CN114357844A - In-vitro device and system for analyzing action of pulsating blood flow on substances in fluid - Google Patents
In-vitro device and system for analyzing action of pulsating blood flow on substances in fluid Download PDFInfo
- Publication number
- CN114357844A CN114357844A CN202210030231.1A CN202210030231A CN114357844A CN 114357844 A CN114357844 A CN 114357844A CN 202210030231 A CN202210030231 A CN 202210030231A CN 114357844 A CN114357844 A CN 114357844A
- Authority
- CN
- China
- Prior art keywords
- blood flow
- flow
- fluid
- substance
- waveform
- 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.)
- Granted
Links
Images
Classifications
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06F—ELECTRIC DIGITAL DATA PROCESSING
- G06F30/00—Computer-aided design [CAD]
- G06F30/20—Design optimisation, verification or simulation
- G06F30/28—Design optimisation, verification or simulation using fluid dynamics, e.g. using Navier-Stokes equations or computational fluid dynamics [CFD]
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06F—ELECTRIC DIGITAL DATA PROCESSING
- G06F30/00—Computer-aided design [CAD]
- G06F30/20—Design optimisation, verification or simulation
- G06F30/23—Design optimisation, verification or simulation using finite element methods [FEM] or finite difference methods [FDM]
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06F—ELECTRIC DIGITAL DATA PROCESSING
- G06F2113/00—Details relating to the application field
- G06F2113/08—Fluids
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06F—ELECTRIC DIGITAL DATA PROCESSING
- G06F2119/00—Details relating to the type or aim of the analysis or the optimisation
- G06F2119/14—Force analysis or force optimisation, e.g. static or dynamic forces
Abstract
An in-vitro device and system for analyzing the action of pulsating blood flow on substances in fluid belong to the technical field of hemodynamics and biomechanics. Based on the fluid mechanics principle, the shape of the flow channel of the device is designed by using a topological optimization method, so that the spatial distribution waveform of the flow velocity on the axial line of the flow channel is similar to the blood flow waveform. When a substance circularly flows through a device flow passage, the flow velocity of fluid around the substance dynamically changes, the flow velocity waveform with space change in the flow passage is converted into the waveform with time change sensed by the substance, the simulation of a pulsatile blood flow environment is realized, and the rule and the mechanism of the flow velocity waveform influencing cells and medicament macromolecules are explored. By adjusting the shape of the flow channel boundary, the in-vitro simulation of the blood flow pulsation waveform under different physiological and pathological conditions is flexibly realized, the requirements on the precision of a flow pump and circulating system elements are greatly reduced, the device has low processing cost and good observability, and is expected to provide a convenient and efficient experimental device and platform for the research of cardiovascular diseases and the design of drug carriers in blood.
Description
Technical Field
The invention belongs to the technical field of hemodynamics and biomechanics, and relates to a method for simulating a complex pulsating blood flow environment through an in-vitro device based on the hydrodynamics principle and researching the influence of a flow velocity waveform on suspended cells (such as blood cells and tumor cells), vascular wall cells and drug macromolecules in fluid.
Background
The blood flow environment in the human body is dynamic and complex and changeable, and in a cardiac cycle, the artery blood flow velocity fluctuates along with the contraction and relaxation of ventricles; when the ventricles contract, the blood flow is accelerated to reach the peak value of the flow velocity of dozens of centimeters per second, and then the flow velocity is gradually reduced; in the post systole phase, the flow rate reaches a second peak; thereafter ventricular diastole, the flow rate decreases to the first trough; the flow rate reduced to the trough rebounds under the effect of the elastic effect of the blood vessels, recovers to a flow rate slightly lower than the second peak value, and then continuously reduces until the minimum flow rate value in the whole cardiac cycle; after which the ventricles resume contraction and proceed to the next cardiac cycle. The peak and trough values of blood flow velocity and the systolic and diastolic time of the ventricles are affected by different physiological and health conditions. For example, a woman typically has a first systolic peak slightly lower than a man, while a second systolic peak and both flow troughs are higher than a man.
The dynamically changing blood flow environment generates shear force on cells and macromolecular substances (such as drug particles) in the blood flow environment, and further influences the properties and the state of the cells and the release rule of the drug. Therefore, the research on the effect of the complex blood flow environment on cell molecules has very important significance for diagnosis and treatment of cardiovascular diseases and design of drug carriers.
