CN116656473A - High-speed phase flow biological cell breaking device - Google Patents

Abstract

The invention relates to a high-speed flow biological cell crushing device, which comprises a shell, wherein the shell is provided with a first inlet and a first outlet, a first runner, a second runner, a liquid collecting channel, a first valve core, a second valve core and a third valve core are arranged in the shell, one end of a first micropore of the first valve core is sequentially communicated with the first runner and the first inlet, the other end of the first micropore is sequentially communicated with the second runner, a first rotational flow micro-runner of the first valve core, a second micropore of the second valve core and a third rotational flow micro-runner of the third valve core, the liquid collecting channel and the outlet, and the first rotational flow micro-runner, the second micropore and the second rotational flow micro-runner form an X-shaped flow channel.

Description

High-speed phase flow biological cell breaking device

Technical Field

The invention belongs to the technical field of biological cell disruption equipment, and particularly relates to a high-speed phase flow biological cell disruption device.

Background

The traditional high-speed phase flow cell crushing device is characterized in that fluids such as water and the like carrying biological cells are respectively subjected to opposite collision from left and right nozzles to be cut and then contact with the vibration sheet, the biological cells are further crushed by utilizing ultra-high frequency sound waves, compared with other shearing mechanical crushing equipment for processing the biological cells, the cells can be crushed into nano-scale without destroying biological activity, no additional actual is needed to be added, the bioavailability can be improved, the device is widely applied to crushing and extraction of various thalli such as yeast, cefprozil, streptomyces and the like in the fields of microbial pharmacy, DNA recombination and the like, but along with the improvement of the requirements of sample preparation on particle size distribution, when the PDI is required to be lower than 0.1, the cell crushing pressure is mainly determined by the resistance born by the breaking gap of the fluids, and the energy conversion rate is lower.

Therefore, the high-pressure micro-jet of the diamond interaction cavity is adopted, under the action of the pressurizing mechanism, the high pressure generated by the hydraulic pump is utilized, the fluid passes through the valve core with very small aperture to generate fluid with several times of sonic velocity, and the fluid passes through the narrow gaps of the dispersing units quickly to perform strong high-speed impact, in the impact process, the fluid instantaneously converts most of energy, the pressure in the fluid rapidly drops to form supersonic fluid, particles in the fluid collide, cavitation and turbulent flow, the shearing force acts on tiny molecules with nanometer size, the obtained PDI distribution is smaller, but the main defects are that: the cavity is generally Z-shaped and Y-shaped, the impact effect is insufficient, the processing capacity of a single-flow-channel or double-flow-channel intersection structure is small, although the cross-shaped micro-jet cavity is proposed in the prior art, a plurality of independent micro-jets can be formed to increase the processing capacity, the cross-shaped micro-jet cavity is limited by the pressure of a power system, the impact shearing effect is influenced due to insufficient fluid jet speed of an X-shaped cross-shaped cavity, the processing cycle is long due to the need of in-vitro repeated circulation processing, and the thinning degree and uniformity are difficult to meet the requirements.

Secondly, single-stage collision and in-vitro multiple circulation are combined, the fluid movement direction is single, the flow rate loss and the treatment capacity are limited, the power consumption is high, and the processing efficiency and the raw material utilization rate are reduced.

In addition, for the ductile material, the working pressure requirement in the single-phase flow liquid flow system is higher, and meanwhile, a stable speed field is established after a certain distance, so that the damage degree caused by cavitation and flow elimination is smaller, the target surface stress is smaller than the tensile strength of the material, and the crushing requirement is difficult to reach.

Disclosure of Invention

The invention aims to solve at least one of the technical problems to a certain extent, and provides a high-speed phase flow biological cell crushing device which can strengthen impact crushing force by increasing jet flow speed through rotational flow, reduce working pressure requirements, reduce in-vitro circulation times by matching with biphasic micro-jet flow and in-vivo multi-stage impact, and improve biological cell crushing treatment efficiency, crushing fineness and uniformity.

The technical scheme adopted for solving the technical problems is as follows:

the high-speed phase flow biological cell crushing device comprises a shell, wherein the shell is provided with a first inlet and an outlet, a first runner, a second runner, a liquid collecting channel, a first valve core, a second valve core and a third valve core are arranged in the shell, the first valve core is provided with a plurality of first micropores, the first valve core is provided with a first conical surface matched with the second valve core, a plurality of first rotational flow micro-runners are arranged on the first conical surface, the second valve core is provided with a second micropore, the third valve core is provided with a second conical surface matched with the second valve core, the second conical surface is arranged opposite to the first conical surface, and a plurality of second rotational flow micro-runners are arranged on the second conical surface; one end of the first micropore is sequentially communicated with the first runner and the first inlet, and the other end of the first micropore is sequentially communicated with the second runner, the first cyclone micro-runner, the second micropore, the third cyclone micro-runner, the liquid collecting channel and the outlet.

Further, a groove body and a first sleeve are arranged in the shell, the groove body is communicated with the first inlet and the first flow passage, a first flow passage with a radial first valve core of which the opening is gradually reduced is formed in the first sleeve, and a second flow passage is formed between the outer part of the first sleeve and the shell.

Further, the first micropore is perpendicular to the first runner and the second runner, the aperture of the first micropore is gradually expanded towards the direction of the first runner, a second sleeve matched with the first valve core is arranged in the shell, and a plurality of third micropores positioned in the second runner are arranged in the second sleeve.

Further, the aperture of the third micropore is gradually reduced towards the second valve core.

Further, a first gap arranged in a way of being out of position with the third micropore is arranged between the first valve core and the second valve core, and the first gap is communicated with the first micropore, the third micropore and the first rotational flow micro-channel.

Further, a third flow channel and a fourth valve core are arranged in the shell, the fourth valve core is provided with a plurality of third rotational flow micro-channels matched with the second valve core, one end of each third flow channel is communicated with the second flow channel, the other end of each third flow channel corresponds to one end of each third rotational flow micro-channel, and the other end of each third rotational flow micro-channel corresponds to the second rotational flow micro-channel.

Further, a third sleeve matched with the second valve core is arranged in the shell, the second flow channel and the third flow channel are respectively positioned at two sides of the third sleeve, and a plurality of fourth micropores communicated with the second flow channel and the third flow channel are formed in the third sleeve.

Further, the caliber of the fourth micropore gradually tapers to the third flow path direction.

Further, a fourth sleeve matched with the third sleeve and the fourth valve core is arranged in the shell, the fourth sleeve is provided with a plurality of fifth micropores, one end of each fifth micropore is communicated with the third flow channel, and the other end of each fifth micropore corresponds to the third rotational flow micro flow channel.

Further, the caliber of the fifth micropore is gradually reduced to the third rotational flow micro-channel.

Further, a fifth sleeve is arranged between the third valve core and the shell, second gaps are respectively arranged between the third valve core and the fourth valve core, between the third valve core and the fifth sleeve and between the fifth sleeve and the fourth valve core, a plurality of sixth micropores are arranged on the fifth sleeve, one end of each sixth micropore is communicated with the second gaps and the second rotational flow micro-channels in sequence, and the other end of each sixth micropore is communicated with the liquid collecting channel.

Further, the section of the second gap between the inner side of the third valve core and the fourth valve core gradually expands towards the outflow direction.

Further, the section of the second gap among the third valve core, the fourth valve core and the fifth sleeve is of an h-shaped structure.

Further, the high-pressure plunger pump comprises a high-pressure plunger pump and a circulating pipe, wherein two ends of the circulating pipe are respectively communicated with an inlet end of the high-pressure plunger pump and an outlet of the shell, the inlet end of the high-pressure plunger pump is towards the outlet direction of the shell, the circulating pipe is sequentially connected with a first one-way valve, a first inlet pipe, a first outlet pipe and a second one-way valve, stop valves are respectively arranged on the first inlet pipe and the first outlet pipe, and the outlet end of the high-pressure plunger pump is communicated with the first inlet of the shell.

Further, the shell is provided with a second inlet communicated with the second flow passage, the second inlet is connected with a third one-way valve and a second inlet pipe, the first inlet pipe is used for introducing fluid containing biological cells, and the second inlet pipe is used for introducing gas.

Compared with the prior art, the invention has the beneficial effects that:

(1) The first rotational flow micro-flow channel of the first valve core on the first conical surface, the second micropore of the second valve core and the second rotational flow micro-flow channel of the third valve core on the second conical surface can form an X-like cross-shaped flow channel, compared with the traditional Z-like single flow channel or Y-like double flow channel intersection structure, the novel centrifugal flow type biological cell crushing device has a plurality of independent micro-jets, can increase the treatment capacity, simultaneously utilizes centripetal movement through the first rotational flow micro-flow channel, utilizes centrifugal movement through the second rotational flow micro-flow channel, accelerates the fluid flow velocity, has high energy conversion rate and long high-pressure duration, can reduce the working pressure requirement and the extracorporeal circulation times, improves the biological cell crushing treatment efficiency and ensures that the particle size of materials is refined uniformly.

(2) Through first micropore after the first runner, take place first level striking with the second runner, the cross runner of rethread class "X" takes place the second level striking, carry out third level striking through a plurality of third whirl micro-channels of third runner and fourth case after accelerating again, carry out fourth level striking through third case, fourth case and fifth sleeve, constantly change the fluid flow direction, utilize the internal multistage collision to reduce the extracorporeal circulation number, further make the material particle diameter refine evenly, reduce velocity of flow loss and consumption, raise machining efficiency and raw materials utilization ratio.

(3) The turbulence is increased through the biphasic fluid, bubbles in the fluid are excited, high-density cavitation bubbles are generated in the fluid jet flow, and a large number of cavitation bubbles are utilized to collapse in a local micro-area on the cell surface to generate strong micro-jet impact force, so that the stress of the target surface is easily higher than the tensile strength of the material, the crushing requirement is met, the biological cell crushing treatment efficiency is further improved, and the particle size of the material is refined uniformly.

Drawings

The foregoing and/or additional aspects and advantages of the invention will become apparent and may be better understood from the following description of embodiments taken in conjunction with the accompanying drawings in which:

FIG. 1 is an external block diagram of an embodiment of the present invention;

FIG. 2 is a schematic cross-sectional view of an embodiment of the present invention;

FIG. 3 is a schematic view of a cross-section of the interior of a housing according to an embodiment of the invention;

FIG. 4 is a top exploded view of one embodiment of the present invention;

FIG. 5 is a bottom exploded view of one embodiment of the present invention;

FIG. 6 is a perspective view of a first valve cartridge according to an embodiment of the present invention;

FIG. 7 is a perspective view of a second valve cartridge according to an embodiment of the present invention;

FIG. 8 is a perspective view of a third valve core according to an embodiment of the present invention;

fig. 9 is a perspective view of a fourth valve element according to an embodiment of the present invention.

The marks in the figure: the housing 1, the first housing 101, the first notch 1011, the second notch 1012, the second housing 102, the sixth notch 1021, the seventh notch 1022, the third housing 103, the fourth housing 104;

the device comprises a first inlet 2, an outlet 3, a first flow channel 4, a second flow channel 5, a liquid collecting channel 6, a first valve core 7, a first micropore 701, a first conical surface 702 and a first rotational flow micro-channel 703;

the second valve core 8, the second micro-hole 801, the third valve core 9, the second conical surface 901, the second rotational flow micro-channel 902, the tank body 10, the first sleeve 11, the second sleeve 12, the third micro-hole 121, the third notch 122, the fourth notch 123, the first gap 13, the third channel 14, the fourth valve core 15 and the third rotational flow micro-channel 151;

third sleeve 16, fourth micro-hole 161, fifth notch 162, fourth sleeve 17, fifth micro-hole 171, eighth notch 172, fifth sleeve 18, sixth micro-hole 181, second gap 19;

the high-pressure plunger pump 20, the circulating pipe 21, the first check valve 22, the first inlet pipe 23, the outlet pipe 24, the second check valve 25, the stop valve 26, the second inlet 27, the third check valve 28, the second inlet pipe 29, the first sealing ring 30 and the second sealing ring 31.

Detailed Description

Embodiments of the present invention are described in detail below, examples of which are illustrated in the accompanying drawings, wherein like or similar reference numerals refer to like or similar elements or elements having like or similar functions throughout. The embodiments described below by referring to the drawings are illustrative and intended to explain the present invention and should not be construed as limiting the invention.

In the description of the present invention, it should be understood that the terms "center," "longitudinal," "transverse," "length," "width," "thickness," "upper," "lower," "axial," "radial," "vertical," "horizontal," "inner," "outer," and the like indicate orientations or positional relationships based on the orientation or positional relationships shown in the drawings, merely to facilitate describing the present invention and simplify the description, and do not indicate or imply that the devices or elements referred to must have a specific orientation, be configured and operated in a specific orientation, and therefore should not be construed as limiting the present invention. Furthermore, the terms "first," "second," and the like, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include one or more such feature. In the description of the present invention, the meaning of "a plurality" or "a number" means two or more, unless specifically defined otherwise.

In the present invention, unless explicitly specified and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly and may be, for example, fixedly connected, detachably connected, or integrally connected; can be directly connected or indirectly connected through an intermediate medium, and can be communication between two elements. The specific meaning of the above terms in the present invention can be understood by those of ordinary skill in the art according to the specific circumstances.

As shown in fig. 1-9, in a preferred embodiment of the high-speed phase flow biological cell disruption device according to the present invention, the high-speed phase flow biological cell disruption device includes a housing 1, the housing 1 is provided with a first inlet 2 and an outlet 3, a first flow channel 4, a second flow channel 5, a liquid collecting channel 6, a first valve core 7, a second valve core 8 and a third valve core 9 are provided in the housing 1, the first valve core 7 is provided with a plurality of first micro-holes 701, the first valve core 7 is provided with a first conical surface 702 matched with the second valve core 8, the first conical surface 702 is provided with a plurality of first rotational flow micro-flow channels 703, the second valve core 8 is provided with a second micro-hole 801, the third valve core 9 is provided with a second conical surface 901 matched with the second valve core 8, the second conical surface 901 is provided opposite to the first conical surface 702, and the second conical surface 901 is provided with a plurality of second rotational flow micro-channels 902;

one end of the first micro-hole 701 is sequentially communicated with the first flow channel 4 and the first inlet 2, and the other end of the first micro-hole 701 is sequentially communicated with the second flow channel 5, the first rotational flow micro-channel 703, the second micro-hole 801, the third rotational flow micro-channel 151, the liquid collecting channel 6 and the outlet 3.

Further, a groove body 10 and a first sleeve 11 are arranged in the shell 1, the groove body 10 is communicated with the first inlet 2 and the first flow channel 4, the first sleeve 11 is internally provided with the first flow channel 4 with a radial first valve core 7, a second flow channel 5 is formed between the outer part of the first sleeve 11 and the shell 1, fluid which enters the shell 1 from the first inlet 2 and contains biological cells firstly collides with two sides of the groove body 10, uniformity of mixing and dissolving of the biological cells and the fluid is promoted, and crushing uniformity is improved.

Further, the housing 1 includes a first housing 101 and a second housing 102, the first inlet 2 is disposed on the first housing 101, the first housing 101 is provided with a first notch 1011, the first notch 1011 and the second housing 102 form a groove 10, the lower end of the first sleeve 11 is in limit fit with the second housing 102, so that the first sleeve 11 is convenient to be positioned and installed, and a first sealing ring 30 is disposed between the third sleeve 16 and the second housing 102, so as to improve the sealing performance between the third sleeve 16 and the second housing 102, and prevent leakage between the first flow channel 4 and the second flow channel 5.

Further, the first housing 101 is provided with a second notch 1012 in limit fit with the second housing 102, so that rapid alignment is facilitated, and the first housing 101 and the second housing 102 can be sealed through welding connection.

Further, the first micro-holes 701 are perpendicular to the first flow channel 4 and the second flow channel 5, the diameter of the first micro-holes 701 gradually expands towards the direction of the first flow channel 4, so that the fluid containing biological cells in the first flow channel 4 is accelerated to be ejected outwards after passing through the first micro-holes 701, the second sleeve 12 matched with the first valve core 7 is arranged in the shell 1, and the second sleeve 12 is provided with a plurality of third micro-holes 121 positioned in the second flow channel 5, so that the gas in the second flow channel 5 is uniformly dispersed through a plurality of micro-holes, and can be opposite to the fluid containing biological cells, thereby further improving the crushing efficiency and uniformity.

Further, the second sleeve 12 is provided with a third notch 122 and a fourth notch 123, the third notch 122 is in limit fit with the first sleeve 11, the second sleeve 12 is rapidly positioned and installed on the first sleeve 11, and the fourth notch 123 is in limit fit with the first valve core 7 and is used for rapidly positioning and installing the first valve core 7 on the second sleeve 12.

Further, the diameter of the third micropore 121 tapers toward the second valve core 8, so that the gas in the second flow channel 5 flows through the third micropore 121 in an accelerating manner, and the flow speed and the crushing effect are further improved.

Further, a first gap 13 arranged in a manner of being out of position with the third micro-hole 121 is arranged between the first valve core 7 and the second valve core 8, the first gap 13 is communicated with the first micro-hole 701, the third micro-hole 121 and the first rotational flow micro-channel 703, so that a channel with an L-shaped cross section can be formed among the first valve core 7, the second valve core 8 and the second sleeve 12, and after the fluid flowing out of the first micro-hole 701 and the fluid flowing out of the third micro-hole 121 are intersected, a first-stage collision occurs, the second valve core 8 can be impacted, and then flows to the first rotational flow micro-channel 703 through the first gap 13, so that the collision effect and the crushing effect are further improved.

Further, a third flow channel 14 and a fourth valve core 15 are disposed in the housing 1, the fourth valve core 15 is provided with a plurality of third rotational flow micro flow channels 151 matched with the second valve core 8, one end of the third flow channel 14 is communicated with the second flow channel 5, the other end of the third flow channel 14 corresponds to one end of the third rotational flow micro flow channel 151, and the other end of the third rotational flow micro flow channel 151 corresponds to the second rotational flow micro flow channel 902.

After the gas in the second flow channel 5 collides with the fluid jet of the first flow channel 4 and the second stage of collision is intersected at the second micro-hole 801 through the first rotational flow micro-channel 703, the gas can collide with the accelerated gas flowing out from the third flow channel 14 through the third rotational flow micro-channel 151 in the third stage when the gas flows out along the second rotational flow micro-channel 902 in an accelerating way, so that the shearing, collision and cavitation crushing effects are further enhanced, the crushing efficiency is improved, and the extracorporeal circulation is reduced.

Further, a third sleeve 16 matched with the second valve core 8 is arranged in the casing 1, the second flow channel 5 and the third flow channel 14 are respectively located at two sides of the third sleeve 16, a plurality of fourth micropores 161 communicated with the second flow channel 5 and the third flow channel 14 are formed in the third sleeve 16, and gas in the second flow channel 5 can be uniformly dispersed to the second flow channel 5 through the plurality of fourth micropores 161, so that the efficiency and uniformity are further improved.

Further, the diameter of the fourth micro-holes 161 is reduced toward the third flow channel 14, so that the flow rate of the gas passing through the fourth micro-holes 161 can be increased.

Further, the third sleeve 16 is provided with a fifth notch 162 in limit fit with the second valve core 8, so that the second valve core 8 can be positioned on the third sleeve 16 quickly, and meanwhile, the fluid ejected from the first micro-holes 701 can strike on the inner wall of the third sleeve 16, so as to increase the striking effect.

Further, the housing 1 includes a third housing 103, the second housing 102 is provided with a sixth notch 1021 and a seventh notch 1022, the sixth notch 1021 is in limit fit with the third sleeve 16, so that the third sleeve 16 is convenient to be quickly positioned and mounted on the second housing 102, the seventh notch 1022 is in limit fit with the third housing 103, so that the third housing 103 is convenient to be quickly positioned and mounted on the second housing 102, the third housing 103 is in welded connection with the second housing 102, a second flow passage 5 is formed between the first sleeve 11 and the third sleeve 16, and a third flow passage 14 is formed between the third sleeve 16 and the third housing 103, so that the quick mounting is facilitated.

Further, a fourth sleeve 17 matched with the third sleeve 16 and the fourth valve core 15 is disposed in the housing 1, the fourth sleeve 17 is provided with a plurality of fifth micropores 171, one end of the fifth micropores 171 is communicated with the third flow channel 14, the other end of the fifth micropores 171 corresponds to the third swirl micro-flow channel 151, and gas in the third flow channel 14 can be uniformly dispersed into the third swirl micro-flow channel 151 through the plurality of fifth micropores 171, so that the efficiency and uniformity are further improved.

Further, the diameter of the fifth micro holes 171 is tapered toward the third cyclone micro flow channel 151, so that the flow rate of the gas passing through the fifth micro holes 171 can be increased.

Further, the fourth sleeve 17 is provided with an eighth notch 172 in limit fit with the third sleeve 16, so that the fourth sleeve 17 is convenient to quickly position and mount on the third sleeve 16, the third housing 103 is provided with a ninth notch in limit fit with the fourth valve core 15, so that the fourth valve core 15 is convenient to quickly position and mount on the fourth sleeve 17 and the third housing 103, and the disassembly and assembly are convenient.

Further, the housing 1 includes a fourth housing 104, a mating thread is provided between the fourth housing 104 and the third housing 103, a second sealing ring 31 is provided between the fourth housing 104 and the fourth valve core 15, the third valve core 9 is connected with the fourth housing 104, the outlet 3 is disposed on the fourth housing 104, the fourth valve core 15 can be detachably connected with the third housing 103 through the fourth housing 104, and the tightness between the fourth valve core 15 and the fourth housing 104 is improved through the second sealing ring 31, so that leakage is avoided, and disassembly and assembly are convenient.

Further, a fifth sleeve 18 is arranged between the third valve core 9 and the casing 1, a second gap 19 is arranged between the third valve core 9 and the fourth valve core 15, a second gap 19 is arranged between the third valve core 9 and the fifth sleeve 18, and a second gap 19 is arranged between the fifth sleeve 18 and the fourth valve core 15, a plurality of sixth micropores 181 are arranged on the fifth sleeve 18, one end of each sixth micropore 181 is sequentially communicated with the second gap 19 and the second rotational flow micro-channel 902, and the other end of each sixth micropore 181 is communicated with the liquid collecting channel 6.

After the accelerated fluid passing through the second swirling flow micro flow channel 902 collides with the gas passing through the third swirling flow micro flow channel 151, the accelerated fluid can collide between the third valve core 9, the fourth valve core 15 and the fifth sleeve 18 along the second gap 19, perform fourth-stage collision, flow to the liquid collecting channel 6 through the sixth micro-holes 181, and finally be discharged from the outlet 3, so that the crushing efficiency and effect can be further improved, and the extracorporeal circulation is reduced.

Further, the section of the second gap 19 between the inner side of the third valve core 9 and the fourth valve core 15 is gradually widened towards the outflow direction, so that the fluid flow velocity between the inner side of the third valve core 9 and the fourth valve core 15 can be reduced, the shearing effect of the fluid between the top of the third valve core 9 and the fourth valve core 15 can be improved, and the crushing effect can be further improved.

Further, the section of the second gap 19 between the third valve core 9, the fourth valve core 15 and the fifth sleeve 18 is in an h-shaped structure, so that after the fluid impacts the third valve core 9, the fluid passes through the third valve core 9 and the fourth valve core 15, flows to the gap between the fourth valve core 15 and the fifth sleeve 18 to impact the fourth valve core 15, returns to the sixth micro-hole 181, and further improves the impact strength and the crushing effect.

Further, the high-pressure plunger pump comprises a high-pressure plunger pump 20 and a circulating pipe 21, wherein two ends of the circulating pipe 21 are respectively communicated with an inlet end of the high-pressure plunger pump 20 and an outlet 3 of the shell 1, the inlet end of the high-pressure plunger pump 20 is towards the outlet 3 of the shell 1, the circulating pipe 21 is sequentially connected with a first check valve 22, a first inlet pipe 23, a second check valve 24 and a second check valve 25, stop valves 26 are respectively arranged on the first inlet pipe 23 and the second inlet pipe 24, and an outlet end of the high-pressure plunger pump 20 is communicated with the first inlet 2 of the shell 1.

Further, the casing 1 is provided with a second inlet 27 communicated with the second flow channel 5, the second inlet 27 is located on the second casing 102, the second inlet 27 is connected with a third one-way valve 28 and a second inlet pipe 29, the first inlet pipe 23 is used for introducing fluid containing biological cells, the second inlet pipe 29 is used for introducing gas, and the crushing effect is further improved through two-phase flow.

The working principle of the high-speed phase flow biological cell disruption device comprises the following steps:

the stop valve 26 of the first inlet pipe 23 is opened, the stop valve 26 of the outlet pipe 24 is closed, fluid containing biological cells is introduced into the first inlet pipe 23, when the plunger of the high-pressure plunger pump 20 moves backward, the pressure in the high-pressure plunger pump 20 is reduced, the first one-way valve 22 is opened, fluid containing biological cells enters the high-pressure plunger pump 20, when the plunger moves forward, the first one-way valve 22 is closed, the fluid is injected into the first inlet 2 of the shell 1, and high-pressure gas is introduced into the second inlet pipe 29 to open the third one-way valve 28.

The fluid entering the first inlet 2 passes through the groove body 10, part of the fluid impacts the first shell 101 and then turns back, enters the first flow channel 4 in the first sleeve 11 along with the rest of the fluid, and flows along the first flow channel 4, impacts the inside of the first valve core 7, then is dispersed along a plurality of second micro holes 801, and is ejected to the third sleeve 16, meanwhile, the gas entering the second inlet 27 is dispersed to the second flow channel 5 and the third flow channel 14, the gas flowing along the second flow channel 5 is dispersed through the third micro holes 121 of the second sleeve 12, and is ejected to the second valve core 8, so that after the fluid containing biological cells is intersected with the gas, the first-stage impact occurs, the fluid impacts the third sleeve 16, and flows to the first rotational flow micro flow channel 703 along the first gap 13 between the first valve core 7 and the second valve core 8 after turning back, and high-density cavitation bubbles are generated in the fluid jet stream.

The ends of the first cyclone micro-channels 703 are communicated at the taper angle of the first conical surface 702 and are in an arc structure which is arranged around the first valve core 7 at intervals, the ends of the second cyclone micro-channels 902 are communicated at the taper angle of the second conical surface 901 and are in an arc structure which is arranged around the third valve core 9 at intervals, so that mixed fluid accelerated along the first cyclone micro-channels is intersected at the second micropores 801 to generate second-stage collision, high-pressure fluid passes through between the narrow first cyclone micro-channels 703 and the second micropores 801 rapidly, at the moment, the supersonic velocity formed by the rapid decrease of the pressure in the fluid is generated, particles in the fluid collide, cavitation and leakage flow, and the shearing force acts on fine molecules with the split nanometer size, and then the mixed fluid accelerated along the second cyclone micro-channels 902 is ejected.

Meanwhile, the gas in the second flow channel 5 is uniformly dispersed to the second flow channel 5 through a plurality of fourth micropores 161 of the third sleeve 16, the gas in the third flow channel 14 is uniformly dispersed to the third rotational flow micro-channel 151 through a plurality of fifth micropores 171 of the fourth sleeve 17, the end parts of a plurality of second rotational flow micro-channels 902 are communicated at the center of the fourth valve core 15 and are in an arc-shaped structure which is arranged around the fourth valve core 15 at intervals, and the mixed fluid flowing out along the second rotational flow micro-channel 902 and the accelerated gas flowing out through the third rotational flow micro-channel 151 are subjected to third-stage collision to further split nano-sized fine molecules.

After striking the third valve core 9, the mixed fluid after striking the third stage strikes the fourth valve core 15 through the third valve core 9 and the fourth valve core 15, then flows to the gap between the fourth valve core 15 and the fifth sleeve 18 to strike the fourth valve core 15, and the fourth stage striking can generate strong shearing, then returns to flow to the sixth micro-hole 181, flows to the liquid collecting channel 6 through the sixth micro-hole 181, and finally is discharged from the outlet 3 to enter the circulating pipe 21.

The shutoff valve 26 of the first inlet pipe 23 and the shutoff valve 26 of the outlet pipe 24 are closed, the fluid in the circulation pipe 21 is pumped into the housing 1 again by the repeated movement of the high-pressure plunger pump 20, the above-mentioned operation is repeated, the cyclic crushing processing is performed, after the processing, the shutoff valve 26 of the first inlet pipe 23 is closed, the shutoff valve 26 of the outlet pipe 24 is opened, and the processed fluid containing biological cells can be discharged from the outlet pipe 24.

After the fluid of the device is dispersed by the first flow channel 4 through a plurality of first micropores 701, a first rotational flow micro-channel 703 of a first valve core 7 on a first conical surface 702, a second micropore 801 of a second valve core 8 and a second rotational flow micro-channel 902 of a third valve core 9 on a second conical surface 901 can form an X-like cross-shaped flow channel, compared with the existing Z-shaped single flow channel or Y-shaped double flow channel intersection structure, the device has a plurality of independent micro-jets, the device can increase the treatment capacity, simultaneously, the first rotational flow micro-channel 703 utilizes centripetal movement, and the second rotational flow micro-channel 902 utilizes centrifugal movement to accelerate the fluid flow velocity, so that the pressure of a power system and the high-pressure plunger pump 20 to the fluid can be reduced, the problem that the existing X-shaped cross-shaped cavity is insufficient in fluid jet flow is solved, the energy conversion rate is high, the high-pressure duration time is long, the working pressure requirement and the number of in vitro circulation are reduced, the material particle diameter is thinned through high-frequency shearing, the pressure of the material particle pair and the huge pressure between the material particle pair, the impact shearing effect is improved, the material particle diameter is uniform, and the uniform I is subjected to uniform and the uniform distribution of the same force in the channel is smaller when the channel is subjected to the uniform I.

The fluid of the device passes through the first micro holes 701 and then collides with the second flow passage 5 at the first stage, then collides with the second stage through the cross-shaped flow passage similar to the X shape, then collides with the third stage through the third flow passage 14 and a plurality of third rotational flow micro flow passages 151 of the fourth valve core 15 after accelerating, then collides with the fourth stage through the third valve core 9, the fourth valve core 15 and the fifth sleeve 18, the fluid flow direction is continuously changed, the extracorporeal circulation times are reduced by utilizing the multi-stage collision, the particle size of the material is further thinned uniformly, the flow speed loss and the power consumption are reduced, and the processing efficiency and the raw material utilization rate are improved.

The fluid of the device increases turbulence through the biphasic fluid, and excites bubbles in the fluid, the bubbles are involved into jet flow to further grow, so that high-density cavitation bubbles are generated in the fluid jet flow, and the stress of a target surface is easily higher than the tensile strength of a material by utilizing strong micro-jet impact force generated by collapse of a large number of cavitation bubbles in a local micro-area on the surface of the cell, so that the crushing requirement is met, and the particle size of the material is further thinned uniformly.

The above list of detailed descriptions is only specific to practical embodiments of the present invention, and they are not intended to limit the scope of the present invention, and all equivalent embodiments or modifications that do not depart from the spirit of the present invention should be included in the scope of the present invention.

Claims (10)

1. The utility model provides a high-speed flow biological cell breaker, its characterized in that includes casing (1), casing (1) are equipped with first import (2) and export (3), are equipped with first runner (4), second runner (5), liquid collecting channel (6), first case (7), second case (8) and third valve core (9) in casing (1), first case (7) are equipped with a plurality of first micropore (701), first case (7) are equipped with first conical surface (702) with second case (8) complex, be equipped with a plurality of first whirl micro-channel (703) on first conical surface (702), second case (8) are equipped with second micropore (801), third valve core (9) are equipped with second conical surface (901) with second case (8) complex, second conical surface (901) are set up with first conical surface (702) opposite direction, second conical surface (901) are equipped with a plurality of second whirl micro-channel (902);

one end of the first micropore (701) is sequentially communicated with the first flow channel (4) and the first inlet (2), and the other end of the first micropore (701) is sequentially communicated with the second flow channel (5), the first rotational flow micro-channel (703), the second micropore (801), the third rotational flow micro-channel (151), the liquid collecting channel (6) and the outlet (3).

2. The high-speed phase flow biological cell disruption device according to claim 1, wherein a groove body (10) and a first sleeve (11) are arranged in the shell (1), the groove body (10) is communicated with the first inlet (2) and the first flow channel (4), the first sleeve (11) is internally provided with a first flow channel (4) with a radially tapered first valve core (7), and a second flow channel (5) is formed between the outside of the first sleeve (11) and the shell (1).

3. The high-speed phase flow biological cell disruption device as claimed in claim 1, wherein the first micro-holes (701) are perpendicular to the first flow channel (4) and the second flow channel (5), the aperture of the first micro-holes (701) gradually expands towards the direction of the first flow channel (4), a second sleeve (12) matched with the first valve core (7) is arranged in the shell (1), a plurality of third micro-holes (121) positioned in the second flow channel (5) are arranged in the second sleeve (12), and the aperture of the third micro-holes (121) gradually expands towards the second valve core (8).

4. A high-speed phase flow biological cell disruption device according to claim 3, wherein a first gap (13) arranged in a way of being away from the third micropore (121) is arranged between the first valve core (7) and the second valve core (8), and the first gap (13) is communicated with the first micropore (701), the third micropore (121) and the first rotational flow micro-channel (703).

5. The high-speed phase flow biological cell disruption device according to claim 1, wherein a third flow channel (14) and a fourth valve core (15) are arranged in the shell (1), the fourth valve core (15) is provided with a plurality of third rotational flow micro-channels (151) matched with the second valve core (8), one end of the third flow channel (14) is communicated with the second flow channel (5), the other end of the third flow channel (14) corresponds to one end of the third rotational flow micro-channel (151), and the other end of the third rotational flow micro-channel (151) corresponds to the second rotational flow micro-channel (902).

6. The high-speed phase flow biological cell disruption device according to claim 5, wherein a third sleeve (16) matched with the second valve core (8) is arranged in the shell (1), the second flow channel (5) and the third flow channel (14) are respectively positioned at two sides of the third sleeve (16), a plurality of fourth micropores (161) communicated with the second flow channel (5) and the third flow channel (14) are arranged on the third sleeve (16), and the caliber of the fourth micropores (161) is gradually reduced towards the direction of the third flow channel (14).

7. The high-speed phase flow biological cell disruption device according to claim 6, wherein a fourth sleeve (17) matched with the third sleeve (16) and the fourth valve core (15) is arranged in the shell (1), the fourth sleeve (17) is provided with a plurality of fifth micropores (171), one end of each fifth micropore (171) is communicated with the third flow channel (14), the other end of each fifth micropore (171) corresponds to the third rotational flow micro-channel (151), and the caliber of each fifth micropore (171) is gradually reduced to the third rotational flow micro-channel (151).

8. The high-speed phase flow biological cell disruption device according to claim 5, wherein a fifth sleeve (18) is arranged between the third valve core (9) and the shell (1), second gaps (19) are respectively arranged between the third valve core (9) and the fourth valve core (15), between the third valve core (9) and the fifth sleeve (18) and between the fifth sleeve (18) and the fourth valve core (15), a plurality of sixth micropores (181) are arranged on the fifth sleeve (18), one end of each sixth micropore (181) is sequentially communicated with the second gaps (19) and the second rotational flow micro-channels (902), and the other end of each sixth micropore (181) is communicated with the liquid collecting channel (6).

9. The high-speed phase flow biological cell disruption device according to claim 5, wherein a second gap (19) between the inner side of the third valve core (9) and the fourth valve core (15) is gradually widened in the outflow direction, and the second gap (19) between the third valve core (9), the fourth valve core (15) and the fifth sleeve (18) is of an h-shaped structure in cross section.

10. The high-speed phase flow biological cell disruption device according to any one of claims 1 to 9, comprising a high-pressure plunger pump (20) and a circulation pipe (21), wherein two ends of the circulation pipe (21) are respectively communicated with an inlet end of the high-pressure plunger pump (20) and an outlet (3) of the shell (1), the inlet end of the high-pressure plunger pump (20) is towards the outlet (3) of the shell (1), the circulation pipe (21) is sequentially connected with a first check valve (22), a first inlet pipe (23), a second check valve (24) and a second check valve (25), the first inlet pipe (23) and the second inlet pipe (24) are respectively provided with a stop valve (26), the first inlet pipe (23) is used for introducing fluid containing biological cells, the outlet end of the high-pressure plunger pump (20) is communicated with the first inlet (2) of the shell (1), the shell (1) is provided with a second inlet (27) communicated with a second flow channel (5), and the second inlet (27) is connected with a third check valve (28) and a second inlet pipe (29) for introducing gas.