CN111489624A - Single-alveolus three-dimensional amplification model and alveolus respiration simulation device - Google Patents
Single-alveolus three-dimensional amplification model and alveolus respiration simulation device Download PDFInfo
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Abstract
The invention discloses a single-alveolus three-dimensional amplification model and an alveolus respiration simulation device, wherein the single-alveolus three-dimensional amplification model comprises a transparent closed container, a simulation alveolus pipeline and a simulation alveolus; the transparent closed container is provided with a cavity and a gas inlet and outlet communicated with the inside and the outside of the cavity; one end of the simulated alveolar pipeline is provided with a liquid inlet, and the other end of the simulated alveolar pipeline is provided with a liquid outlet; the simulated alveolus is arranged in a cavity of the transparent closed container; the simulated alveolus has an inner cavity and a transparent elastic side wall, and the inner cavity is communicated with the simulated alveolus pipeline. The single-alveolar three-dimensional amplification model has a simple structure, can be used for researching complex three-dimensional flow fields in alveoli, and accurately simulates the flow fields of all sections in different stages of alveoli.
Description
Technical Field
The invention relates to biomedical equipment, in particular to a single-alveolus three-dimensional amplification model and an alveolus respiration simulation device.
Background
When the human lung exchanges gas with the outside through a respiratory system, pollutants and particles in the air are inevitably sucked, and further the human health is harmed. Therefore, the research on the fluid transmission and particle transportation and deposition rule in the lung is of great significance for determining the cause and deterioration of common respiratory system diseases such as lung diseases and improving clinical treatment and prevention measures.
In order to research the flow mode and particle deposition in the alveolus, some researchers design a multi-stage alveolus crotch structure, obtain an alveolus tree male mold by utilizing a light soft lithography technology, and pour a chip by using a flexible material, which is a great progress of an alveolus experiment on the real size. However, because the size of the alveolus is small and the structure is complex, the existing micro-nano manufacturing technology can not establish a physical model which completely accords with the actual size and the structure of the alveolus, and the shape of the alveolus in the manufactured alveolus chip is cylindrical and is not consistent with the real shape (spherical shape) of the alveolus of a human body; and the existing research content is only limited to two-dimensional flow, and three-dimensional flow data of a real model cannot be obtained. In addition, at present, researchers also have the defect that a real model is complemented by establishing an alveolar amplification model, but most of current amplification model tests are only geometrically similar, matching is not performed on fluid flow dynamics similarity, and the consistency of an alveolar expansion and contraction process and flow input cannot be accurately and synchronously controlled in a breathing process, so that the flow details in the alveolar cannot be revealed. At present, all experiments of the amplification model only measure data of a single plane, and three-dimensional quantitative flow data in an alveolus is not found.
Disclosure of Invention
The present invention is directed to solving at least one of the problems of the prior art. Therefore, the invention provides a single-alveolus three-dimensional amplification model and an alveolus respiration simulation device, wherein the single-alveolus three-dimensional amplification model can be used for researching a complex three-dimensional flow field in the alveolus and accurately simulating the flow field of each section in different stages of alveolus.
The technical scheme adopted by the invention is as follows:
in a first aspect of the present invention, a single-alveolar three-dimensional amplification model is provided, which includes:
the transparent closed container is provided with a chamber and a gas inlet and outlet communicated with the inside and the outside of the chamber;
the device comprises a simulation alveolar pipeline, a liquid inlet and a liquid outlet, wherein one end of the simulation alveolar pipeline is provided with the liquid inlet, and the other end of the simulation alveolar pipeline is provided with the liquid outlet;
the simulated alveolus is arranged in the cavity of the transparent closed container; the simulated alveoli have lumens and transparent elastic sidewalls, the lumens communicating with the simulated alveoli conduit.
The single-alveolar three-dimensional amplification model provided by the embodiment of the invention at least has the following beneficial effects: the single-alveolar three-dimensional amplification model is simple in structure, is amplified based on the real alveolar size, can be used for researching a complex three-dimensional flow field in the alveolar when the side wall expands, contracts and deforms due to respiration, and can accurately simulate the flow field of each section in different levels of alveolar; the three-dimensional amplification model can be used for researching the transportation and deposition characteristics of micro-nano particles (PM2.5) and medicine particles (including nutrient substances) in alveolar ducts and alveoli; based on the three-dimensional amplification model, the research on the flow mode in the alveolar sac can also provide useful data for developing artificial lung and chip lung organs, and contributes to the research and development of a lung drug screening platform.