Because it is difficult to observe blood flow and the state change of substances therein in vivo, early studies have mainly calculated the pressure and flow velocity in blood vessels by constructing numerical models (such as fluid-solid coupling models), and estimated the deformation of blood vessel wall cells and suspended red blood cells under the action of fluid. However, the accuracy of the calculation remains questionable due to the simplified complex blood flow and cellular properties of the numerical model. In recent years, researchers construct an extracorporeal circulation system model by using a pulse pump, a compliance chamber, a one-way valve, an adjustable resistance valve and a connecting pipeline, realize the generation of a pulse blood flow environment in an extracorporeal cell culture chamber, and study the effect of the pulse blood flow on endothelial cells. The in vitro model has few interference factors and good observability, and is expected to provide more accurate conclusion for researching the action of the shearing force of the pulsating blood flow. However, because the control of the pulse pump is complex, the adjustable precision is limited, and the formed flow velocity waveform is influenced by each element in the circulation system individually and crossly, the device system for accurately simulating the blood flow waveform in vivo cannot be successfully constructed at present, and the construction of the personalized blood flow environment cannot be realized according to different human physiological and pathological conditions; meanwhile, the pulsation pump is expensive in cost and difficult to maintain, and the wide application of the in-vitro model is limited.
Disclosure of Invention
Aiming at the problems in the prior art, the invention designs an in-vitro device system which is realized based on a common constant-speed flow pump and can flexibly simulate the flow velocity waveform of pulsatile blood flow. Firstly, designing the boundary shape of a device flow channel by a topological optimization method, so that the spatial distribution waveform of the flow velocity on the axial line along the flow channel is similar to the simulated real blood flow waveform; secondly, substances (such as cells and drug molecules) are injected into a flow channel of the device through a flow pump, when the substances flow along the central axis of the flow channel, the flow velocity waveform distributed in the flow channel in space is converted into a flow velocity waveform which changes along with time and is sensed by the substances, and the fluid shearing force applied to the substances also changes dynamically; and finally, liquid and substances are circularly and continuously filled into the device by using the flow pump, so that the periodically changed shearing force is applied to the substances in the fluid.
The technical scheme of the invention is as follows:
an extracorporeal device for analyzing the effect of pulsatile blood flow, wherein the extracorporeal device 1 comprises a sheath flow inlet 1-1, a substance inlet 1-2, a blood flow pulsatile waveform generating channel 1-3, and a fluid outlet 1-4; the two sheath inlets 1-1 are respectively connected with the initial ends of the blood flow pulsation waveform generation channels 1-3 through two sheath flow channels; the substance inlet 1-2 is positioned between the two sheath inlets 1-1 and is connected with the initial end of the blood flow pulsation waveform generation channel 1-3 through the injection channel; the tail end of the blood flow pulsation waveform generation channel 1-3 is provided with a fluid outlet 1-4; after the cell or drug macromolecules introduced from the substance inlet 1-2 flow through the injection channel, the macromolecules are focused at the center of the flow channel under the action of sheath flow, pass through the blood flow pulsation waveform generation channel 1-3, and then flow out of the chip through the fluid outlet 1-4.
Furthermore, the in-vitro device for analyzing the effect of the pulsating blood flow is mainly used for researching the effect of periodically-changed shearing force applied by the pulsating blood flow to substances (such as red blood cells, circulating tumor cells, drug macromolecules and the like) and blood vessel wall cells in the in-vitro device; specifically, the boundary shape of the blood flow pulsation waveform generation channel 1-3 is changed to enable the spatial distribution condition of the flow velocity on the axis of the flow channel to be similar to the blood flow waveform in a pulsation period in the artery, when substances such as cells, drug macromolecules and the like pass through the blood flow pulsation waveform generation channel 1-3 along the axis, the shearing force generated by the fluid on the substances is dynamically changed along with time due to the unevenly distributed flow velocity, the change condition is similar to the blood flow pulsation waveform, and therefore the stress of the substances in the simulated pulsation blood flow environment is achieved.
