaged consumables of the isolated organ perfusion system according to an embodiment of the present invention;

FIG. 7 is a view of another perspective of the auxiliary mounting housing of the isolated organ perfusion system with consumable parts according to an embodiment of the present invention;

FIG. 8 is a schematic diagram of an isolated organ perfusion system with a reservoir containing a first pressure sensor and a second pressure sensor, according to an embodiment of the present invention;

FIG. 9 is an enlarged schematic view of FIG. 8 at A;

FIG. 10 is a schematic diagram of an isolated organ perfusion system without a first pressure sensor and a second pressure sensor in a reservoir of the system;

FIG. 11 is a schematic diagram of an isolated organ perfusion system according to an embodiment of the present invention;

FIG. 12 is an enlarged view of FIG. 11 at B;

FIG. 13 is a schematic sectional view of a portion of an ex vivo organ perfusion system according to an embodiment of the present invention;

FIG. 14 is a schematic sectional view of another part of an isolated organ perfusion system according to an embodiment of the present invention;

FIG. 15 is an enlarged schematic view of FIG. 14 at C;

FIG. 16 is a simplified schematic diagram of an ex vivo organ perfusion system in accordance with an embodiment of the present invention.

10. Wrapping the bag; 11. a first cover body; 12. buckling holes; 20. a reservoir; 21. a trapezoidal boss; 22. A liquid outlet; 23. a joint; 24. a support; 25. a second cover body; 30. an auxiliary mounting housing; 31. a second locking structure; 41. a hemodialyzer; 42. a membrane lung; 43. a pH monitor; 44. a microembolus filter; 441. A first latch structure; 45. a centrifugal pump; 46. a first peristaltic pump; 47. a waste liquid bag; 48. a first pressure sensor; 481. a seat plate; 482. mounting holes; 49. a second pressure sensor; 51. a first clamp; 511. a first clamping plate; 52. a second clamp; 521. a second clamping plate; 53. a third clamp; 531. a third clamping plate; 54. a fourth clamp; 541. a support plate; 542. an arc-shaped hole; 543. a via hole; 55. a first sensor clamp; 551. a base plate; 552. an L-shaped limiting plate; 553. a strip-shaped opening; 56. a second sensor clamp; 57. a leukocyte filter; 61. a communicating pipe; 62. a liquid level sensor; 63. a flow guiding frame; 631. a top plate; 632. a foot plate; 633. a gap; 64. a first on-off valve; 65. a fluid infusion bag; 66. a second on-off valve; 67. A second peristaltic pump; 68. a first temperature sensor; 69. a second temperature sensor; 70. a flow sensor.

Detailed Description

In order to make the aforementioned objects, features and advantages of the present invention comprehensible, embodiments accompanied with figures are described in detail below. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present invention. This invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein.

Referring to fig. 1, 6 and 7, fig. 1 is a schematic structural diagram of an isolated organ perfusion system according to an embodiment of the present invention, fig. 6 is a structural diagram of one perspective of a consumable installed in an auxiliary installation housing 30 of the isolated organ perfusion system according to an embodiment of the present invention, and fig. 7 is a structural diagram of another perspective of a consumable installed in an auxiliary installation housing 30 of the isolated organ perfusion system according to an embodiment of the present invention. An ex vivo organ perfusion system, comprising: the kit comprises an outer sleeve 10, a liquid storage container 20, an auxiliary mounting shell 30, a hemodialyzer 41 and a membrane lung 42. The liquid storage container 20 is arranged in the sheath package 10, the liquid storage container 20 is used for containing perfusate, the auxiliary mounting shell 30 is detachably arranged in the sheath package 10, and the hemodialyzer 41 and the membrane lung 42 are both detachably arranged in the auxiliary mounting shell 30.

Foretell isolated organ perfusion system, hemodialyzer 41 all belongs to the consumptive material with membrane lung 42, install hemodialyzer 41 and membrane lung 42 in supplementary installation shell 30, supplementary installation shell 30 all installs in overcoat package 10 with stock solution container 20, when using, directly put into stock solution container 20 with isolated organ and insert into the filling line can, need not the on-the-spot equipment consumptive material and carry out the disinfection work after the equipment consumptive material, so can improve experiment work efficiency. In addition, when one of them consumptive material broke down, can be with supplementary installation shell 30 and take the consumptive material whole to change, also can change the consumptive material that breaks down alone, it is comparatively convenient to operate.

Referring to fig. 2, 6 and 7, fig. 2 is a schematic structural view of an isolated organ perfusion system according to an embodiment of the present invention, in which a first cover 11 is omitted. Further, the isolated organ perfusion system further comprises a pH monitor 43, a micro-plug filter 44 and a leukocyte filter 57. The pH monitor 43, the micro-plug filter 44 and the leukocyte filter 57 are detachably mounted in the auxiliary mounting case 30. Therefore, when isolated organ perfusion system still includes pH monitor 43, when microembolus filter 44 and leucocyte filter 57, also can install pH monitor 43, microembolus filter 44 and leucocyte filter 57 detachably in supplementary installation shell 30, make pH monitor 43, microembolus filter 44 and leucocyte filter 57 three, and both adorn in same supplementary installation shell 30 with hemodialyzer 41 and membrane lung 42, can form a combination module through the tube coupling earlier, when using, directly put into the stock solution container 20 with isolated organ and insert in the filling line can, need not the on-the-spot equipment consumptive material and carry out disinfection work after the equipment consumptive material, so can improve experiment work efficiency. In addition, when one of them consumptive material broke down, can be with supplementary installation shell 30 and take the consumptive material whole to change, also can change the consumptive material that breaks down alone, it is comparatively convenient to operate.

Referring to fig. 3 to 7, fig. 3 illustrates an exploded view of an isolated organ perfusion system in an embodiment of the present invention, fig. 4 illustrates a view-point structural diagram of an auxiliary mounting housing 30 of the isolated organ perfusion system in an embodiment of the present invention, fig. 5 illustrates another view-point structural diagram of the auxiliary mounting housing 30 of the isolated organ perfusion system in an embodiment of the present invention, fig. 6 illustrates a view-point structural diagram of a consumable assembled in the auxiliary mounting housing 30 of the isolated organ perfusion system in an embodiment of the present invention, and fig. 7 illustrates another view-point structural diagram of a consumable assembled in the auxiliary mounting housing 30 of the isolated organ perfusion system in an embodiment of the present invention. Further, the isolated organ perfusion system further includes a first clamp 51, a second clamp 52, a third clamp 53, a fourth clamp 54 and a fifth clamp disposed on the auxiliary mounting housing 30. The hemodialyzer 41 is detachably mounted on the first jig 51, the membrane lung 42 is detachably mounted on the second jig 52, the pH monitor 43 is detachably mounted on the third jig 53, the thrombolytic filter 44 is detachably mounted on the fourth jig 54, and the leukocyte filter 57 is detachably mounted on the fifth jig. So, hemodialyzer 41, membrane lung 42, pH monitor 43, microembolus filter 44 all have corresponding anchor clamps to carry out the centre gripping fixed with leukocyte filter 57, conveniently carry out the installation of single consumptive material and dismantle the change work.

Referring to fig. 4 to 7, further, the first clamp 51 includes two first clamping plates 511 oppositely disposed on the auxiliary mounting shell 30. The first clamping plate 511 is provided with a first arc-shaped face adapted to the side wall of the hemodialyzer 41. The second clamp 52 includes two second clamping plates 521 oppositely disposed on the auxiliary mounting case 30. The second clamping plate 521 is provided with a second arc-shaped surface adapted to the side wall of the membrane lung 42. The third clamp 53 includes two third clamping plates 531 oppositely disposed on the auxiliary mounting case 30. The third clamping plate 531 is provided with a third arc-shaped surface adapted to the side wall of the PH monitor 43. The fourth fixture 54 includes a supporting plate 541 disposed on the auxiliary mounting housing 30, two arc-shaped holes 542 disposed on the supporting plate 541, and a through hole 543 correspondingly communicated with an end of the arc-shaped hole 542. The two first locking structures 441 on the bottom surface of the micro-bolt filter 44 are arranged in one-to-one correspondence with the two through holes 543, the first locking structures 441 can penetrate through the through holes 543 and can move along the arc-shaped holes 542, and the size of the buckling plate area of the first locking structures 441 is larger than the width of the arc-shaped holes 542.

Thus, the first arc surfaces of the two first clamping plates 511 are respectively clamped on the opposite side walls of the hemodialyzer 41, so that the first clamp 51 can clamp and fix the hemodialyzer 41. The second arc-shaped surfaces of the two second clamping plates 521 are respectively clamped on the opposite side walls of the membrane lung 42, so that the second clamp 52 can clamp and fix the membrane lung 42. The third arc-shaped surfaces of the two third clamping plates 531 are respectively clamped on the opposite side walls of the PH monitor 43, so that the PH monitor 43 can be clamped and fixed by the third clamps 53.

It should be noted that the width of the arc-shaped hole 542 refers to the distance between the inner circle and the outer circle of the arc-shaped hole 542, and when the area of the buckle plate of the first locking structure 441 is greater than the width of the arc-shaped hole 542, the supporting plate 541 has a limiting effect on the buckle plate of the first locking structure 441, that is, the micro-bolt filter 44 can be fixed on the fourth fixture 54, when the micro-bolt filter 44 needs to be detached from the fourth fixture 54, the micro-bolt filter 44 is rotated to align the first locking structure 441 of the micro-bolt filter 44 with the through hole 543, the micro-bolt filter 44 is moved upward, and the first locking structure 441 of the micro-bolt filter 44 passes through the through hole 543.

It should be noted that, the models of the leukocyte filters 57 are different, and the corresponding shapes are different, so that the shape of the fifth fixture can be designed adaptively according to the different models of the leukocyte filters 57, which is not described herein again.

Referring to fig. 16, fig. 16 is a simplified schematic diagram of an ex vivo organ perfusion system according to an embodiment of the present invention. In one embodiment, the isolated organ perfusion system further comprises a centrifugal pump 45, a first peristaltic pump 46, and a waste bag 47. The liquid inlet end of the centrifugal pump 45 is communicated with the liquid storage container 20 through a pipeline, the liquid outlet end of the centrifugal pump 45 is communicated with the liquid inlet end of the membrane lung 42 through a pipeline, the liquid outlet end of the membrane lung 42 is used for being connected with the isolated organ through a pipeline, and the liquid storage container 20, the centrifugal pump 45, the membrane lung 42 and the isolated organ form a perfusion circulation main path.

In addition, the liquid inlet end of the first peristaltic pump 46 is communicated with the liquid storage container 20 through a pipeline, the liquid outlet end of the first peristaltic pump 46 is communicated with the liquid inlet end of the hemodialyzer 41 through a pipeline, the liquid outlet end of the hemodialyzer 41 is communicated with the liquid storage container 20 through a pipeline, the waste discharge end of the hemodialyzer 41 is communicated with the waste liquid bag 47 through a pipeline, the liquid storage container 20, the first peristaltic pump 46 and the hemodialyzer 41 form a filtration circulation auxiliary path, the leukocyte filter 57 is arranged on the perfusion circulation main path or the filtration circulation auxiliary path, and the micro-suppository filter 44 is arranged on the perfusion circulation main path or the filtration circulation auxiliary path.

Referring to fig. 16, further, a leukocyte filter 57 is disposed on the pipeline between the first peristaltic pump 46 and the hemodialyzer 41.

Referring to fig. 16, further, the isolated organ perfusion system further includes a first pressure sensor 48 and a second pressure sensor 49. The first pressure sensor 48 is disposed at the outlet or inlet end of the leukocyte filter 57, and the second pressure sensor 49 is disposed at the outlet end of the membrane lung 42. Therefore, the first pressure sensor 48 can sense the pressure of the liquid outlet end or the liquid inlet end of the leukocyte filter 57 correspondingly, and can judge whether the leukocyte filter 57 is blocked according to the pressure, so that the degree of automation is greatly improved without manual judgment. In order to determine whether the leukocyte filter 57 is clogged, the first pressure sensor 48 is provided at both the inlet end and the outlet end of the leukocyte filter 57.

In addition, the second pressure sensor 49 can be used to detect the perfusion pressure of the membrane lung 42, because the human lung is pressure-demanding during respiration, and in order to meet the pressure value of the human true respiration, the perfusion pressure of the outlet end of the membrane lung 42 is detected by the second pressure sensor 49. If the pressure value at the beginning stage of the fluid outlet end of the membrane lung 42 is normal, and the perfusion pressure value at the later stage is abnormal, the perfusion effect of the lung can be judged.

Referring to fig. 6, 8 to 10, fig. 8 is a schematic structural view illustrating an isolated organ perfusion system according to an embodiment of the present invention, wherein the reservoir 20 is provided with a first pressure sensor 48 and a second pressure sensor 49, fig. 9 is an enlarged structural view of fig. 8 at a, and fig. 10 is a schematic structural view illustrating an isolated organ perfusion system according to an embodiment of the present invention, wherein the reservoir 20 is not provided with the first pressure sensor 48 and the second pressure sensor 49. Further, the isolated organ perfusion system further comprises a first sensor clamp 55 and a second sensor clamp 56. The first sensor clamp 55 is mounted on the auxiliary mounting case 30 or on the outer sidewall of the liquid storage container 20, and the first pressure sensor 48 is detachably mounted on the first sensor clamp 55. The second sensor clamp 56 is mounted on the outer side wall of the liquid storage container 20, and the second pressure sensor 49 is detachably mounted on the second sensor clamp 56. Therefore, the first pressure sensor 48 and the second pressure sensor 49 are disposable consumables, which is convenient for disassembly, assembly and replacement and convenient for operation. In addition, the second pressure sensor 49 is installed on the outer sidewall of the liquid storage container 20, that is, the artery outlet of the isolated organ is closer to the inside of the liquid storage container 20, so that the detected perfusion pressure is more accurate.

Further, the first sensor holder 55 includes a base plate 551 and two L-shaped restriction plates 552 connected to opposite sides of the base plate 551. The bottom plate 551 is installed on the auxiliary mounting shell 30 or on the outer side wall of the liquid storage container 20, the L-shaped limiting plate 552 is provided with a strip-shaped opening 553, the L-shaped limiting plate 552 is in limited fit with the seat plate 481 of the first pressure sensor 48 to prevent the seat plate 481 from moving in the direction perpendicular to the surface of the bottom plate 551, the seat plate 481 can slide along the surface of the bottom plate 551, the seat plate 481 is provided with a mounting hole 482 corresponding to the strip-shaped opening 553, and the seat plate 481 is installed on the L-shaped limiting plate 552 by passing the strip-shaped opening 553 through the mounting piece and the mounting. Thus, the first pressure sensor 48 can be easily mounted on the first sensor holder 55 while the mounting position on the first sensor holder 55 is adjustable.

In addition, the structure of the second sensor holder 56 is the same as that of the first sensor holder 55, and the description thereof is omitted. Since the height position of the second pressure sensor 49 can be adjusted on the second sensor holder 56, the height position of the second pressure sensor 49 can be adjusted to be consistent with the height position of the perfusion inlet of the pulmonary artery, so that the detection is more accurate.

Referring to fig. 3 and 7, in an embodiment, the auxiliary mounting shell 30 is provided with a second locking structure 31 on a wall thereof, the outer bag 10 is provided with a locking hole 12 corresponding to the second locking structure 31 on a wall thereof, and the second locking structure 31 is disposed in the locking hole 12. In this manner, it is convenient to detachably mount the auxiliary mounting case 30 in the outer bag 10.

Referring to fig. 10, in one embodiment, the isolated organ perfusion system further includes a communicating tube 61 and a liquid level sensor 62. Communicating pipe 61 is located outside liquid storage container 20, and the bottom of communicating pipe 61 is linked together with liquid storage container 20, and level sensor 62 sets up on communicating pipe 61, and level sensor 62 is used for acquireing the liquid level height on communicating pipe 61. So, the perfusate in the stock solution container 20 enters into communicating pipe 61 through the bottom of communicating pipe 61, and the liquid level height in communicating pipe 61 is the liquid level height of stock solution container 20 promptly, because the bubble on the perfusate surface of stock solution container 20 can't enter into communicating pipe 61 in, therefore level sensor 62 can acquire the liquid level height in communicating pipe 61 comparatively accurately, promptly can acquire the liquid level height in stock solution container 20, thereby can acquire whether the perfusate capacity in stock solution container 20 is in the scope of predetermineeing comparatively accurately.

Further, the liquid level sensor 62 is a photo sensor, the photo sensor is disposed outside the communication pipe 61, and the communication pipe 61 is a transparent pipe or a translucent pipe. So, level sensor 62 need not with the perfusate contact in the communicating pipe 61, can not lead to polluting the perfusate to level sensor 62 can reuse, need not regard as disposable consumptive material, makes device cost reduction. It is understood that the level sensor 62 may be other types of sensors, such as ultrasonic sensors, and is not limited thereto.

Further, the top end of the communicating tube 61 is communicated with the liquid storage container 20; alternatively, the wall of the communication pipe 61 is provided with scale marks. Thus, after the top end of the communication pipe 61 is communicated with the liquid storage container 20, the perfusion fluid in the liquid storage container 20 is not discharged outside through the top end of the communication pipe 61. In addition, after the scale marks are arranged on the tube wall of the communicating tube 61, the liquid level height of the liquid storage container 20 can be observed through the scale marks, and the use is convenient.

Referring to fig. 11 to 13, fig. 11 is a schematic structural diagram of an ex-vivo organ perfusion system according to an embodiment of the present invention, fig. 12 is an enlarged structural diagram of fig. 11 at B, and fig. 13 is a schematic structural diagram of a portion of the ex-vivo organ perfusion system according to an embodiment of the present invention after being cut open. Further, the middle part of the bottom wall of the liquid storage container 20 is raised upwards to form a trapezoid boss 21, and the area of the top surface of the trapezoid boss 21 is smaller than that of the bottom surface of the trapezoid boss 21. So, the interval width of the space region that trapezoidal boss 21's side and the lateral wall of stock solution container 20 enclose narrows down gradually from last, can realize the in-process that the perfusate in the stock solution container 20 outwards discharged like this, the perfusate assembles in the bottom region of stock solution container 20 gradually to discharge outwards through the liquid outlet 22 of stock solution container 20 bottom, it is comparatively complete to discharge the effect, and it is less to remain the volume on the diapire wall of stock solution container 20.

Referring to fig. 14 and 15, fig. 14 is a schematic sectional view of another part of an isolated organ perfusion system according to an embodiment of the present invention, and fig. 15 is an enlarged view of fig. 14 at C. It should be noted that the bottom wall of the liquid storage container 20 is generally provided with two liquid outlets 22, for example, the two liquid outlets 22 are generally provided, one of the liquid outlets 22 is connected to a centrifugal pump 45 of the main filling cycle path through, for example, a joint 23, and when the centrifugal pump 45 is operated, the filling liquid in the liquid storage container 20 is pumped out through one of the liquid outlets 22; the other of the outlet ports 22 is connected, for example, by a connector 23, to a first peristaltic pump 46 of the filter circuit, the first peristaltic pump 46 being operable to draw perfusion fluid from the reservoir 20 outwardly through the other of the outlet ports 22. The perfusion liquid is easy to generate vortex in the liquid storage container 20 in the process of being drawn out through the liquid outlet 22, so that bubbles are generated and mixed in the perfusion liquid, and adverse effects are caused to the isolated organ.

Referring to fig. 13 to 15, further, the isolated organ perfusion system further includes a diversion frame 63. The diversion frame 63 is disposed in the liquid storage container 20 and above the liquid outlet 22 of the liquid storage container 20. Specifically, the projection of the diversion frame 63 on the bottom wall of the liquid storage container 20 covers the liquid outlet 22. So, under the blocking effect of water conservancy diversion frame 63, the perfusate of stock solution container 20 upper portion department can not directly discharge outwards through the liquid outlet 22 of stock solution container 20 bottom department, can avoid producing the swirl in the stock solution container 20 like this, also can effectively restrain and produce the bubble in the perfusate or sneak into the air.

Referring to fig. 13 to 15, in a specific embodiment, a central portion of a bottom wall of the liquid storage container 20 is upwardly protruded to form a trapezoid boss 21, a top surface area of the trapezoid boss 21 is smaller than a bottom surface area of the trapezoid boss 21, and the liquid outlet 22 of the liquid storage container 20 is located at an outer peripheral portion of the bottom wall of the liquid storage container 20. The isolated organ perfusion system further comprises a flow guide frame 63. The diversion frame 63 is disposed between the side surface of the trapezoid boss 21 and the side wall of the liquid storage container 20, the diversion frame 63 is located above the liquid outlet 22 of the liquid storage container 20, and a gap 633 is disposed between the diversion frame 63 and the side surface of the trapezoid boss 21 or between the diversion frame 63 and the side wall of the liquid storage container 20. So, under the blocking effect of water conservancy diversion frame 63, the perfusate of stock solution container 20 upper portion department can not directly outwards discharge through the liquid outlet 22 of stock solution container 20 bottom department, but enters into the lower region of water conservancy diversion frame 63 through clearance 633 and outwards discharges through liquid outlet 22, can avoid producing the swirl in the stock solution container 20 like this better, also can effectively restrain the producing bubble in the perfusate or sneak into the air better. Specifically, the baffle frame 63 includes a top plate 631 and leg plates 632 located at two sides of the top plate 631, the leg plates 632 are connected to the bottom wall of the liquid storage container 20, and the leg plates 632 at two sides support the top plate 631 so that the top plate 631 and the bottom wall of the liquid storage container 20 form a gap. The top plate 631 is located above the liquid outlet 22 of the liquid storage container 20, and the top plate 631 prevents the perfusion liquid at the upper portion of the liquid storage container 20 from directly discharging outwards through the liquid outlet 22 at the bottom of the liquid storage container 20, but enters the lower region of the diversion frame 63 through the gap 633 and is discharged outwards through the liquid outlet 22.

Referring to fig. 11, further, the isolated organ perfusion system further includes a first cover 11. The first cover 11 is detachably disposed at the mouth of the outer bag 10, and the first cover 11 is located above the auxiliary mounting case 30.

Referring to fig. 11, further, the isolated organ perfusion system further includes a support 24 and a second cover 25. The support 24 is arranged on the inner wall of the liquid storage container 20, and the support 24 is used for supporting and placing an isolated organ. The second lid 25 is detachably provided to the mouth of the liquid storage container 20.

It should be noted that, in the infringement comparison, the "flow guiding frame 63" may be a part of the "liquid storage container 20", that is, the "flow guiding frame 63" and the "other part of the liquid storage container 20" are integrally manufactured; or a separate component which can be separated from the other parts of the liquid storage container 20, namely the flow guiding frame 63 can be manufactured separately and then combined with the other parts of the liquid storage container 20 into a whole.

It should be noted that, in infringement comparison, the "bracket 24" may be a "part of the reservoir 20", that is, the "bracket 24" is integrally formed with "other parts of the reservoir 20"; the "holder 24" may be manufactured separately from the "other portion of the reservoir 20" and then integrated with the "other portion of the reservoir 20" as a single unit.

The perfusate is, for example, a mixed solution of low-molecular dextran-40, sodium chloride, potassium chloride, calcium chloride, glucose, etc., and the specific components of the perfusate are not limited herein.

In addition, when the perfusate circularly flows in the perfusion circulation main path, the perfusate can be continuously perfused to the isolated organ, so that the isolated organ can be preserved for a long time in a normal temperature environment, and the problems of tissue cell damage, organ ischemia and the like caused by a low-temperature environment are effectively avoided; meanwhile, the perfusion fluid is driven to circularly flow by the power pump, so that thrombus, inflammatory factors or other foreign matter harmful substances in the isolated organ can be effectively removed, and functional vessels of the isolated organ can be maintained to be smooth, pulmonary edema can be improved, oxygenation capacity of the heart and lung can be improved, the isolated organ can be subjected to repair treatment, the risk of postoperative graft failure is reduced, and the utilization rate of the isolated organ and the success rate of transplantation operation can be effectively improved.

In addition, the fluid of the fluid infusion bag 65 is used for supplementing trace substances, such as sodium element, potassium element, etc., which are needed and consumed by the isolated organ, and is not limited herein.

The isolated organ perfusion system can realize that perfusion fluid in the liquid storage container 20 enters the isolated organ through the membrane lung 42 and circularly flows back to the liquid storage container 20 from the isolated organ under the power action of the centrifugal pump 45. Under the power action of the first peristaltic pump 46, the perfusate in the liquid storage container 20 can be filtered by the hemodialyzer 41, and after the perfusate is filtered by the hemodialyzer 41, impurities such as particles, heavy metals and the like can be filtered; wherein, because the filtering circulation auxiliary road is provided with the leucocyte filter 57, on one hand, the leucocyte filter 57 can filter the leucocyte in the perfusate, thereby effectively reducing the damage of the isolated organ caused by perfusate perfusion, meanwhile, the occurrence of rejection reaction of organ transplantation can be effectively delayed, the utilization rate of donor organs and the success rate of transplantation operation are further improved, on the other hand, since the leukocyte filter 57 is disposed on the secondary path of the filtration cycle, rather than on the primary path of the perfusion cycle, thus, when the leukocyte filter 57 is clogged due to a long-term operation (for example, 10 hours), the leukocyte filter 57 may cause the clogging of the filter circulation path, and the main perfusion circulation path can not be blocked, and at the moment, the main perfusion circulation path can still continue to work, can continuously protect the isolated organ, and can replace the leukocyte filter 57 on the filtering circulation path in time.

Referring to fig. 16, a micro-suppository filter 44 is further disposed on the primary perfusion cycle path or the secondary filtration cycle path. Thus, the micro-suppository filter 44 is used for filtering various micro-suppositories in the perfusate, preventing the micro-blood vessels of the isolated organ from being embolized due to various micro-suppositories such as thrombus or air embolism, effectively improving the blood perfusion of the micro-blood vessels of the human body, and further improving the utilization rate of the donor organ and the success rate of the transplantation operation.

Referring to fig. 16, further, a micro-suppository filter 44 is disposed in the line between the centrifugal pump 45 and the membrane lung 42. Thus, the perfusate flowing out of the centrifugal pump 45 enters the membrane lung 42 after being filtered by the micro-suppository filter 44, so that the phenomenon that the membrane lung 42 is blocked due to the fact that the micro-suppository enters the membrane lung 42 can be avoided.

Referring to fig. 16, further, a leukocyte filter 57 is disposed on the pipeline between the first peristaltic pump 46 and the hemodialyzer 41. So, leukocyte filter 57's the position of setting is comparatively reasonable, because when leukocyte filter 57 takes place to block up, the perfusate can not reentrant hemodialyzer 41 and cause harmful effects to hemodialyzer 41, and first peristaltic pump 46 still can provide power promotion perfusate and move forward in addition. Of course, alternatively, the leukocyte filter 57 can be disposed on the line from the reservoir 20 to the first peristaltic pump 46, or on the line from the hemodialyzer 41 back to the reservoir 20.

Referring to fig. 16, further, the isolated organ perfusion system further includes a first switch valve 64. The number of the first switch valves 64 and the number of the leukocyte filters 57 are two or more, the two or more leukocyte filters 57 are arranged in parallel on the auxiliary filtration circulation path, the two or more first switch valves 64 and the two or more leukocyte filters 57 are arranged in one-to-one correspondence, and the first switch valves 64 are used for controlling whether the corresponding leukocyte filters 57 are connected to the auxiliary filtration circulation path. Specifically, in this embodiment, there are two leukocyte filters 57, and when one of the leukocyte-packing filters is connected to the filtration cycle bypass, the corresponding first on-off valve 64 is in an open state, the other leukocyte filter 57 is not connected to the filtration cycle bypass, and the corresponding first on-off valve 64 of the other leukocyte filter 57 is in a closed state. When one of the leukocyte filters 57 is blocked, the corresponding first switch valve 64 is closed, and the corresponding first switch valve 64 of the other leukocyte filter 57 is opened, so that the other leukocyte filter 57 is connected to the filtration circulation auxiliary circuit, and the filtration circulation auxiliary circuit can still perform the function of circularly filtering the perfusion fluid.

Referring to fig. 16, the first on-off valve 64 is an electric pinch valve or a manual pinch valve for controlling the opening of the branch of the leukocyte filter 57. Thus, the electric pinch valve or the manual pinch valve is clamped on the branch where the leukocyte filter 57 is located, and the flow rate of the branch where the leukocyte filter 57 is located and whether the branch where the leukocyte filter 57 is located is connected to the filtration cycle sub-circuit are controlled by controlling the opening degree of the branch. In addition, the electric pinch valve or the manual pinch valve can not contact the perfusion liquid, so that the perfusion liquid can be prevented from being polluted, the circulation utilization can be realized, and disposable consumables are not required.

In one embodiment, the first pressure sensors 48 are two or more, and the two or more first pressure sensors 48 are disposed in one-to-one correspondence with and in series with the two or more leukocyte filters 57. Therefore, the first pressure sensor 48 can sense the pressure of the branch of the corresponding leukocyte filter 57, and can judge whether the corresponding leukocyte filter 57 is blocked according to the pressure, so that manual judgment is not needed, and the automation degree is greatly improved.

In one embodiment, the controller is electrically connected to the first pressure sensor 48 and the first on-off valve 64, respectively. In this way, when the controller determines that the leukocyte filter 57 corresponding to the first pressure sensor 48 is blocked according to the first pressure sensor 48, the controller controls the other first switch valve 64 to be opened, and opens and connects the branch where the other first switch valve 64 is located to the filtration cycle auxiliary circuit.

In one embodiment, the isolated organ perfusion system further comprises a fluid bag 65 and a second on-off valve 66. Fluid infusion bag 65 is linked together through pipeline and stock solution container 20, and second ooff valve 66 sets up on fluid infusion bag 65 is connected to the pipeline of stock solution container 20, and level sensor 62 is used for acquireing stock solution container 20's liquid level height, and second ooff valve 66, level sensor 62 all are connected with controller electric connection. So, the controller senses the corresponding aperture size of controlling second ooff valve 66 of the liquid level height information of liquid storage container 20 according to level sensor 62 to control fluid infusion bag 65 and give the fluid infusion speed and the fluid infusion volume size of liquid storage container 20, make the perfusate volume in the liquid storage container 20 maintain the balance. Specifically, the second on-off valve 66 is, for example, an electric pinch valve. The electric pinch valve is clamped on a pipeline of the fluid infusion bag 65 connected to the liquid storage container 20, and controls the fluid infusion flow of the fluid infusion bag 65 by controlling the opening. In addition, the electric pinch valve can not contact the supply liquid, so that the supply liquid can be prevented from being polluted, the supply liquid can be recycled, and disposable consumables are not needed.

In one embodiment, the pH monitor 43 is electrically connected to the controller, and the pH monitor 43 is used to obtain the pH of the perfusate. The PH monitor 43 may be disposed on the perfusion circulation main path or the filtration circulation auxiliary path, and is not limited herein. In addition, the PH monitor 43 can monitor the PH condition of the perfusate on line in real time, replaces manual detection, and has higher automation degree.

Alternatively, when the pH monitor 43 detects a decrease in the pH of the perfusate that is less than the predetermined range, a pH adjusting fluid is added to the fluid replacement bag 65 so as to increase the pH of the perfusate.

Referring to fig. 16, the isolated organ perfusion apparatus may further include a conditioning fluid bag (not shown), in which a PH conditioning fluid is filled, and the conditioning fluid bag is connected to the reservoir 20 through a pipeline. A third on/off valve (not shown) is disposed on a pipeline connecting the regulating fluid bag to the fluid storage container 20, and the third on/off valve is electrically connected to the controller. When the pH monitor 43 detects that the pH of the perfusate is reduced and is smaller than the preset range, the controller correspondingly controls the third switch valve to act, and the pH adjusting liquid in the adjusting liquid bag is conveyed into the liquid storage container 20 so as to increase the pH of the perfusate and maintain the pH of the perfusate within the preset range. On the contrary, when the PH monitor 43 detects that the PH value of the perfusate is increased and is greater than the preset range, the controller correspondingly controls the third on/off valve to close, and the liquid supplementing is not performed.

In one embodiment, the membrane lung 42 is provided with a mixed gas port for communicating with a line of a mixed gas source (not shown in the drawings). The perfusate combines with the gas mixture in the membrane lung 42 to form an oxygenated perfusate to ensure that the perfusate flowing into the artery has sufficient oxygen content. In addition, the membrane lung 42 is communicated with a heat exchange device through a heat exchange tube to form a circulating heat exchange loop, and the perfusate exchanges heat with a heat exchange medium of the circulating heat exchange loop in the membrane lung 42 so as to keep the temperature of the perfusate proper to the isolated organ.

In one embodiment, the ex vivo organ perfusion system further comprises a second peristaltic pump 67. A second peristaltic pump 67 is provided on the tubing between the waste end of the hemodialyzer 41 and the waste fluid bag 47. The second peristaltic pump 67 can provide enough power to drive the waste liquid in the hemodialyzer 41 to be discharged into the waste liquid bag 47, so that the problem that the blood filter is not smooth in waste liquid discharge due to insufficient pressure difference is avoided.

In one embodiment, the ex vivo organ perfusion system further comprises a first temperature sensor 68 and a second temperature sensor 69. The first temperature sensor 68 is disposed on the pipeline of the membrane lung 42 connected to the isolated organ, and the first temperature sensor 68 is used for acquiring the temperature at the fluid outlet end of the membrane lung 42. In addition, a second temperature sensor 69 is disposed on the reservoir 20 for obtaining the temperature of the perfusion fluid in the reservoir 20. In addition, the isolated organ perfusion system further includes a flow sensor 70. The flow sensor 70 is arranged on the pipeline between the centrifugal pump 45 and the microembolus filter 44, and the flow sensor 70 can acquire the flow of the perfusate on the pipeline between the centrifugal pump 45 and the microembolus filter 44 and can judge whether the centrifugal pump 45, the microembolus filter 44 and the membrane lung 42 work normally according to the flow. In addition, the flow sensor 70 can be used to control the rotation speed of the centrifugal pump 45, so as to ensure that the rotation speed of the centrifugal pump 45 is within a preset range.

The technical features of the embodiments described above may be arbitrarily combined, and for the sake of brevity, all possible combinations of the technical features in the embodiments described above are not described, but should be considered as being within the scope of the present specification as long as there is no contradiction between the combinations of the technical features.

The above-mentioned embodiments only express several embodiments of the present invention, and the description thereof is more specific and detailed, but not construed as limiting the scope of the invention. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the inventive concept, which falls within the scope of the present invention. Therefore, the protection scope of the present patent shall be subject to the appended claims.

In the description of the present invention, it is to be understood that the terms "central," "longitudinal," "lateral," "length," "width," "thickness," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," "clockwise," "counterclockwise," "axial," "radial," "circumferential," and the like are used in the orientations and positional relationships indicated in the drawings for convenience in describing the invention and to simplify the description, and are not intended to indicate or imply that the referenced device or element must have a particular orientation, be constructed and operated in a particular orientation, and are not to be considered limiting of the invention.

Furthermore, the terms "first", "second" and "first" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one such feature. In the description of the present invention, "a plurality" means at least two, e.g., two, three, etc., unless specifically limited otherwise.

In the present invention, unless otherwise expressly stated or limited, the terms "mounted," "connected," "secured," and the like are to be construed broadly and can, for example, be fixedly connected, detachably connected, or integrally formed; can be mechanically or electrically connected; they may be directly connected or indirectly connected through intervening media, or they may be connected internally or in any other suitable relationship, unless expressly stated otherwise. The specific meanings of the above terms in the present invention can be understood by those skilled in the art according to specific situations.

In the present invention, unless otherwise expressly stated or limited, the first feature "on" or "under" the second feature may be directly contacting the first and second features or indirectly contacting the first and second features through an intermediate. Also, a first feature "on," "over," and "above" a second feature may be directly or diagonally above the second feature, or may simply indicate that the first feature is at a higher level than the second feature. A first feature being "under," "below," and "beneath" a second feature may be directly under or obliquely under the first feature, or may simply mean that the first feature is at a lesser elevation than the second feature.

It will be understood that when an element is referred to as being "secured to" or "disposed on" another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present. The terms "vertical," "horizontal," "upper," "lower," "left," "right," and the like as used herein are for illustrative purposes only and do not denote a unique embodiment.

Claims

1. An ex vivo organ perfusion system, comprising:

the blood dialyzer comprises an outer sleeve package, a liquid storage container, an auxiliary installation shell, a hemodialyzer and a membrane lung, wherein the liquid storage container is arranged in the outer sleeve package, the liquid storage container is used for installing perfusate, the auxiliary installation shell is detachably arranged in the outer sleeve package, and the hemodialyzer and the membrane lung are detachably arranged in the auxiliary installation shell.

2. The isolated organ perfusion system of claim 1, further comprising a PH monitor, a micro-plug filter, and a leukocyte filter, wherein the PH monitor, the micro-plug filter, and the leukocyte filter are removably mounted in the auxiliary mounting housing.

3. The isolated organ perfusion system of claim 2, further comprising first, second, third, fourth, and fifth clamps disposed on the auxiliary mounting housing; the hemodialyzer is detachably arranged on the first clamp, the membrane lung is detachably arranged on the second clamp, the pH monitor is detachably arranged on the third clamp, the micro-suppository filter is detachably arranged on the fourth clamp, and the leukocyte filter is detachably arranged on the fifth clamp.

4. The isolated organ perfusion system of claim 3, wherein the first clamp comprises two first clamping plates oppositely disposed on the auxiliary mounting housing, the first clamping plates having first arcuate surfaces conforming to the side walls of the hemodialyzer; the second clamp comprises two second clamping plates which are oppositely arranged on the auxiliary mounting shell, and the second clamping plates are provided with second arc-shaped surfaces which are matched with the side walls of the membrane lungs; the third clamp comprises two third clamping plates which are oppositely arranged on the auxiliary mounting shell, and the third clamping plates are provided with third arc-shaped surfaces which are matched with the side walls of the PH monitor; fourth anchor clamps including set up in backup pad on the supplementary installation shell, be equipped with relative and coaxial two arc holes in the backup pad, and with the via hole of the tip correspondence intercommunication in arc hole, two first latch structures and two on the micro-bolt filter bottom surface the via hole one-to-one sets up, first latch structure can pass the via hole can along the arc hole removes, the buckle area size of first latch structure is greater than the width in arc hole.

5. The ex-vivo organ perfusion system according to claim 2, further comprising a centrifugal pump, a first peristaltic pump, and a waste fluid bag; the liquid inlet end of the centrifugal pump is communicated with the liquid storage container through a pipeline, the liquid outlet end of the centrifugal pump is communicated with the liquid inlet end of the membrane lung through a pipeline, the liquid outlet end of the membrane lung is used for being connected with an isolated organ through a pipeline, and the liquid storage container, the centrifugal pump, the membrane lung and the isolated organ form a perfusion circulation main path;

6. The isolated organ perfusion system of claim 5, wherein the leukocyte cell filter is disposed on tubing between the first peristaltic pump and the hemodialyzer.

7. The isolated organ perfusion system of claim 5, further comprising a first pressure sensor disposed at the outlet or inlet end of the leukocyte filter, and a second pressure sensor disposed at the outlet end of the membrane lung.

8. The ex vivo organ perfusion system of claim 7, further comprising a first sensor clamp and a second sensor clamp; the first sensor clamp is arranged on the auxiliary mounting shell or the outer side wall of the liquid storage container, and the first pressure sensor is detachably arranged on the first sensor clamp; the second sensor clamp is arranged on the outer side wall of the liquid storage container, and the second pressure sensor is detachably arranged on the second sensor clamp.

9. The isolated organ perfusion system of claim 8, wherein the first sensor clamp comprises a base plate and two L-shaped limiting plates connected to opposite sides of the base plate; the bottom plate is arranged on the auxiliary mounting shell or on the outer side wall of the liquid storage container, a strip-shaped opening is formed in the L-shaped limiting plate, the L-shaped limiting plate is in limiting fit with the seat plate of the first pressure sensor to prevent the seat plate from moving in the direction perpendicular to the surface of the bottom plate, the seat plate can slide along the surface of the bottom plate, a mounting hole corresponding to the strip-shaped opening is formed in the seat plate, and the seat plate penetrates through the strip-shaped opening through a mounting piece and is arranged on the L-shaped limiting plate.

10. The isolated organ perfusion system according to any one of claims 1-9, wherein a second locking structure is provided on a wall of the auxiliary mounting housing, a locking hole corresponding to the second locking structure is provided on a wall of the outer sheath, and the second locking structure is provided in the locking hole;

the isolated organ perfusion system further comprises a support and a second cover body, the support is arranged on the inner wall of the liquid storage container, and the support is used for supporting and placing an isolated organ; the second cover body is arranged at the opening part of the liquid storage container in an openable way;

isolated organ perfusion system still includes communicating pipe and level sensor, communicating pipe is located outside the stock solution container, the bottom of communicating pipe with the stock solution container is linked together, level sensor set up in communicating pipe is last, level sensor is used for acquireing liquid level height on communicating pipe.