According to some embodiments of the invention, the transparent elastic sidewall is made of a transparent elastic polymer; preferably, the material of the transparent elastic side wall is polydimethylsiloxane.
According to some embodiments of the invention, the simulated alveoli are spherical simulated alveoli.
According to some embodiments of the invention, the simulated alveolar duct is a transparent simulated alveolar duct; preferably, the material of the simulated alveolar duct is the same as that of the simulated alveoli.
According to some embodiments of the invention, the simulated alveolar conduit is mounted on the transparent closed container through the cavity of the transparent closed container, and the simulated alveoli are mounted in the cavity of the transparent closed container.
According to some embodiments of the invention, the simulated alveolar duct is a spherical simulated alveolar duct.
According to some embodiments of the invention, the diameter of the spherical simulated alveolar duct is 20-25 mm, the diameter of the simulated alveolus is 20-25 mm, and the thickness of the transparent elastic side wall of the simulated alveolus is 70-100 μm.
In a second aspect of the present invention, there is provided an alveolar respiration simulation apparatus, comprising any one of the single-alveolar three-dimensional amplification models provided in the first aspect of the present invention.
According to some embodiments of the invention, the alveolar respiration simulation device further comprises a feed pressure control device for delivering and pumping working fluid to the simulated alveolar duct and controlling the air pressure within the chamber of the transparent closed container. Through the arrangement of the feeding pressure control device, the reciprocating motion of the fluid in the simulated alveolar pipeline and the expansion and contraction motion of the simulated alveolus can be periodically, synchronously and cooperatively regulated through the feeding pressure control device, the respiratory process of the alveolus is simulated, the dynamic similarity with the flow in the actual human alveolar pipeline can be achieved, and the chaotic flow state of the fluid in the alveolus under different respiratory conditions is obtained.
According to some embodiments of the invention, the feed pressure control device is a two-channel programmable syringe pump; the two-channel programmable syringe pump comprises a first channel and a second channel; the first channel is communicated with a liquid inlet of a simulated alveolar pipeline on the single-alveolar three-dimensional amplification model and is used for conveying and pumping working fluid to the simulated alveolar pipeline; the second channel is communicated with the gas inlet and outlet on the transparent closed container and is used for controlling the gas pressure in the chamber of the transparent closed container;
or the feeding pressure control device comprises a feeding device and a pressure control device, wherein the feeding device is communicated with a liquid inlet of a simulated alveolar pipeline on the single-alveolar three-dimensional amplification model and is used for conveying and pumping working fluid to the simulated alveolar pipeline; the pressure control device is communicated with the gas inlet and outlet on the transparent closed container and is used for controlling the gas pressure in the chamber of the transparent closed container.
According to some embodiments of the invention, further comprising a control system for controlling the operational operation of the feed pressure control device.
Drawings
FIG. 1 is a front view of one embodiment of a single alveolar three-dimensional magnification model of the present invention;
FIG. 2 is a right side view of the single alveolar three-dimensional magnification model of FIG. 1;
FIG. 3 is a top view of the single alveolar three-dimensional magnification model of FIG. 1;
FIG. 4 is a schematic structural view of a single alveolar three-dimensional enlarged structure shown in FIG. 1;
FIG. 5 is a schematic diagram of an embodiment of an alveolar breath simulator according to the present invention;
FIG. 6 is a schematic diagram of the alveolar breath simulation apparatus of FIG. 5 simulating alveolar breath motion;
FIG. 7 is a graph of the flow field changes of the alveolar respiration simulation device of FIG. 5 simulating stage 6 alveolar respiration at various points in time during a respiratory cycle;
FIG. 8 is a graph of the flow field changes of the alveolar respiration simulation device of FIG. 5 simulating stage 8 alveolar respiration at various points in time during a respiratory cycle;
FIG. 9 is a graph of the velocity profile of a working fluid simulating different cross-sections within the alveoli at different times during a respiratory cycle simulating the 6 th stage alveoli;
fig. 10 is a flow chart of different cross-sections of simulated stage 6 alveoli at time T-0.125T.