Furthermore, the extracorporeal device for analyzing the pulsating blood flow effect can simulate different blood flow pulsating waveforms generated under the influence of physiological and pathological conditions such as sex, age, diseases and the like by adjusting the boundary shape of the blood flow pulsating waveform generation channels 1-3, and research the rules and mechanisms of the different waveforms for influencing the properties and the states of substances.
Furthermore, the in-vitro device for analyzing the pulsating blood flow effect realizes the design of the shape of the flow channel of the device by a topological optimization method based on the fluid mechanics principle. The parallel plate flow chamber with the length and width (x and y directions) far larger than the height (z direction) is designed, because the flow velocity components in the length and width directions are far larger than the height direction components, the cross section (y-z section) of the flow channel along the height direction can be approximately treated as the same, and the average flow field in the height direction
An ideal flow field can be approximated. Therefore, the design of the three-dimensional flow channel and the calculation of the flow field can be simplified into the boundary shape of the flow channel on the x-y cross section and the flow problem of two-dimensional ideal fluid. On the x-y cross section, if the simulated blood flow velocity waveform is u0Then the flow channel shape can be obtained by solving the following optimization problem
div uρ＝0 inΩ
Wherein
Is a two-dimensional plane including all possible flow channel shapes uρIs the average flow velocity in the height direction over the x-y cross-section, p is the pressure,
is the strain rate tensor, μ is the fluid viscosity, ρ is the material density,
representing a range of desirable values of p,
mα(p) is the permeability of the fluid, generally defined as
(α and q are parameters of the optimization problem) by mα(rho) the fluid is limited to flow in a region where rho is close to 0 and cannot enter a region where rho is close to 1, k is a parameter of an optimization problem, and the existing flow waveform u is realized by adjusting the value of k0While also reducing flow energy dissipation. Combining finite elements and optimization calculationsAnd (3) solving the optimization problem by a method (such as a Newton method) to obtain the distribution of the material density rho on a two-dimensional plane, setting a region in which the rho is close to 0 as a flow channel region, and setting a region in which the rho is close to 1 as a boundary solid region, thereby realizing the design of the shape of the blood flow pulsation waveform generation channel 1-3 of the device.
Further, the extracorporeal device for analyzing the pulsating blood flow effect can be refilled into the device by the constant speed pump 2 after the fluid flows out of the device through the outlets 1 to 4, thereby realizing the liquid circulation flow and applying the periodically changing shearing force to the substance therein.
Further, the extracorporeal device for analyzing the pulsating blood flow effect is designed to have a length of the extracorporeal device 1 in the order of centimeters due to the high blood flow velocity in the artery (usually 4.9-19 cm/sec) and a pulsation period of about 1 second; in order to maintain the flow in the extracorporeal device 1 in a laminar state, the width of the extracorporeal device 1 is designed to be in the order of millimeters; the machining of the extracorporeal device 1 is achieved by precision lathing or laser cutting of PMMA.
A system for analyzing the effects of pulsatile blood flow, said system comprising an extracorporeal device 1, a constant speed pump 2, a one-way valve 3 and a catheter; the blood storage is connected with two sheath inlets 1-1 of the extracorporeal device 1 through a catheter, and the substance storage to be detected is connected with a substance inlet 1-2 of the extracorporeal device 1 through a catheter; the fluid outlet 1-4 of the extracorporeal device 1 is connected with a constant speed pump 2 and a one-way valve 3 in sequence through a conduit, and the constant speed pump 2 is used for maintaining the constant speed circulation flow of blood flow in the system. In use, blood (blood plasma) is firstly injected into the device through two sheath inlets 1-1 of the extracorporeal device 1; then connecting a sheath inflow port 1-1 of the device with a constant-speed pump 2 and a one-way valve 3 through a catheter 5, and maintaining the constant-speed circulation flow of blood in the system by using the pump; finally, substances such as cells and drug macromolecules are injected into the device through the substance inlet 1-2 of the device, and the substances flow along with the circulation of the fluid in the system.
The invention has the beneficial effects that: 1) by changing the boundary shape of the flow channel, the blood flow waveforms under different physiological and pathological influences can be flexibly simulated; 2) the waveform simulation precision is high, and the influence of a pump and circulating system elements (such as a hose, a valve, a compliance chamber and the like) is avoided; 3) the cost is low, the use is convenient, and the expensive pulse pump and the programming control of the pump are not involved; 4) fluid movement and flowing materials are easily observed.
