A device for in-vitro simulation of intestinal motility

Abstract

The present application relates to a device for in vitro simulation of intestinal movement, comprising a flexible tubular body composed of an inner wall surface and an outer wall surface, the flexible tubular body is divided into multiple non-communicating segments in the axial direction, at least one petal-shaped unit is arranged in the circumferential direction of each segment, and a sandwich space is arranged between the inner wall surface and the outer wall surface in the petal-shaped unit; a driving mechanism comprises at least one syringe pump and a connecting pipeline, the syringe pump is communicated with the sandwich space of at least one petal-shaped unit through the connecting pipeline; a dialysis bag is arranged in the internal cavity of the flexible tubular body; a permeate cavity is formed between the outer wall of the dialysis bag and the inner wall surface of the flexible tubular body; a liquid inlet pipe is communicated with the permeate cavity; a sample inlet pipe and a sample outlet pipe are both communicated with the dialysis bag. By adopting the segmented petal-shaped flexible wall surface structure cooperating with the hydraulic drive of the syringe pump, the present application can be simultaneously applied to the physiological movement simulation of small intestine and colon, realize the accurate reproduction of multiple movement modes and the real-time material exchange in the movement process.

Description

Technical Field

[0001] This invention relates to the field of in vitro digestive simulation technology, and in particular to a device for simulating intestinal motility in vitro. Background Technology

[0002] The small intestine and colon, as core digestive organs in the human digestive tract, respectively undertake the crucial functions of nutrient absorption and water reabsorption. The small intestine achieves thorough mixing, digestion, and nutrient absorption of chyme through tonic contractions, segmental movements, and peristalsis. The colon, through its characteristic haustra structure (composed of haustra septa, haustra pouches, and interhaustra passages), combined with sac-like reciprocating movements, multi-sac propulsive movements, and peristalsis, achieves the storage, mixing, and water reabsorption of contents, gradually transforming food residue into semi-solid feces. In vitro simulation of the physiological structure and motility of the small and colon is of great significance for evaluating food digestibility, studying drug release behavior, and analyzing gut microbiota metabolism, effectively reducing reliance on animal experiments and human clinical trials.

[0003] Existing in vitro devices for simulating intestinal motility have the following significant drawbacks: Insufficient biomimicry in structural morphology: Existing small intestine simulation devices are mostly straight tubes or simple curved structures, lacking simulation of the winding and coiling spatial layout of the real small intestine in the abdominal cavity; existing colon simulation devices mostly use rigid glass jars or smooth flexible membranes, lacking the reproduction of the characteristic sac-like structure of the colon. The above-mentioned rigid or simplified structures cannot realistically reflect the flexible characteristics and complex spatial morphology of the intestinal wall, resulting in significant differences between the digestive process and the actual physiological state.

[0004] The existing devices mainly use mechanical stirring, magnetic stirring, or rigid rollers and extrusion plates to squeeze the wall surface, which can only simulate simple shearing, squeezing, or single peristaltic patterns. For complex physiological movement patterns such as the tonic contraction and segmental movement of the small intestine, as well as the sacral reciprocating movement and multi-sac propulsion movement of the colon, the existing technology cannot accurately reproduce them, and the degree of movement biomimicry is low.

[0005] The lack or lag in the function of substance exchange: Most existing small intestine simulation devices adopt a step-by-step operation of "digestion before absorption", transferring digestive products to an independent dialysis device for passive absorption, which cannot simulate the continuous physiological process of digestion and absorption in the small intestine; most existing colon simulation devices lack the simulation of water reabsorption function, and cannot reproduce the physiological changes of food residues gradually dehydrating in the colon, resulting in a discrepancy between in vitro research results and the actual situation in vivo.

[0006] In summary, the existing technology lacks a universal device that can be applied to both small intestine and colon simulation. Such a device should have a flexible biomimetic structure, multi-mode motion driving capability, and integrated material exchange function to achieve a realistic in vitro reproduction of intestinal physiological processes. Summary of the Invention

[0007] Therefore, the technical problem to be solved by the present invention is to overcome the shortcomings of the prior art and provide an in vitro device for simulating intestinal movement. The device adopts a segmented, lobed flexible wall structure and is hydraulically driven by an injection pump. It can be applied to the physiological movement simulation of both the small intestine and the colon, and can accurately reproduce multiple movement patterns and real-time material exchange during the movement process.

[0008] To address the aforementioned technical problems, the present invention provides an in vitro device for simulating intestinal motility, comprising: A flexible tubular body is composed of an inner wall and an outer wall. The flexible tubular body is divided into multiple non-connected segments along the axial direction. Each segment is provided with at least one petal-shaped unit along the circumferential direction. A sandwich space is provided in the petal-shaped unit between the inner wall and the outer wall. The driving mechanism includes at least one injection pump and a connecting pipeline. The injection pump is connected to the interlayer space of the petal unit through the connecting pipeline and is used to control the injection and extraction of fluid in the petal unit to drive the inner wall surface to produce periodic radial deformation. A dialysis bag is disposed in the internal cavity of the flexible tubular body to contain the contents; an permeate cavity is formed between the outer wall of the dialysis bag and the inner wall of the flexible tubular body to contain the dialysis fluid or hypertonic solution. The inlet tube is connected to the dialysis bag and is used to inject the digested sample; Both the injection tube and the sampling tube are connected to the permeate chamber, which facilitates the injection or replacement of dialysate or hypertonic solution into the permeate chamber.

[0009] In one embodiment of the present invention, the thickness of the inner wall surface is less than the thickness of the outer wall surface.

[0010] In one embodiment of the present invention, when the number of petal units in each segment is greater than 1 and the interlayer space between the petal units is connected, the injection pump is connected to the interlayer space of at least one of the petal units through a connecting pipe for injecting or extracting fluid into the interlayer space.

[0011] In one embodiment of the present invention, when the number of the petal units in each segment is greater than 1, and the interlayer spaces between the petal units are not interconnected, the injection pump is connected to the interlayer space of each petal unit through a connecting pipe for injecting or extracting fluid into the interlayer space.

[0012] In one embodiment of the present invention, a fixing ring is further included, which is sleeved on the outer wall surface of the flexible tubular body to fix the flexible tubular body and limit its radial expansion range.

[0013] In one embodiment of the present invention, the flexible tubular body is a coiled section, the coiled section is in a meandering coiled shape, and the permeate cavity is filled with dialysis fluid.

[0014] In one embodiment of the invention, each segment of the coiled section has at least one petal-shaped unit along the circumferential direction.

[0015] In one embodiment of the present invention, the flexible tubular body is a sac-like segment, the sac-like segment has a bag-like bulging structure, and the permeation cavity is filled with a hypertonic solution.

[0016] In one embodiment of the present invention, each segment of the sac-like segment is evenly distributed with at least one petal-like unit along the circumferential direction. When there are two petal-like units, the sac-like segment is peanut-shaped; when there are three petal-like units, the sac-like segment as a whole is petal-shaped.

[0017] In one embodiment of the invention, a heating device is further included for heating the fluid within the injection pump.

[0018] Compared with the prior art, the above-described technical solution of the present invention has the following advantages: The present invention discloses an in vitro intestinal motility simulation device. Through the flexible wall structure of segmented valve-shaped units and hydraulic drive of an injection pump, it can be applied to the physiological motility simulation of both the small intestine and colon. It also integrates a dialysis bag to realize real-time material exchange (absorption or dehydration) during the motility process, making the simulation process more consistent with the real physiological state and improving the reliability of experimental data. Attached Figure Description

[0019] To make the content of this invention easier to understand, the invention will be further described in detail below with reference to specific embodiments and accompanying drawings, wherein: Figure 1 This is a schematic diagram of the structure of the device for simulating intestinal motility in vitro in this invention; Figure 2 This is a schematic diagram of the external device for simulating small intestinal motility in Embodiment 1 of the present invention; Figure 3 for Figure 2 A schematic diagram of the structure of the local AA section of the coiled section and the injection pump; Figure 4 for Figure 2 A schematic diagram of the partial AA structure of the coiled section; Figure 5 for Figure 4 Schematic diagrams of the structure of part A before and after water filling; Figure 6 for Figure 4 Side sectional view; Figure 7 for Figure 6 A magnified schematic diagram of part B in the middle; Figure 8 for Figure 1 A schematic diagram of the segmental circumferential lobe units of the coiled segment; Figure 8 (a) is a single lobe-like unit structure; Figure 8 (b) is a structure consisting of two lobe-like units; Figure 8 (c) is a structure with 3 lobe-like units; Figure 8 (d) is a structure consisting of 4 lobe-like units; Figure 8 (e) is a structure consisting of 5 lobe-like units; Figure 8 (f) is a structure with 6 lobe-like units; Figure 9 This is a schematic diagram of the external device for simulating colonic motility in Embodiment 2 of the present invention; Figure 10 for Figure 9 A schematic diagram of a portion of the tubing in the simulated midcolon section and the structure of the infusion pump; Figure 11 for Figure 9 A schematic diagram of the structure of a section of the flexible tubular main body; Figure 12 for Figure 11 Schematic diagram of the structure of part C before and after water filling; Figure 13 for Figure 11 Side sectional view; Figure 14 for Figure 13 Enlarged schematic diagram of part D in the middle; Figure 15 for Figure 11 A schematic diagram of the flexible tubular body and the fixing ring; Explanation of reference numerals in the accompanying drawings: 1. Flexible tubular body; 11. Segment; 110. Lobe-shaped unit; 12. Outer wall surface; 13. Inner wall surface; 14. Intercalation space; 2. Injection pump; 3. Dialysis bag; 4. Sample inlet tube; 5. Sampling tube; 6. Permeate chamber; 7. Fixing ring; 8. Heating device. Detailed Implementation

[0020] The present invention will be further described below with reference to the accompanying drawings and specific embodiments, so that those skilled in the art can better understand and implement the present invention. However, the embodiments described are not intended to limit the present invention. Example 1

[0021] Reference Figure 1-7 As shown, an in vitro device for simulating small intestinal motility according to the present invention includes: a flexible tubular body 1, the flexible tubular body 1 being a coiled segment, the coiled segment being in a tortuous coiled shape, the flexible tubular body 1 being composed of an inner wall surface 13 and an outer wall surface 12, with a sandwich space 14 formed between the inner wall surface 13 and the outer wall surface 12; the flexible tubular body 1 being divided into multiple independent segments 11 along the axial direction, each segment 11 being divided into at least one petal-shaped unit 110 along the circumferential direction; The driving mechanism includes an injection pump 2 and a connecting pipeline. The injection pump 2 is connected to the interlayer space 14 of at least one of the petal units 110 through the connecting pipeline. It is used to drive the inner wall surface 13 to generate periodic radial deformation by controlling the injection and extraction of fluid in the petal unit 110. The dialysis bag 3 is disposed in the internal cavity of the flexible tubular body 1 and is used to contain the contents; the outer wall of the dialysis bag 3 and the inner wall surface 13 of the flexible tubular body 1 form an permeate cavity 6 for containing the dialysis fluid.

[0022] The inlet tube (not shown) is connected to the dialysis bag 3 and is used to inject the digested sample; Both the inlet tube 4 and the sampling tube 5 are connected to the permeate chamber 6, facilitating the injection or replacement of dialysate into the permeate chamber 6. The inlet tube 4 and the sampling tube 5 enable continuous or intermittent exchange of substances between the dialysate and the digestion products, simplifying operation, allowing for real-time monitoring of absorption, and avoiding frequent disassembly and assembly of the device, thus reducing the risk of contamination.

[0023] Preferably, the thickness of the inner wall surface 13 is less than the thickness of the outer wall surface 12. By limiting the thickness of the inner wall surface 13 to be less than that of the outer wall surface 12, the deformation of the inner wall surface 13 is more pronounced when the interlayer space 14 is filled with liquid and expands, which enhances the squeezing effect on the contents, improves the mechanical stirring and propulsion effect on the chyme, and makes the simulated small intestinal movement more thorough and effective in processing the food.

[0024] When the number of petal units 110 in each segment 11 is greater than 1 and the interlayer spaces 14 between the petal units 110 are interconnected, the injection pump 2 is connected to the interlayer spaces 14 of at least one of the petal units 110 via connecting pipes, for injecting or extracting fluid into the interlayer spaces 14. When the number of petal units 110 in each segment 11 is greater than 1 and the interlayer spaces 14 between the petal units 110 are not interconnected, the injection pump 2 is connected to the interlayer spaces 14 of each of the petal units 110 via connecting pipes.

[0025] In this embodiment, each segment 11 of the flexible tubular body 1 can be divided into at least one lobe-like unit 110 along the circumferential direction, covering a variety of structural forms from single-lobe overall compression to multi-lobe segmented independent control. The number of lobe segments can be flexibly selected according to different experimental needs, such as simulating the motility intensity or form of different segments of the small intestine, achieving a balance between structural complexity and control precision. Figure 8 (a)-(f) exemplarily show cross-sectional schematic diagrams of 1, 2, 3, 4, 5, and 6 lobe units 110.

[0026] This embodiment uses four circumferentially distributed petal units 110 as an example. The flexible tubular body 1 is made of silicone, which is an elastic and soft material that is resistant to acids and alkalis, making it an excellent material for in vitro models. This number ensures the feasibility of circumferential multi-point independent control, effectively simulating the alternating circumferential contraction of segmented motion, while avoiding structural complexity and control difficulties caused by too many petals, thus balancing simulation realism and device practicality. In this embodiment, preferably, the number of petal units 110 in each segment 11 is greater than one, and the interlayer space 14 between the petal units 110 is not connected. One injection pump 2 can be connected to at least one petal unit 110, or to multiple petal units 110. When multiple petals need to move synchronously with the same amplitude, one injection pump 2 can be connected to multiple petal units 110 to achieve coordinated movement of multiple petals; when fine control is required, multiple injection pumps 2 are connected one-to-one with multiple petal units 110 to achieve independent control. When the injection pump 2 is connected to multiple valve units 1110 in a one-to-one correspondence, independent fluid filling control of each valve unit 110 can be achieved. This allows for precise control of the expansion sequence and pressure of each valve, thereby accurately simulating the contractile movements of different regions and phases of the small intestine, such as alternating contractions during segmentation, improving the precision and controllability of the motion simulation. Connecting one injection pump 2 to multiple valve units 110 simplifies the complexity of the tubing layout. When multiple valves require synchronous, same-amplitude movements, such as tonic contractions or overall peristalsis, the number of injection pumps 2 can be reduced, lowering device cost and control difficulty, while ensuring the synchronous and coordinated movement of the relevant valve units.

[0027] It also includes a fixing ring 7, which is fitted onto the outer periphery of the flexible tubular body 1. By setting the fixing ring 7 in the device, the outer periphery of the flexible tubular body 1 is mechanically fixed, which can effectively maintain the spatial morphological layout of the meandering tubular structure, prevent the model from shifting or deforming due to internal liquid expansion or external disturbance, and ensure the stability of the device structure and the repeatability of experimental results during the experiment.

[0028] It also includes a heating device 8, which is used to heat the fluid in the injection pump 2. The heating device 8 can control the temperature of the liquid injected into the interlayer space 14, so that the interior of the flexible tubular body 1 is kept at a suitable reaction temperature, such as 37°C, the human body temperature, to provide an optimal activity environment for digestive enzymes. At the same time, the constant temperature liquid flowing in the interlayer space 14 helps to maintain a uniform and stable reactor temperature.

[0029] The in vitro device for simulating small intestinal motility based on the above structure operates as follows: A digested sample is added to the dialysis bag 3 with a molecular weight of 8000 Da. In this embodiment, the digested sample is chyme. Dialysis fluid is filled between the outer side of the dialysis bag 3 and the flexible inner wall 13 through the sample inlet tube 4 to form the permeate cavity 6, which simulates the absorption function of the small intestine.

[0030] The water temperature of the heating device 8 is set to 37°C. After the heating device 8 heats the water to 37°C, it is injected into the interlayer space 14 by the injection pump 2 to maintain the temperature inside the flexible tubular body 1 and provide the best activity environment for digestive enzymes.

[0031] The squeezing time is set to 6 hours to allow sufficient time for digestion and absorption of the chyme. Two adjacent injection pumps 2 are connected one-to-one to the valve-like units 110 of two adjacent segments 11. By alternately driving the adjacent injection pumps 2, the movement pattern of the adjacent segments 11 of the flexible tubular body 1 being cross-squeezed is achieved, simulating the segmented movement of the small intestine.

[0032] In practical applications, by controlling the water pressure and movement sequence of the injection pump 2, different movement effects can be achieved, realizing various forms of movement in the small intestine, including tonic contraction, segmental movement, and peristalsis.

[0033] Example 2 like Figure 9-14 As shown, the present invention provides an extracorporeal device for simulating colonic motility, comprising a flexible tubular body 1, wherein the flexible tubular body 1 is a sac-like segment, the sac-like segment having a bag-like bulging structure, the flexible tubular body 1 is composed of an inner wall surface 13 and an outer wall surface 12, the thickness of the inner wall surface 13 being less than the thickness of the outer wall surface 12; an interlayer space 14 between the inner wall surface 13 and the outer wall surface 12; the flexible tubular body 1 is divided into multiple independent segments 11 along the axial direction, each segment 11 being divided into at least one petal-like unit 110 along the circumferential direction; The driving mechanism includes an injection pump 2 and a connecting pipeline. The injection pump 2 is connected to the interlayer space 14 of the petal unit 110 through the connecting pipeline. It is used to drive the inner wall surface 13 to generate periodic radial deformation by controlling the injection and extraction of fluid in the petal unit 110. A dialysis bag 3 is disposed in the internal cavity of the flexible tubular body 1 to contain the contents; an permeate cavity 6 is formed between the outer wall of the dialysis bag 3 and the inner wall surface 13 of the flexible tubular body 1, and the permeate cavity 6 is filled with a hypertonic solution; An inlet tube (not shown) is connected to the dialysis bag 3 and is used to inject the digested sample into the dialysis bag 3; Both the injection tube 4 and the sampling tube 5 are connected to the permeate chamber 6, which facilitates the injection or replacement of hypertonic solution into the permeate chamber 6.

[0034] In this embodiment, a hypertonic solution is filled into the permeate chamber 6 of each segment 11, and the liquid is pushed in or drawn out by the injection pump 2.

[0035] When the number of petal units 110 in each segment 11 is greater than 1 and the interlayer space 14 between the petal units 110 is connected, the injection pump 2 is connected to the interlayer space 14 of at least one of the petal units 110 through a connecting pipe, for injecting or extracting fluid into the interlayer space 14. When the number of petal units 110 in each segment 11 is greater than 1 and the petal units 110 are not connected to each other, the injection pump 2 is connected to the interlayer space 14 of each of the petal units 110 through a connecting pipe.

[0036] In this embodiment, preferably, the number of valve units 110 in each segment 11 is greater than 1 and the interlayer space 14 between the valve units 110 is not connected. One injection pump 2 is connected to at least one valve unit 110, and can connect to an infinite number of valve units 110. Multiple valve units 110 connected to one injection pump 2 will move together. By changing the filling sequence of each segment 11, more realistic colonic movements can be simulated, such as sac-like reciprocating movements, multi-sac propulsion movements, and peristalsis.

[0037] In addition, a heating device 8 is included, which is used to heat the fluid in the injection pump 2. By setting the heating device 8 to preheat the fluid, the fluid injected into the interlayer space 14 is kept at a constant physiological temperature (e.g., 37°C). While driving the wall movement of the flexible tubular body 1, the temperature is maintained, simulating the physiological environment temperature of the real intestine and improving the accuracy of digestion or fermentation simulation. At the same time, it avoids temperature fluctuations caused by cold fluid directly contacting the flexible wall, ensuring the stability and repeatability of experimental conditions.

[0038] like Figure 15As shown, the device also includes a fixing ring 7, which is fitted onto the outer periphery of the flexible tubular body 1. By setting the fixing ring 7 in the device, the outer periphery of the flexible tubular body 1 is mechanically fixed, which can effectively maintain the spatial morphological layout of the colon segment, prevent the model from shifting or deforming due to internal fluid expansion or external disturbance, and ensure the stability of the device structure and the repeatability of experimental results during the experiment.

[0039] The interlayer space 14 of the three lobe-like units 110 in each segment 11 is connected to the same constant-temperature water injection pump 2 through a diversion pipe. By controlling the water pressure, movement sequence and number of injection pumps 2, different movement effects can be achieved, and multiple movement modes of the colon can be realized: Sacral reciprocating motion: The injection pumps 2 of two adjacent controllable segments 11 alternately inject and withdraw fluid, causing the two adjacent colonic sacs to squeeze alternately. Multi-bag propulsion motion: Each injection pump 2 is activated sequentially along the axial direction to achieve directional delivery of the contents; Peristalsis: The injection pump 2 of multiple controllable segments 11 operates sequentially to form peristaltic waves; Tonic contraction: The three lobular units 110 within the same controllable segment 11 are simultaneously filled, achieving overall radial contraction of the segment.

[0040] Preferably, in this embodiment, a flexible tubular body 1 is prepared using medical-grade silicone material with a Shore A hardness of 40 degrees. The flexible tubular body 1 is divided into 5 independent segments 11 along the axial direction, and the distance between adjacent segments 11 is 6 cm.

[0041] In this embodiment, each segment 11 is evenly divided into 3 petal-shaped units 110 along the circumferential direction. The cross-section is in the shape of three petals with an inner diameter of 5 cm, so as to simulate the haustra structure of a real colon.

[0042] The interlayer space 14 of the three lobe-shaped units of each segment 11 is connected to the injection pump 2 through a shunt pipe. Since one injection pump 2 can be connected to multiple connecting pipes, in actual applications, if it is necessary to control 5 segments 11, 5 injection pumps 2 or less can be connected.

[0043] In addition, a fixing ring 7 is fitted on the outer wall surface 12 of the flexible tubular body 1 to prevent the model from expanding excessively.

[0044] During operation, a dialysis bag 3 with a molecular weight of 100 Da is placed in the internal cavity of the flexible tubular body 1, and the dialysis bag 3 is filled with a soybean fermentation sample as the contents. A 20wt% polyethylene glycol (PEG) solution is filled into the permeate cavity 6 formed between the outer wall of the dialysis bag 3 and the inner wall 13 of the flexible tubular body 1 through the sample inlet tube 4 as a hypertonic solution. The water in the contents is transferred to the permeate cavity 6 by utilizing the osmotic pressure difference, simulating the water absorption function of the colon.

[0045] The heating device 8 is turned on to heat the fluid in the injection pump 2 to 37°C, maintaining the temperature inside the flexible tubular body 1. The squeezing time is set to 24 hours, and the injection pumps 2 of two adjacent segments 11 are controlled to squeeze alternately. That is, when the first segment 11 is filled, the second segment 11 is emptied, and when the second segment 11 is filled, the third segment 11 is emptied, and so on, to achieve bag-like reciprocating motion.

[0046] During operation, the increase in liquid volume in the permeate chamber 6 is periodically detected through the sampling tube 4 to assess the dehydration effect, while the viscosity change of the contents in the dialysis bag 3 is monitored.

[0047] Compared with the hollow fiber membrane dehydration method used in the prior art, the dehydration technology using dialysis bag 3 and hypertonic solution in this embodiment has the following advantages: the soft wall of dialysis bag 3 can cooperate with the squeezing and peristaltic movements of the colon model without causing additional resistance to the squeezing movement; no supporting equipment such as high-pressure pumps and membrane modules are required, the operation is simple and the cost is low; the device can effectively simulate the bag-like reciprocating movement and water reabsorption function of the colon, and its morphology and usage are suitable for in vitro fermentation research of high-viscosity ferments.

[0048] Obviously, the above embodiments are merely illustrative examples for clear explanation and are not intended to limit the implementation. Those skilled in the art will recognize that other variations or modifications can be made based on the above description. It is neither necessary nor possible to exhaustively list all possible implementations here. However, obvious variations or modifications derived therefrom are still within the scope of protection of this invention.

Claims

1. A device for simulating intestinal motility in vitro, characterized in that, include: A flexible tubular body is composed of an inner wall and an outer wall. The flexible tubular body is divided into multiple non-connected segments along the axial direction. Each segment is provided with at least one petal-shaped unit along the circumferential direction. A sandwich space is provided in the petal-shaped unit between the inner wall and the outer wall. The driving mechanism includes at least one injection pump and a connecting pipeline. The injection pump is connected to the interlayer space of the petal unit through the connecting pipeline and is used to control the injection and extraction of fluid in the petal unit to drive the inner wall surface to produce periodic radial deformation. A dialysis bag is disposed in the internal cavity of the flexible tubular body to contain the contents; an permeate cavity is formed between the outer wall of the dialysis bag and the inner wall of the flexible tubular body to contain the dialysis fluid or hypertonic solution. The inlet tube is connected to the dialysis bag and is used to inject the digested sample; Both the injection tube and the sampling tube are connected to the permeate chamber, which facilitates the injection or replacement of dialysate or hypertonic solution into the permeate chamber.

2. The device for simulating intestinal motility in vitro according to claim 1, characterized in that, The thickness of the inner wall surface is less than the thickness of the outer wall surface.

3. The device for simulating intestinal motility in vitro according to claim 1, characterized in that, When the number of petal units in each segment is greater than 1, and the interlayer space between the petal units is connected, the injection pump is connected to the interlayer space of at least one of the petal units through a connecting pipe, for injecting or extracting fluid into the interlayer space.

4. The device for simulating intestinal motility in vitro according to claim 1, characterized in that, When the number of the petal units in each segment is greater than 1, and the interlayer spaces between the petal units are not interconnected, the injection pump is connected to the interlayer space of each petal unit through a connecting pipe for injecting or extracting fluid into the interlayer space.

5. The device for simulating intestinal motility in vitro according to claim 1, characterized in that, It also includes a fixing ring, which is sleeved on the outer wall of the flexible tubular body to fix the flexible tubular body and limit its radial expansion range.

6. The device for simulating intestinal motility in vitro according to claim 1, characterized in that, The flexible tubular body is a coiled section, which is in a meandering coiled shape, and the permeate cavity is filled with dialysis fluid.

7. The device for simulating intestinal motility in vitro according to claim 6, characterized in that, Each segment of the coiled section has at least one petal-shaped unit evenly distributed along the circumferential direction.

8. The device for simulating intestinal motility in vitro according to claim 1, characterized in that, The flexible tubular body is a sac-like segment, which has a bag-like bulging structure, and the permeation cavity is filled with a hypertonic solution.

9. The device for simulating intestinal motility in vitro according to claim 8, characterized in that, Each segment of the sac-like segment has at least one petal-like unit evenly distributed along the circumference. When there are two petal-like units, the sac-like segment is peanut-shaped; when there are three petal-like units, the sac-like segment as a whole is petal-shaped.

10. The device for simulating intestinal motility in vitro according to claim 1, characterized in that, It also includes a heating device for heating the fluid within the injection pump.

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