Detailed Description
The concept and technical effects of the present invention will be clearly and completely described below in conjunction with the embodiments to fully understand the objects, features and effects of the present invention. It is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all embodiments, and those skilled in the art can obtain other embodiments without inventive effort based on the embodiments of the present invention, and all embodiments are within the protection scope of the present invention.
Referring to fig. 1 to 4, fig. 1 is a front view of a single-alveolar three-dimensional enlarged model according to an embodiment of the present invention, fig. 2 is a right view corresponding to the single-alveolar three-dimensional enlarged model shown in fig. 1, fig. 3 is a top view corresponding to the single-alveolar three-dimensional enlarged model shown in fig. 1, and fig. 4 is a schematic structural view of the single-alveolar three-dimensional enlarged structure shown in fig. 1. As shown in fig. 1 to 4, the single-alveolar three-dimensional enlarged model includes a transparent closed container 110, a simulated alveolar pipe 120, and a simulated alveolus 130. The transparent closed container 110 is provided with a chamber 111 and a gas inlet and outlet 112 communicating the inside and outside of the chamber 111; one end of the simulated alveolar conduit 120 has an inlet port 121 and the other end has an outlet port 122; the simulated alveolus 130 has an inner cavity 131 and a transparent elastic side wall 132, the inner cavity 131 being in communication with the simulated alveolus conduit 120; the simulated alveolus 130 is disposed in the chamber 111 of the transparent sealed container 110 such that the inner cavity 131 of the simulated alveolus 130 is separated from the chamber 111 of the transparent sealed container 110 by the transparent elastic sidewall 132.
The simulated alveoli 130 are in particular spherical. Due to the tiny size (about 200 μm in diameter) of a real alveolus, the complexity of the internal flow of the real alveolus and the limitation of the existing flow measurement technology, the details of a transient three-dimensional microflow pattern and a particle motion trajectory in the alveolus are difficult to quantitatively analyze, so the simulated alveolus 130 is generally enlarged to about 100 times of the actual alveolus size, and the diameter of the simulated alveolus 130 can be designed to be 20-25 mm, so that the flow mode of working fluid in the alveolus and the motion deposition trajectory of particles can be quantified by collecting flow field data.
The transparent elastic sidewall 132 can be made of transparent elastic polymer. Because the transparency and elasticity of the polydimethylsiloxane are good, and the refractive index is matched with that of the conventional working fluid, the influence of the refractive index of the material simulating the alveolus 130 on the particle tracking can be avoided, and therefore, in this embodiment, the transparent elastic sidewall 132 of the simulating alveolus 130 is made of Polydimethylsiloxane (PDMS). Of course, in other embodiments, other transparent elastic polymers may be used to simulate the transparent elastic sidewalls 132 of the alveoli 130.
The simulated alveoli 130 are typically fabricated using a rotary centrifuge process. The preparation method can be specifically processed and prepared by the following steps: a mold similar in geometry to the alveoli is first machined, which is an open spherical shell. Secondly, mixing the PDMS and the curing agent according to the proportion of 15:1, uniformly mixing the mixed solution by stirring, and vacuumizing to remove bubbles in the mixed solution. Treating the inner wall surface of the mold with trichlorosilane, extracting a proper amount of mixed liquid, injecting the mixed liquid into the mold after surface treatment, quickly fixing the mold on a centrifuge, firstly rotating the mold at a low speed of 380r/min for 3 minutes to form the mold, then carrying out high-speed centrifugation at a speed of 1300 r/min at the temperature of 60 ℃ and carrying out pre-curing treatment for 0.5 hour, taking the mold off the centrifuge after the mixed liquid is primarily cured, and putting the mold into a vacuum drying box to cure for 2 hours at the temperature of 100 ℃; stripping the molded simulated alveolus from the inner wall of the mold, and processing to prepare a spherical shell-shaped simulated alveolus 130; the processed simulated alveoli 130 are then combined with the simulated alveolar ducts 120. The polydimethylsiloxane is used as a raw material, the simulated alveolus is prepared by a rotary centrifugal method, the side wall of the prepared simulated alveolus 130 is thin (can be as thin as 70-100 mu m), the transparency is high, the elasticity is strong, the requirements of periodic expansion and contraction of the alveolus can be met, the requirement of visualization of a flow field in a model can also be met, and the three-dimensional flow field and the three-dimensional particle tracking can be carried out.