Drawings
FIG. 1 is a schematic diagram of an in vitro device and circulatory system for analyzing the effects of pulsatile blood flow;
FIG. 2 is a top view and cross-sectional view of a flow channel for achieving a simulated pulsatile blood flow waveform; wherein, (a) is a top view and (b) is a cross-sectional view;
FIG. 3 is a top view of a flow channel and design parameters for achieving a simulated pulsatile blood flow waveform;
FIG. 4 is a graph showing the spatial distribution of flow velocity along the axis of the flow channel and the variation of flow velocity in a cycle of pulsatile blood flow in a human body;
FIG. 5 is a diagram relating to an embodiment, wherein (A) is a diagram illustrating an effect of a pulsating blood flow on cells of a blood vessel wall in the case of analyzing the pulsating blood flow using an extracorporeal device in example 1, and (B) is a diagram illustrating an effect of the pulsating blood flow on flowing blood cells in example 2.
In fig. 1: 1 an extracorporeal device; 2 a constant speed pump; 3, a one-way valve; 4, a conduit;
in fig. 2: 1-1 sheath flow inlet; 1-2 material (such as cells, drug macromolecules, etc.) inlet; 1-3 flow pulsation waveform generation flow channel; 1-4 fluid outlets; h, the height of the runner;
in fig. 3: w1、W2、W3、W4、W5、W6、W7Is the width of the flow channel; wherein W1Is the inlet flow passage width, W2Determines the second valley, W, of the heart relaxing process3Determines the first peak, W, in the systole process4Determines the second peak, W, of the systole5Determines the first valley, W, of the heart relaxing process6Determines a local peak value, W, of the flow velocity caused by the blood vessel elasticity in the diastole process7Is the outlet flow path width;
L1、L2、L3、L4、L5、L6、L7、L8、L9is a pair of different runner widthsThe length of the corresponding flow channel;
R1、R2、R3、R4、R5、R6、R7、R8is the radius of the fillet provided at the place where the turn occurs at the flow path boundary;
in fig. 4: vxIs the component of the flow velocity along the horizontal direction on the central axis of the flow channel.
Detailed Description
The following examples further illustrate the invention but are not intended to limit the invention thereto.
Example 1
An in vitro device for analyzing the pulsatile blood flow effect as shown in fig. 2 and 3 was designed, wherein the flow channel design parameters are as follows:
| W1 | 6.7mm | W2 | 8mm | W3 | 6mm |
| W4 | 8mm | W5 | 12mm | W6 | 8.3mm |
| W7 | 9mm | L1 | 30mm | L2 | 5mm |
| L3 | 1mm | L4 | 4mm | L5 | 10mm |
| L6 | 8mm | L7 | 2mm | L8 | 15mm |
| L9 | 40mm | R1 | 10mm | R2 | 1mm |
| R3 | 0.5mm | R4 | 3mm | R5 | 5mm |
| R6 | 5mm | R7 | 1mm | R8 | 5mm |
| H | 15mm |
table 1: design parameters of flow channel of apparatus in example 1
Machining a flow channel with the depth of H/2 on the two PMMA blocks by a laser cutting or precision machine tool according to the dimensions in the table 1; processing a sheath inflow port 1-1, a substance 1-2 and a fluid outlet port 1-4 into through holes on one PMMA; putting a glass sheet with the area of 2mm multiplied by 2mm and the thickness of less than 0.1mm into the other PMMA flow channel, connecting two sides of the glass sheet with PMMA through a drawing line, adjusting the position of the glass sheet in the flow channel through the drawing line to enable the glass sheet to be always positioned in the center of the cross section of the flow channel shown in (A) in the figure 5, and enabling the glass sheet to move at a constant speed from left to right or from right to left; and finally, aligning the flow channels on the two PMMA plates, and bonding the two PMMA plates together by using special plastic glue to form the in-vitro device.
Treating the upper surface and the lower surface of the glass sheet by using Fibronectin, culturing vascular endothelial cells, introducing a cell culture solution with the flow rate of 5cm/s from a sheath inflow port (1-1) when the coverage rate of the endothelial cells on the surface of the glass sheet exceeds 50%, enabling the glass sheet to move from the left side to the right side of a flow channel at a constant speed under the action of a traction line, and enabling the flow rate of the culture solution around the cells on the glass sheet to change as shown in figure 4; stopping introducing the liquid when the glass sheet reaches the right side of the flow channel, and slowly moving the glass sheet to the left side of the return channel in the static culture solution; and repeating the operation to realize the simulation of the influence of the periodic pulsating blood flow on the vascular endothelial cells.
Example 2
The in vitro device for analyzing the effect of pulsatile blood flow as shown in figures 2 and 3 was designed according to the dimensions of table 1. Specifically, flow channels with the depth of H/2 are machined on two PMMA blocks through a laser cutting or precision machine tool according to the dimensions in the table 1; processing a sheath inflow port 1-1, a substance 1-2 and a fluid outlet port 1-4 into through holes on one PMMA; and then aligning the flow channels on the two PMMA plates, and bonding the two PMMA plates together by using special plastic glue to form the extracorporeal device. Diluted blood containing blood cells is introduced from a substance inlet 1-2 to fill the device, then diluted plasma is introduced from a sheath inflow port 1-1, and the blood cells are circulated through a region of the device where the flow rate is changed by a pump action, thereby realizing a simulation of the influence of the environment of the pulsating blood flow on the blood cells.
Claims (6)
1. An extracorporeal device for analyzing the effect of pulsatile blood flow on a substance in a fluid, wherein the extracorporeal device (1) comprises a sheath flow inlet (1-1), a substance inlet (1-2), a blood flow pulsatile waveform generating channel (1-3) and a fluid outlet (1-4); the two sheath inlets (1-1) are respectively connected with the initial ends of the blood flow pulsation waveform generation channels (1-3) through two sheath flow channels; the substance inlet (1-2) is positioned between the two sheath inlets (1-1) and is connected with the initial end of the blood flow pulsation waveform generation channel (1-3) through the injection channel; the tail end of the blood flow pulsation waveform generation channel (1-3) is provided with a fluid outlet (1-4).
2. The in vitro device for analyzing the effect of pulsatile blood flow on a substance in a fluid according to claim 1, wherein the in vitro device for analyzing the effect of pulsatile blood flow is used to study the effect of periodically varying shear forces exerted by the substance and cells of the blood vessel wall into which pulsatile blood flow is applied; specifically, the boundary shape of the blood flow pulsation waveform generation channel (1-3) is changed to enable the spatial distribution condition of the flow velocity on the axis in the flow channel to be the same as the blood flow waveform in one pulsation period in the artery, when the substances in the pulsation blood flow pass through the blood flow pulsation waveform generation channel (1-3) along the axis, the shearing force generated by the fluid on the substances is dynamically changed along with time due to the unevenly distributed flow velocity, and the change condition is the same as the blood flow pulsation waveform, so that the stress of the substances in the simulated pulsation blood flow environment is realized; by adjusting the boundary shape of the blood flow pulsation waveform generation channels (1-3), different blood flow pulsation waveforms generated under the influence of physiological and pathological conditions can be simulated, and the rules and mechanisms of different waveforms influencing the properties and states of substances are researched.
3. An in vitro apparatus for analyzing the effect of pulsatile blood flow on a substance in a fluid according to claim 1 or 2, wherein the length and width directions of the blood flow pulsatile waveform generating channels (1-3) are defined as x-direction and y-direction, respectively, and the height direction is defined as z-direction, and the velocity waveform of the blood flow is modeled as u if the velocity waveform is defined as x-y cross section0Then the shape of the blood flow pulsation waveform generation channels (1-3) is obtained by solving the following optimization problem
div uρ＝0inΩ
Wherein
Is a two-dimensional plane, mu, including all possible flow channel shapesρIs the average flow velocity in the height direction over the x-y cross-section, p is the pressure,
is the strain rate tensor, μ is the fluid viscosity, ρ is the material density,
representing a range of desirable values of p,
mα(p) is the permeability of the fluid, defined as
α and q are parameters of the optimization problem, passing through mα(rho) the fluid is limited to flow in a region where rho is close to 0 and cannot enter a region where rho is close to 1, k is a parameter of an optimization problem, and the existing flow waveform u is realized by adjusting the value of k0While also reducing flow energy dissipation; and solving the optimization problem by combining a finite element and an optimization algorithm to obtain the distribution of the material density rho on a two-dimensional plane, setting the region of rho close to 0 as a flow channel region, and setting the region of rho close to 1 as a boundary solid region, thereby realizing the design of the shape of the blood flow pulsation waveform generation channel (1-3).