The transparent sealed container 110 may be a transparent glass sealed container or a transparent sealed container made of other materials. In the present embodiment, the transparent closed container 110 has a square shape, but in other embodiments, the transparent closed container 110 may have other shapes. To facilitate the observation of fluid in the alveoli, the simulated alveolar duct 120 is typically designed as a transparent simulated alveolar duct. For ease of manufacture, the simulated alveolar conduit 120 may be made of the same material as the simulated alveoli 130. The simulated alveolar conduit 120 may be a circular conduit or a square conduit in shape; in this embodiment, the simulated alveolar conduit 120 is a circular conduit. In order to facilitate the processing and research operation of the whole structure, the diameter of the circular simulated alveolar pipeline is generally 20-25 mm.
In the present embodiment, the simulated alveolar duct 120 is mounted on the transparent sealed container 110 through the chamber 111 of the transparent sealed container 110, and the simulated alveoli 130 are provided in the chamber 111 of the transparent sealed container 110. With the above structure, the transparent sealed container 110 can be used as a support for simulating the alveolar duct 120, and the whole structure is simplified.
In some embodiments, the single-alveolar three-dimensional enlarged model may further include a liquid storage container, which is in communication with the liquid outlet 122 of the simulated alveolar pipe 120 and is used for collecting the working fluid flowing out of the simulated alveolar pipe 120. In some embodiments, the unialveolar three-dimensional enlarged model may not contain a liquid storage container per se, and may be used in combination with the liquid storage container when in use.
The single-alveolus three-dimensional amplification model is simple in structure, simulates the three-dimensional shape of the alveolus through geometric similarity, specifically amplifies based on the size of the real alveolus, can be used for researching a complex three-dimensional flow field in the alveolus when the side wall expands, contracts and deforms due to respiration, and is easy to measure the details of the flow form and accurately track the movement track of particles; the method is simplified, a single-alveolar three-dimensional amplification model is adopted, the motion parameters can be changed to be matched with the Reynolds number Re (dynamics) in the actual alveoli of each stage, so that the motion conditions in the alveoli of each stage are respectively met, the research on the chaotic phenomenon in the complex flow fields in the alveoli of each stage and the research on the particle track are independently completed, the mutual interference and mutual restriction between the flow fields of each stage can be eliminated, and the flow fields of all interfaces in different alveoli of each stage can be accurately simulated; the three-dimensional amplification model can be used for researching the transportation and deposition characteristics of micro-nano particles (PM2.5) and medicine particles (including nutrient substances) in alveolar ducts and alveoli; based on the three-dimensional amplification model, the research on the flow mode in the alveolar sac can also provide useful data for developing artificial lung and chip lung organs, and contributes to the research and development of a lung drug screening platform.
Referring to fig. 5, fig. 5 is a schematic structural diagram of an alveolar respiration simulation device according to an embodiment of the present invention. As shown in fig. 5, the alveolar respiration simulation device includes a feed pressure control device and a single alveolar three-dimensional enlarged model.
The structure of the single-alveolar three-dimensional amplification model is similar to that of the single-alveolar three-dimensional amplification model shown in fig. 1 to 4, and is not described again.
The feeding pressure control device is used for conveying and pumping working fluid to the simulated alveolar pipeline 120 in the single-alveolar three-dimensional enlarged model and controlling the air pressure in the chamber 111 of the transparent closed container 110 on the single-alveolar three-dimensional enlarged model. In the present embodiment, the feed pressure control device is embodied as a two-channel programmable syringe pump 210, the two-channel programmable syringe pump 210 comprising a first channel 211 and a second channel 212; the first channel 211 is communicated with a liquid inlet 121 of the simulated alveolar pipeline 120 on the single-alveolar three-dimensional amplification model and is used for conveying and pumping working fluid to the simulated alveolar pipeline 120; the second channel 212 is in communication with the gas inlet/outlet 112 of the transparent sealed container 110, and is used for controlling the gas pressure in the chamber 111 of the transparent sealed container 110.
In this embodiment, the alveolar respiration simulation device further includes a liquid storage 220, and the liquid storage 220 is communicated with the liquid outlet 122 of the simulated alveolar pipe 120 and is used for collecting the working fluid flowing out of the simulated alveolar pipe 120. In some embodiments, the alveolar breath simulator may not include a reservoir 220 and may be used in conjunction with an external reservoir.
The alveolar respiration simulation device can be used for simulating the alveolar respiration process. Specifically, please refer to fig. 5 and 6; FIG. 6 is a schematic diagram of the alveolar respiration simulation apparatus of FIG. 5 simulating alveolar respiratory motion. FIG. 6 (a) is a schematic diagram showing the respiratory movement of the alveoli; FIG. 6 (b) shows a respiratory process (cycle T) simulating flow control of the working fluid in the alveolar tract 120; fig. 6 (c) shows the pressure control in the chamber 111 of the transparent closed vessel 110 during the breathing process (period T). In the inspiration phase (T is 0-T/2), working fluid (air simulated to be inhaled into the lung) enters the simulated alveolar pipeline 120 through the liquid inlet 121 of the simulated alveolar pipeline 120 by using the first channel 211 of the two-channel programmable injection pump 210, the flow rate is Qd (a sine function of time T), meanwhile, gas is extracted from the cavity 111 through the gas inlet and outlet 112 on the transparent closed container 110 through the second channel 212 of the two-channel programmable injection pump 210, the transparent elastic side wall 132 of the simulated alveolar 130 is expanded under the force (P), and the working fluid flows into the liquid storage container 220 through the liquid outlet 122 of the simulated alveolar pipeline 120; in the expiration phase (T ═ T/2 to T), the working fluid is pumped from the reservoir 220 into the simulated alveolar duct 120 through the outlet 122 of the simulated alveolar duct 120 by the first channel 211 of the two-channel programmable syringe pump 210, and at the same time, the transparent elastic sidewall 132 of the simulated alveolar 130 is forced to contract by injecting gas into the chamber 111 of the transparent closed container 110 by the second channel 212 of the two-channel programmable syringe pump 210. The flow of the working fluid in the simulated alveolar duct 120 and the pressure change in the chamber 111 of the transparent closed container 110 are synchronously controlled by the two-channel programmable syringe pump 210, and the flow rate runs as a sine function of time. In addition, in order to facilitate observation of alveolar respiratory movement, fluorescent particles can be added into the working fluid, a PIV system comprising a high-speed camera, an image processing computer and a laser generator is adopted to observe a flow field, and specifically, laser is excited by the laser generator to irradiate the fluorescent particles in the working fluid, and the fluorescent particles are excited to emit fluorescence; then, a high-speed camera is used for photographing and recording the breathing motion of the working fluid, and the moving image of the working fluid photographed by the high-speed camera is processed by an image processing computer.
In the above process, the unsteady flow in the simulated alveolar duct 120 in the single-alveolar three-dimensional amplification model is precisely controlled by using the two-channel programmable injection pump 210, and the motion similarity and the dynamic similarity of the working fluid in the model and the fluid in the real alveolar duct are realized by matching dimensionless numbers (such as Reynolds number and Womelsely number) in the model and the real alveolar duct of the human body; by changing flow parameters (such as flow in a simulated alveolar pipeline, expansion size of the alveoli and breathing period), different flow states and chaotic flow signs in the alveoli in the breathing process can be systematically simulated.
In other embodiments, the feeding pressure control device may also be configured to include a feeding device and a pressure control device, the feeding device is communicated with the liquid inlet 121 of the simulated alveolar pipe 120 on the single-alveolar three-dimensional enlarged model for delivering and pumping the working fluid to the simulated alveolar pipe 120; the pressure control device is in communication with a gas inlet and outlet 112 of the transparent closed container 110, and is used for controlling the pressure in the chamber 111 of the transparent closed container 110.
In addition, to further facilitate the control of the flow of the working fluid in the simulated alveolar conduit 120 and the control of the air pressure in the chamber of the transparent closed container 110 by the alveolar respiration simulation apparatus, the alveolar respiration simulation apparatus further comprises a control system for controlling the working motion of the feed pressure control apparatus.
The alveolar respiration simulation device shown in fig. 5 can be used to simulate the alveolar respiration process for the intra-alveolar flow field study. Specifically, a mixed solution of 36 wt% of water and 64 wt% of glycerol is used as a working fluid, 10 μm red fluorescent microspheres are added to the working fluid as tracer particles, and the mass ratio of the tracer particles to the working fluid is 1: 300 is added in proportion; and then observing a flow field in the alveoli in the simulated alveolar respiration process through a PIV system.
First, the alveolar respiration simulation apparatus shown in fig. 5 was used to simulate the alveolar respiration processes of stages 6 and 8 to study the intra-alveolar flow field, and the results are shown in fig. 7 and 8. FIGS. 7 and 8 show simulated flow field changes in the alveoli at different time points during a respiratory cycle, at stage 6 and stage 8, respectively, which are representative of two typical flow fields in the alveoli, respectively. As shown in fig. 7, the flow field in the simulated stage 6 alveolar is swirling, but over time, the swirl disappears at some point. The flow regime in the simulated alveolus is sensitive to both the half-opening angle of the simulated alveolus (meaning the size of the opening of the alveolus, i.e. half the angle between the opening of the alveolus and the centre of the sphere) and the flow ratio of the simulated alveolus to the simulated alveolar duct, which is theoretically constant. But the half opening angle may change with time. As the simulated alveoli expand, they grow in size, with the centers gradually moving away from the axis of the simulated alveolar conduit. Furthermore, the opening of the simulated alveoli is constant, and therefore the geometric expansion or contraction is not self-similar in the single alveolar three-dimensional scaled-up model of the alveolar respiration simulation apparatus. In addition, figure 7 also shows that as the simulated alveoli expand and contract, the position of the vortices change from the alveolar wall towards the center of the alveolar opening. As shown in fig. 8, the flow field in the 8 th stage alveolar is free of eddies and radial flow at different times in a cycle, which is quite different from the 6 th stage alveolar flow field.
In order to understand the velocity distribution in the alveoli in more detail, different cross-sectional shapes in the alveoli are simulated at different times in one respiratory cycle for the 6 th-stage alveoliThe results obtained are shown in FIG. 9, in FIG. 9 (a), as the flow velocity distribution of the fluid1)、(b1) And (c)1) Flow charts in the simulated stage 6 alveolar region were obtained when T is 0.125T, inhalation peak (T is 0.25T), and T is 0.375T, respectively, (a)2)、(b2) And (c)2) Are respectively corresponding to (a)1)、(b1) And (c)1) Of different cross-sections. (a)1) The section line 2 in the figure passes through (a)1) Region in the vicinity of saddle point in the drawing, (b)1) And (c)1) The middle section line 1 passes through (b)1) And (c)1) Center of the vortex in (c). As can be seen from fig. 9, the flow rate of the working fluid becomes smaller as the cross-sectional line is away from the simulated alveolar opening. Therefore, the flow rate of the working fluid in the simulated alveoli gradually decreases from the inlet to the bottom of the simulated alveoli. There is a significant difference in flow rate from the inlet to the middle position, while the flow rate decreases slightly from the middle to the bottom. There is a velocity inflection point on a line passing through the center of the vortex. From the above, the position of the vortex center changes with the respiration of the alveoli, and the change of the vortex position and the vorticity has certain influence on the movement track of the particles.
In addition, a saddle point in an alveolar flow field is observed in a simulated alveolar respiration process, specifically, as shown in fig. 10, fig. 10 is a flow chart of the above simulated 6 th-stage alveoli on different cross sections at the time T equal to 0.125T, all the cross sections are parallel to each other, wherein (a) shows a complete flow chart, and (b) shows a partial enlarged view of the vicinity of the saddle point in (a). As shown in fig. 10, the flow fields on different planes of the simulated alveoli all have saddles, the saddles are the premise of the generation of complex chaotic flow, and the flow pattern near the proximal angle and the saddles are highly complex, which is an obvious sign of chaotic flow. Furthermore, the experimental research can provide experimental data for preliminarily proving that chaotic flow exists in the three-dimensional alveolar flow field.
Therefore, the invention provides a single-alveolar three-dimensional amplification model and an alveolar respiration simulation device, and the single-alveolar three-dimensional amplification model can accurately simulate the flow fields of all interfaces in different stages of alveoli and explore the complex flow in the alveoli. The method is characterized in that the method can be used for researching an alveolar flow system when the side wall is deformed due to respiration expansion and contraction through establishing the three-dimensional amplification model of the alveolar end; and flow field data in the three-dimensional amplified alveolar model is obtained by using a flow measurement technology through geometric, hydrodynamic similarity and optical coefficient matching.
Claims (10)
1. A unialveolar three-dimensional enlarged model, comprising:
the transparent closed container is provided with a chamber and a gas inlet and outlet communicated with the inside and the outside of the chamber;
the device comprises a simulation alveolar pipeline, a liquid inlet and a liquid outlet, wherein one end of the simulation alveolar pipeline is provided with the liquid inlet, and the other end of the simulation alveolar pipeline is provided with the liquid outlet;
the simulated alveolus is arranged in the cavity of the transparent closed container; the simulated alveoli have lumens and transparent elastic sidewalls, the lumens communicating with the simulated alveoli conduit.
2. The unialveolar three-dimensional enlarged model according to claim 1, wherein the transparent elastic sidewalls are made of a transparent elastic polymer.
3. The unialveolar three-dimensional enlarged model according to claim 2, wherein the simulated alveoli are spherical simulated alveoli.
4. The unialveolar three-dimensional enlargement model according to claim 1, wherein the simulated alveolar ducts are transparent simulated alveolar ducts.
5. The unialveolar three-dimensional enlarged model according to claim 1, wherein the simulated alveolar duct is mounted on the transparent closed container through a chamber of the transparent closed container, and the simulated alveoli are disposed in the chamber of the transparent closed container.
6. The unialveolar three-dimensional enlargement model according to claim 1, wherein the simulated alveolar ducts are spherical simulated alveolar ducts.
7. The unialveolar three-dimensional enlargement model according to claim 6, wherein the diameter of the spherical simulated alveolar pipe is 20-25 mm, the diameter of the simulated alveolus is 20-25 mm, and the thickness of the transparent elastic side wall of the simulated alveolus is 70-100 μm.
8. An alveolar respiration simulation apparatus comprising the one-alveolar three-dimensional enlarged model according to any one of claims 1 to 7.
9. The alveolar respiration simulation device of claim 8, further comprising a feed pressure control device for delivering and pumping working fluid to the simulated alveolar ducts and controlling the air pressure within the chamber of the transparent closed container.
10. The alveolar respiration simulation of claim 9, wherein the feed pressure control device is a two-channel programmable syringe pump; the two-channel programmable syringe pump comprises a first channel and a second channel; the first channel is communicated with a liquid inlet of a simulated alveolar pipeline on the single-alveolar three-dimensional amplification model and is used for conveying and pumping working fluid to the simulated alveolar pipeline; the second channel is communicated with the gas inlet and outlet on the transparent closed container and is used for controlling the gas pressure in the chamber of the transparent closed container;
or the feeding pressure control device comprises a feeding device and a pressure control device, wherein the feeding device is communicated with a liquid inlet of a simulated alveolar pipeline on the single-alveolar three-dimensional amplification model and is used for conveying and pumping working fluid to the simulated alveolar pipeline; the pressure control device is communicated with the gas inlet and outlet on the transparent closed container and is used for controlling the gas pressure in the chamber of the transparent closed container.
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| CN114317267A (en) * | 2022-01-05 | 2022-04-12 | 浙江大学 | Multilayer microfluidic organ chip with multistage alveolar tube structure and manufacturing method thereof |
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