4. An extracorporeal device for analyzing the effect of pulsatile blood flow on a substance in a fluid according to claim 1 or 2, wherein the length of the extracorporeal device (1) is in the order of centimeters; the width is designed to be millimeter magnitude; the external device (1) is machined by adopting a precision lathe or laser to cut PMMA.
5. An extracorporeal device for analyzing the effect of pulsatile blood flow on a substance in a fluid according to claim 3, wherein the length of the extracorporeal device (1) is in the order of centimeters; the width is designed to be millimeter magnitude; the external device (1) is machined by adopting a precision lathe or laser to cut PMMA.
6. A system for analyzing the effect of pulsatile blood flow on a substance in a fluid, characterized in that it comprises an extracorporeal device (1), a constant-speed pump (2), a one-way valve (3) and a catheter; the blood storage is connected with two sheath inlets (1-1) of the extracorporeal device (1) through a catheter, and the substance storage to be detected is connected with a substance inlet (1-2) of the extracorporeal device (1) through a catheter; the fluid outlet (1-4) of the extracorporeal device (1) is sequentially connected with a constant speed pump (2) and a one-way valve (3) through a catheter, and the constant speed pump (2) is used for maintaining the constant speed circulation flow of blood flow in the system.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202210030231.1A CN114357844B (en) | 2022-01-12 | 2022-01-12 | In-vitro device and system for analyzing action of pulsating blood flow on substances in fluid |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202210030231.1A CN114357844B (en) | 2022-01-12 | 2022-01-12 | In-vitro device and system for analyzing action of pulsating blood flow on substances in fluid |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN114357844A true CN114357844A (en) | 2022-04-15 |
| CN114357844B CN114357844B (en) | 2023-01-13 |
Family
ID=81109885
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202210030231.1A Active CN114357844B (en) | 2022-01-12 | 2022-01-12 | In-vitro device and system for analyzing action of pulsating blood flow on substances in fluid |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN114357844B (en) |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| AU2002230396A1 (en) * | 2000-10-06 | 2002-07-04 | Krstec, Victor | System and method to simulate hemodynamics |
| WO2005033671A1 (en) * | 2003-10-08 | 2005-04-14 | Haemoprobe B.V. | Method and device for in vitro simulation of an in vivo fluid flow |
| CN1965754A (en) * | 2005-11-15 | 2007-05-23 | 王卫东 | Analyzer of blood circulation dynamics and method thereof |
| US20110152398A1 (en) * | 2009-12-18 | 2011-06-23 | Bissah Kofi A | Compositions for repelling fluid and uses thereof |
| CN105925480A (en) * | 2016-05-12 | 2016-09-07 | 大连理工大学 | Micro-fluidic chip for high-throughput screening of blood brain barrier drug permeability and preparation method of micro-fluidic chip |
| CN109106348A (en) * | 2018-07-29 | 2019-01-01 | 大连理工大学 | A kind of coronary flow reserve score calculation method based on pore media theory |
| CN111652849A (en) * | 2020-05-08 | 2020-09-11 | 武汉联影医疗科技有限公司 | Blood flow parameter calculation result obtaining method, device, equipment and system |
| CN112980679A (en) * | 2021-02-04 | 2021-06-18 | 大连理工大学 | Endothelial cell in-vitro culture system for optimizing continuous flow artificial heart pulsation working mode |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| AU3039602A (en) * | 2000-10-06 | 2002-04-29 | Michael B Dancu | System and method to simulate hemodynamics |
-
2022
- 2022-01-12 CN CN202210030231.1A patent/CN114357844B/en active Active
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| AU2002230396A1 (en) * | 2000-10-06 | 2002-07-04 | Krstec, Victor | System and method to simulate hemodynamics |
| WO2005033671A1 (en) * | 2003-10-08 | 2005-04-14 | Haemoprobe B.V. | Method and device for in vitro simulation of an in vivo fluid flow |
| CN1965754A (en) * | 2005-11-15 | 2007-05-23 | 王卫东 | Analyzer of blood circulation dynamics and method thereof |
| US20110152398A1 (en) * | 2009-12-18 | 2011-06-23 | Bissah Kofi A | Compositions for repelling fluid and uses thereof |
| CN105925480A (en) * | 2016-05-12 | 2016-09-07 | 大连理工大学 | Micro-fluidic chip for high-throughput screening of blood brain barrier drug permeability and preparation method of micro-fluidic chip |
| CN109106348A (en) * | 2018-07-29 | 2019-01-01 | 大连理工大学 | A kind of coronary flow reserve score calculation method based on pore media theory |
| CN111652849A (en) * | 2020-05-08 | 2020-09-11 | 武汉联影医疗科技有限公司 | Blood flow parameter calculation result obtaining method, device, equipment and system |
| CN112980679A (en) * | 2021-02-04 | 2021-06-18 | 大连理工大学 | Endothelial cell in-vitro culture system for optimizing continuous flow artificial heart pulsation working mode |
Non-Patent Citations (4)
| Title |
|---|
| YAN-XIA WANG 等: "A multi-component parallel-plate flow chamber system for studying the effect of exercise-induced wall shear stress on endothelial cells", 《BIOMEDICAL ENGINEERING ONLINE》 * |
| 柳兆荣 等: "脉动流条件下血管壁的应力分布", 《力学学报》 * |
| 覃开蓉 等: "动脉内皮血流动力学微环境建模分析和体外模拟方法与技术研究进展", 《实验流体力学》 * |
| 魏延宾: "血管支架血流动力学性能体外测试装置的实验研究", 《中国优秀硕士学位论文全文数据库工程科技Ⅱ辑》 * |
Also Published As
| Publication number | Publication date |
|---|---|
| CN114357844B (en) | 2023-01-13 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| Deutsch et al. | Experimental fluid mechanics of pulsatile artificial blood pumps | |
| CN103215185B (en) | Micro-fluid control device capable of simultaneously exerting mechanical stimulation and chemical stimulation | |
| Chen et al. | Microfluidic models of physiological or pathological flow shear stress for cell biology, disease modeling and drug development | |
| Abdullah et al. | A micropolar fluid model of blood flow through a tapered artery with a stenosis | |
| Quarteroni et al. | Cardiovascular mathematics | |
| CN110853471A (en) | Bionic simulation training device for cardiac surgery | |
| CN114357844B (en) | In-vitro device and system for analyzing action of pulsating blood flow on substances in fluid | |
| US20060096348A1 (en) | Method for measuring recirculation in catheters | |
| CN108467837B (en) | Visual multichannel fluid shear force cell culture device and method thereof | |
| Eldesoky | Unsteady MHD pulsatile blood flow through porous medium in a stenotic channel with slip at the permeable walls subjected to time dependent velocity (injection/suction) | |
| Avrahami et al. | Can vortices in the flow across mechanical heart valves contribute to cavitation? | |
| Park et al. | Dynamic adhesion characterization of cancer cells under blood flow-mimetic conditions: effects of cell shape and orientation on drag force | |
| Park | The need of slanted side holes for venous cannulae | |
| CN107177500A (en) | A kind of bionical impulsive motion bioreactor based on Luo Ye pumps | |
| He et al. | Finite element analysis on fluid filtration in system of permeable curved capillary and tissue | |
| Quarteroni | What mathematics can do for the simulation of blood circulation | |
| Ni et al. | Numerical study of RBC motion and deformation through microcapillary in alcohol plasma solution | |
| CN108339580A (en) | A kind of fluid shearing force generating mechanism and hydrodynamic shear generation method | |
| Bazan et al. | Design conception and experimental setup for in vitro evaluation of mitral prosthetic valves | |
| CN208194421U (en) | A kind of fluid shearing force generating mechanism | |
| Nadeem et al. | Numerical analysis of blood flow through multiple stenosis right coronary artery | |
| CN111718843B (en) | Balloon pulsating perfusion culture system | |
| Almomani et al. | Influence of erythrocyte shape on platelet scattering towards vessel wall | |
| Mongrain et al. | Study of catheter designs and drug mixing processes using 2D steady numerical simulations | |
| Niroomand-Oscuii et al. | An innovative method for generating pulsatile blood flow via an axial ventricular assist device |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |