CN118022111A - Atomizing device - Google Patents

Abstract

The invention provides an atomizing device, comprising a pressure metered dose inhaler, which comprises a shell with a nozzle, a storage tank installed in the shell, a metering chamber arranged in the storage tank, a metering valve connected to the metering chamber and an expansion chamber communicated with the metering valve, and the atomizing device also comprises: a connecting pipe, a first end of which is communicated with an outlet of the expansion chamber; a clamping sleeve, a first end of which is communicated with a second end of the connecting pipe, and a second end of which faces the nozzle; a micro-channel chip fixed inside the clamping sleeve, comprising: a chip body, which comprises a first surface, and the first surface is parallel to the extension direction of the clamping sleeve; a plurality of guide channels, which are arranged at one end of the first surface facing the expansion chamber; a first injection channel and a second injection channel, which are opened on the first surface, are both arranged on a side of the guide channel facing the nozzle, are respectively communicated with the guide channel, and both extend to the end of the chip body, and the extension lines of the two facing the nozzle intersect; a sealing ring is arranged between the micro-channel chip and the inner wall of the clamping sleeve.

Description

Atomization device

Technical Field

The invention relates to the technical field of inhalation medication devices, and in particular to an atomization device.

Background technique

Inhalation drug delivery refers to a drug delivery method in which drugs are inhaled from the respiratory tract through a specific device. Currently, many respiratory diseases still lack ideal treatment methods. Due to its own characteristics and unique advantages, inhalation drug delivery has gradually become the best treatment for diseases such as asthma and chronic obstructive pulmonary disease.

Inhaled medications require dedicated delivery devices. There are three main types of inhaled delivery devices: dry powder inhalers (DPIs), pressurized metered dose inhalers (pMDIs), and nebulizers. These devices are designed to aerosolize medications to produce an aerosol for delivery to the lungs. An aerosol is a group of particles with a low settling volume. The effective mass mean aerodynamic diameter of a therapeutic aerosol is between 0.5 and 5 μm.

pMDI is one of the many inhalation drug delivery technologies currently available. It is a portable device that can be driven manually and can be used by patients for inhalation drug delivery anytime and anywhere. pMDI is mainly composed of a shell, a storage tank, a metering chamber, a metering valve and an expansion chamber. When started, the storage tank is manually pressed to use the decompression gasification of the propellant in the storage tank to spray the compound of the drug, propellant and excipients, and deliver the precise atomized dose of the compound to the expansion chamber through the metering chamber and the metering valve. The delivery amount is usually 25-100μL. The aerosol atomized in the expansion chamber is discharged from the nozzle of the shell for inhalation by the human lungs. However, due to the influence of the particle size of the aerosol generated by pMDI, a large part of the aerosol particles will be deposited in the oropharynx, and the lung deposition rate is only 20%-40%.

Summary of the invention

In view of this, the present invention provides an atomization device, which combines a pressure metered dose inhaler with a micro-channel chip. During the process of aerosol particles ejected from the pressure metered dose inhaler being ejected through a first ejection channel and a second ejection channel on the micro-channel chip, the two jets collide at a certain angle to generate atomized aerosol particles with a smaller particle size, thereby extending the spray time and providing a higher lung deposition rate, so as to overcome the defects of the prior art.

The atomizing device provided by the present invention comprises a pressure metered dose inhaler, which comprises a shell with a nozzle, a storage tank installed in the shell, a metering chamber arranged in the storage tank, a metering valve connected to the metering chamber, and an expansion chamber connected to the metering valve through an output pipe, and further comprises: a connecting pipe, a first end of which is connected to an outlet of the expansion chamber; a clamping sleeve, a first end of which is connected to a second end of the connecting pipe, and the second end of the clamping sleeve faces the nozzle; a microchannel chip, which is fixed inside the clamping sleeve, and comprises: a chip main The chip body comprises a first surface, which is parallel to the extension direction of the clamping sleeve; a plurality of guide channels, which are opened at one end of the first surface facing the expansion chamber; a first injection channel and a second injection channel, which are opened on the first surface, are both arranged on the side of the guide channel facing the nozzle, are respectively connected with the guide channel, and both extend to the end of the chip body, and the extension lines of the two toward the nozzle intersect; a sealing ring is arranged between the microchannel chip and the inner wall of the clamping sleeve.

Optionally, the microchannel chip of the atomization device further includes: a filter component, and the filter component is arranged between the guide channel and the first injection channel and the second injection channel.

Optionally, the filter assembly includes: a plurality of filter plates, and the plurality of filter plates are arranged at intervals in a direction toward the first injection channel and the second injection channel.

Optionally, the atomization device further comprises: a limiting member, the limiting member is connected to the second end of the clamping sleeve, and a spray hole is formed through the limiting member.

Optionally, an inner wall of the second end of the clamping sleeve is provided with an internal thread, and the limiting member is threadably connected to the clamping sleeve.

Optionally, an angle between the extension lines of the first injection channel and the second injection channel toward the nozzle is 60°-90°.

Optionally, a distance between the first injection channel and the second injection channel at the end of the chip body is 160 μm-320 μm.

Optionally, the first injection channel has a depth of 50 μm-75 μm and a width of 100 μm-150 μm at the end of the chip body; and/or the second injection channel has a depth of 50 μm-75 μm and a width of 100 μm-150 μm at the end of the chip body.

Optionally, the microchannel chip is manufactured by etching, bonding and cutting processes.

Optionally, the clamping sleeve is made of high pressure resistant material.

Compared with the prior art, the above technical solution provided by the present invention has at least the following beneficial effects:

By using the atomization device of the present invention, a pressure metered dose inhaler is combined with a micro-channel chip. During the process of aerosol particles ejected from the pressure metered dose inhaler being ejected through the first ejection channel and the second ejection channel on the micro-channel chip, the two jets collide at a certain angle to generate atomized aerosol particles with a smaller particle size, thereby extending the spray time, improving the lung deposition rate, enhancing the hand-mouth coordination during use, and achieving a better drug delivery effect.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG1 is a schematic diagram of an atomization device according to an embodiment of the present invention;

FIG2 is a 3D schematic diagram of the microchannel chip of the atomization device shown in FIG1 ;

FIG. 3 is a side view of the microchannel chip shown in FIG. 2 .

Reference numerals:

1: pressure metered dose inhaler; 11: housing; 111: nozzle; 12: storage tank; 13: metering chamber; 14: metering valve; 15: output pipe; 16: expansion chamber; 2: connecting pipe; 3: clamping sleeve; 4: microchannel chip; 41: chip body; 42: guide channel; 43: first injection channel; 44: second injection channel; 45: filter assembly; 451: filter plate; 5: limiter.

Detailed ways

The embodiments of the present invention will be further described below in conjunction with the accompanying drawings. In the description of the present invention, it should be noted that the orientations or positional relationships indicated by the terms "center", "up", "down", "left", "right", "vertical", "horizontal", "inside", "outside", etc. are based on the orientations or positional relationships shown in the accompanying drawings, and are only simplified descriptions for the convenience of describing the present invention, rather than indicating or implying that the device or component referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore cannot be understood as limiting the present invention. In addition, the terms "first", "second", and "third" are used for descriptive purposes only and cannot be understood as indicating or implying relative importance. Among them, the terms "first position" and "second position" are two different positions.

FIG. 1 is a schematic diagram of an atomization device according to an embodiment of the present invention; FIG. 2 is a 3D schematic diagram of a microchannel chip of the atomization device shown in FIG. 1 ; and FIG. 3 is a side view of the microchannel chip shown in FIG. 2 .

As shown in FIGS. 1 to 3 , the atomization device includes a pressure metered dose inhaler 1 , a connecting tube 2 , a clamping sleeve 3 and a microchannel chip 4 .

The pressure metered dose inhaler 1 comprises a housing 11 with a nozzle 111, a storage tank 12 installed in the housing 11, a metering chamber 13 arranged in the storage tank 12, a metering valve 14 connected to the metering chamber 13, and an expansion chamber 16 connected to the metering valve 14 through an output pipe 15. The first end of the connecting pipe 2 is connected to the outlet of the expansion chamber 16; the first end of the clamping sleeve 3 is connected to the second end of the connecting pipe 2, and the second end of the clamping sleeve 3 faces the nozzle 111. The microchannel chip 4 is fixed inside the clamping sleeve 3, and comprises a chip body 41, a plurality of guide channels 42, a first injection channel 43 and a second injection channel 44. The chip body 41 includes a first surface, which is parallel to the extension direction of the clamping sleeve 3; a plurality of the guide channels 42 are opened at one end of the first surface facing the expansion chamber 16; the first injection channel 43 and the second injection channel 44 are opened on the first surface, both are arranged on the side of the guide channel 42 facing the nozzle 111, are connected to the guide channel 42 respectively, and both extend to the end of the chip body 41, and the extension lines of the two in the direction of the nozzle 111 intersect. A sealing ring (not shown) is arranged between the microchannel chip 4 and the inner wall of the clamping sleeve 3.

As shown in FIG1 , the storage tank 12 is inverted in the housing 11, and the upper part of the storage tank 12 is propellant gas, and the lower part is liquid medicine. When in use, the storage tank 12 is manually pressed, and then under the thrust of the propellant gas in the storage tank 12, the liquid medicine passes through the metering chamber 13, and the liquid medicine that meets the one-time injection dose is ejected from the metering valve 14, and enters the expansion chamber 16 through the output pipe 15 connected to the metering valve 14, and after being atomized into aerosol particles in the expansion chamber 16, it is ejected from the outlet of the expansion chamber 16 into the connecting pipe 2, and then enters the clamping sleeve 3 connected to it through the connecting pipe 2, and the micro-channel chip 4 is arranged in the clamping sleeve 3, and the space between the inner wall of the clamping sleeve 3 and the micro-channel chip 4 is filled with the sealing ring, so that the liquid medicine jet entering the clamping sleeve 3 can only continue to be ejected along the first surface through the multiple guide channels 42 opened on the first surface of the chip body 41, and They respectively enter the first jet channel 43 and the second jet channel 44 connected to the guide channel 42 to form two jet streams, which are respectively ejected along the first jet channel 43 and the second jet channel 44. Since the first jet channel 43 and the second jet channel 44 both extend to the end of the chip body 41 and the extension lines toward the nozzle 111 intersect, the two jet streams are ejected from the two jet channels at a certain angle and collide with each other, generating atomized aerosol particles with smaller particle size after the collision, and ejected through the port of the clamping sleeve 3 and the nozzle 111 for inhalation by the user. Since the particle size of the aerosol particles is further reduced, it is more difficult to deposit and remains suspended longer, the aerosol particles settled in the oropharynx are reduced, and the aerosol particles settled in the lungs are increased.

By using the atomization device of the present invention, the pressure metered dose inhaler 1 is combined with the micro-channel chip 4. During the process of aerosol particles ejected from the pressure metered dose inhaler 1 being ejected through the first ejection channel 43 and the second ejection channel 44 on the micro-channel chip 4, the two jets collide at a certain angle to generate atomized aerosol particles with a smaller particle size, thereby extending the spray time, improving the lung deposition rate, enhancing the hand-mouth coordination during use, and achieving a better drug delivery effect.

In this embodiment, as shown in Fig. 1 to Fig. 3, the pressure metered dose inhaler 1 adopts the prior art, the clamping sleeve 3 is arranged parallel to the housing 11 at the nozzle 111, the left end of the connecting pipe 2 is tightly sleeved at the outlet of the expansion chamber 16, the right end of the connecting pipe 2 is tightly sleeved at the left end of the clamping sleeve 3, and the sleeve joint can be sealed with a sealing ring, etc. to ensure no leakage, and the right end of the clamping sleeve 3 is close to the nozzle 111. The microchannel chip 4 is fixed in the clamping sleeve 3 and is arranged close to the right end of the clamping sleeve 3, that is, close to the nozzle 111 side. As shown in Figures 2 and 3, the chip body 41 is a rectangular parallelepiped as a whole. After being fixed in the clamping sleeve 3, the chip body 41 is parallel to the extension direction of the clamping sleeve 3. The upper surface of the chip body 41 in Figure 2 is the first surface. The left side of the first surface faces the expansion chamber 16, and the right side faces the nozzle 111. A plurality of guide channels 42 are opened, which are arranged at equal intervals along the left end of the first surface and extend to the left end of the chip body 41. When the aerosol particles ejected from the expansion chamber 16 pass through the guide channel 42, the guide channel 42 not only guides the aerosol particles so that they can smoothly enter the chip body 41, but also filters them. Aerosol particles with a particle size larger than the width of the guide channel 42 are intercepted, and aerosol particles with smaller particles pass smoothly. The first jet channel 33 and the second jet channel 34 are opened in the middle of the right side of the first surface, and the guide channel 42 is connected with the first jet channel 33 and the second jet channel 34 through the groove of the first surface. The first jet channel 33 and the second jet channel 34 are arranged in opposite directions, so that the distance between them gradually decreases in the direction toward the nozzle 111. In this embodiment, the microchannel chip 4 is made of a silicon wafer with a length×width×height of 2×2.5×0.665mm, etched, bonded with a glass sheet, and cut. The cross-sectional dimensions of the first jet channel 33 and the second jet channel 34 on the right end face of the chip body 41 in FIG. 2 are 50×100μm. The sealing ring is arranged between the micro-channel chip 4 and the inner wall of the clamping sleeve 3, which blocks the cross section of the clamping sleeve 3 except the micro-channel chip 4 at the location of the micro-channel chip 4. Therefore, when the aerosol particles sprayed by the expansion chamber 16 enter the clamping sleeve 3 to the micro-channel chip 4, they can only continue to spray along the guide channel 42, and further spray to the first spray channel 33 and the second spray channel 34, forming two jets with a certain angle, and when the right end of the chip body 41 in FIG. 2 is sprayed, the two jets with a certain angle collide with each other to form aerosol particles with a smaller particle size, and finally sprayed through the right end port of the clamping sleeve 3 and the nozzle 111 for human inhalation. In this embodiment, the sealing ring is fixed by a metal perforated nut to clamp the micro-channel chip 4. In the present embodiment, a structural unit composed of two identical micro-channel chips 4 is placed in the clamping sleeve 3 for operation, and the two micro-channel chips 4 are fitted so that the two first surfaces are arranged away from each other, so that the aerosol particles sprayed by the expansion chamber 16 can be processed by the two micro-channel chips 4, and more aerosol particles can be shunted to the first injection channel 33 and the second injection channel 34 on the two micro-channel chips 4 at the same time, and collide to form aerosol particles with smaller particle size after ejection. According to actual application, only one micro-channel chip 4 can be set in the clamping sleeve 3, and the size of the chip body 41, the number of the diversion channel 42, the size of the first injection channel 33 and the second injection channel 34 and the spacing between the two, and the angle between the extension lines can all be adjusted. The pressure metered dose inhaler 1 is a mature prior art, and the specific working principle of its spraying medicine is not repeated here.

Optionally, the micro-channel chip 4 further includes a filter assembly 45, which is disposed between the diversion channel 42 and the first injection channel 43 and the second injection channel 44. This arrangement intercepts the larger aerosol particles ejected from the expansion chamber 16, preventing them from remaining larger particles after being ejected from the micro-channel chip 4 and settling in the oropharynx.

In this embodiment, as shown in FIG. 2 and FIG. 3 , the filter assembly 45 is disposed between the guide channel 42 and the first injection channel 43 and the second injection channel 44, and is in an “M” shape as a whole, completely covering each of the guide channels 42, so that the liquid medicine aerosol particles ejected through each of the guide channels 42 need to be filtered by the filter assembly 45 before entering the first injection channel 43 and the second injection channel 44, ensuring that all large-particle aerosols are intercepted. According to actual application conditions, the filter assembly 45 can adopt any filtering structure, as long as it ensures that large-particle aerosols cannot pass through and small-particle aerosols pass smoothly.

Optionally, the filter assembly 45 includes a plurality of filter sheets 451, and the plurality of filter sheets 451 are arranged at intervals in a direction toward the first injection channel 43 and the second injection channel 44. This arrangement simplifies the structure of the filter assembly 45 and facilitates processing.

In this embodiment, as shown in FIG. 2 and FIG. 3 , a plurality of filter sheets 451 are arranged at equal intervals, each filter sheet 451 is parallel to the left end face of the chip body 41, and the projections of each two adjacent filter sheets 451 on the left end face of the chip body 41 have overlapping parts, and the overall arrangement is "M"-shaped, and the gap between the two adjacent filter sheets 451 is smaller than the width of the guide channel 42. After the jet of aerosol particles is initially filtered through the guide channel 42 and sprayed toward the filter assembly 45, the aerosol particles of small particles are sprayed out through the gaps between the adjacent filter sheets 451 and finally enter the first spray channel 43 and the second spray channel 44, and the aerosol particles of larger particles are intercepted and cannot pass through. According to the actual application, the number of filter sheets 451 and the specific arrangement method on the chip body 41 can be adjusted, as long as the aerosol of large particles can be intercepted. Preferably, the angle between the guide channel 42 and the extension line of each filter sheet 451 is set to 90°-135°.

Optionally, the atomization device further includes a stopper 5, which is connected to the second end of the clamping sleeve 3, and a spray hole is formed through the stopper 5. This arrangement enables the stopper 5 to constrain and limit the microchannel chip 4 in the clamping sleeve 3, thereby preventing the microchannel chip 4 from moving and then sliding out of the clamping sleeve 3, and preventing the drug solution from leaking.

In this embodiment, as shown in FIG1 , the stopper 5 is a metal nut, which is inserted from the right end of the clamping sleeve 3 and can be abutted against or spaced from the microchannel chip 4. The injection holes through which the stopper 5 is opened are arranged corresponding to the first injection channel 43 and the second injection channel 44, so that the aerosol particles ejected from the first injection channel 43 and the second injection channel 44 can be smoothly ejected to the nozzle 111 through the injection holes for human inhalation. According to actual application conditions, the stopper 5 can adopt any stopper structure.

Optionally, the inner wall of the second end of the clamping sleeve 3 is provided with an internal thread, and the stopper 5 is threadedly connected to the clamping sleeve 3. This arrangement simplifies the connection relationship between the stopper 5 and the clamping sleeve 3, which is conducive to improving assembly efficiency.

In this embodiment, as shown in FIG. 2 , an internal thread is provided on the inner wall of a certain distance from the right end of the clamping sleeve 3 , and the limiter 5 is a metal nut which is inserted into the right end port of the clamping sleeve 3 to achieve a threaded connection.

Optionally, the angle between the extension lines of the first injection channel 43 and the second injection channel 44 in the direction of the nozzle 111 is 60°-90°. In this arrangement, the two aerosol jets ejected from the first injection channel 43 and the second injection channel 44 can collide to a greater extent and more fully, so that aerosol particles with smaller particle size are obtained after the collision, so as to further improve the lung deposition rate of the drug.

In this embodiment, the angle between the extension lines of the first injection channel 43 and the second injection channel 44 in the direction of the nozzle 111 is set to 60°. According to actual application conditions, the angle between the extension lines of the first injection channel 43 and the second injection channel 44 in the direction of the nozzle 111 can be set to any angle between 60° and 90°.

Optionally, the first jet channel 43 and the second jet channel 44 are spaced 160 μm to 320 μm apart at the end of the chip body 41. With this arrangement, the two aerosol jets ejected from the first jet channel 43 and the second jet channel 44 can collide more fully to a greater extent, so that aerosol particles with a smaller particle size are obtained after the collision, thereby further improving the lung deposition rate of the drug.

In this embodiment, as shown in Figures 2 and 3, the distance between the first jet channel 43 and the second jet channel 44 at the right end of the chip body 41 is 160μm, and the angle between the extension lines of the two is 60°. Under this setting, the particle size of the aerosol particles after the collision of the two jets ejected from the first jet channel 43 and the second jet channel 44 is mainly distributed in the range of 5-20μm.

Optionally, the first injection channel 43 has a depth of 50 μm-75 μm and a width of 100 μm-150 μm at the end of the chip body 41; and/or the second injection channel 44 has a depth of 50 μm-75 μm and a width of 100 μm-150 μm at the end of the chip body 41. This arrangement is conducive to smooth injection of aerosol particles through the first injection channel 43 and the second injection channel 44, and sufficient collision between them.

In this embodiment, the depth×width of the first injection channel 43 at the end of the chip body 41 is 50μm×100μm, and similarly, the depth×width of the second injection channel 44 at the end of the chip body 41 is also 50μm×100μm. According to actual application conditions, the depth and width of the first injection channel 43 and the second injection channel 44 at the end of the chip body 41 can be the same or different.

Optionally, the microchannel chip 4 is made by etching, bonding, and cutting processes. The above process is flexible to operate and highly efficient.

In this embodiment, the silicon wafer is etched by using photolithography technology, and the guide channel 42, the filter 451, the first injection channel 43 and the second injection channel 44 are etched on a 2×2.5 mm silicon wafer.

Optionally, the clamping sleeve 3 is made of a high-pressure resistant material to support the high-pressure drug jet injected into the clamping sleeve 3 .

According to the actual application, any commercially available high-pressure resistant material that meets the pressure conditions can be selected.

The following further describes the use process of the atomization device:

When in use, the storage tank 12 is manually pressed. Then, under the thrust of the propellant gas in the storage tank 12, after the liquid medicine passes through the metering chamber 13, the liquid medicine that meets the one-time injection dose is ejected from the metering valve 14, and enters the expansion chamber 16 through the output pipe 15 connected to the metering valve 14. After being atomized into aerosol particles in the expansion chamber 16, the liquid medicine is ejected from the outlet of the expansion chamber 16 into the connecting pipe 2, and then enters the clamping sleeve 3 connected thereto through the connecting pipe 2. The micro-channel chip 4 is arranged in the clamping sleeve 3, and the space between the inner wall of the clamping sleeve 3 and the micro-channel chip 4 is filled with the sealing ring. Therefore, the liquid medicine jet entering the clamping sleeve 3 can only continue to be ejected along the first surface through the multiple guide channels 42 opened on the first surface of the chip body 41. When the liquid medicine jet guided and preliminarily filtered by the guide channel 42 passes through the filter assembly 45, The larger aerosol particles are filtered and intercepted for the second time by the filter assembly 45, and the smaller aerosol particles pass smoothly and enter the first injection channel 43 and the second injection channel 44 respectively to form two jet streams, which are respectively ejected along the first injection channel 43 and the second injection channel 44. Since the first injection channel 43 and the second injection channel 44 both extend to the end of the chip body 41 and the extension lines toward the nozzle 111 intersect, the two jet streams are ejected from the two injection channels at a certain angle and collide with each other, generating atomized aerosol particles with smaller particle size after the collision, and ejected through the port of the clamping sleeve 3 and the nozzle 111 for inhalation by the user. Since the particle size of the aerosol particles is further reduced, it is more difficult to settle and remains suspended for a longer time, the aerosol particles settled in the oropharynx are reduced, and the aerosol particles settled in the lungs are increased.

By using the atomization device of the present invention, the pressure metered dose inhaler 1 is combined with the micro-channel chip 4. During the process of aerosol particles ejected from the pressure metered dose inhaler 1 being ejected through the first ejection channel 43 and the second ejection channel 44 on the micro-channel chip 4, the two jets collide at a certain angle to generate atomized aerosol particles with a smaller particle size, thereby extending the spray time, improving the lung deposition rate, enhancing the hand-mouth coordination during use, and achieving a better drug delivery effect.

Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some of the technical features therein. However, these modifications or replacements do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present invention.

Claims (10)

1. The utility model provides an atomizing device, includes the quantitative inhaler of pressure, the quantitative inhaler of pressure is including seting up the shell of spout, install in storage tank in the shell, set up in the measurement room in the storage tank, with the measurement valve that the measurement room is connected and through the output tube with the expansion chamber of measurement valve intercommunication, its characterized in that still includes:

A connecting tube, a first end of which communicates with an outlet of the expansion chamber;

A clamping sleeve, a first end of which is communicated with a second end of the connecting pipe, and a second end of which faces the nozzle;

The micropore way chip, micropore way chip is fixed in inside the centre gripping sleeve pipe includes:

The chip body comprises a first surface, and the first surface is parallel to the extending direction of the clamping sleeve;

The plurality of diversion channels are arranged at one end of the first surface facing the expansion chamber;

the first injection channel and the second injection channel are arranged on the first surface, are arranged on one side of the diversion channel facing the nozzle, are respectively communicated with the diversion channel, extend to the end part of the chip main body, and are intersected with each other along the extension line of the direction of the nozzle;

And a sealing ring is arranged between the micro-channel chip and the inner wall of the clamping sleeve.

2. The atomizing device of claim 1, wherein the micro-channel chip further comprises:

The filter assembly is arranged between the diversion channel and the first injection channel and between the first injection channel and the second injection channel.

3. The atomizing device of claim 2, wherein the filter assembly comprises:

The filter sheets are arranged at intervals in the direction towards the first injection channel and the second injection channel.

4. A device according to any one of claims 1-3, further comprising:

The limiting piece is connected with the second end of the clamping sleeve, and the limiting piece is provided with an injection hole in a penetrating mode.

5. An atomizing device according to claim 4, wherein:

The inner wall of the second end of the clamping sleeve is provided with an internal thread, and the limiting piece is in threaded connection with the clamping sleeve.

6. A device according to any one of claims 1-3, wherein:

the included angle between the extension lines of the first injection channel and the second injection channel towards the direction of the nozzle is 60-90 degrees.

7. A device according to any one of claims 1-3, wherein:

the distance between the first injection channel and the second injection channel at the end part of the chip main body is 160-320 mu m.

8. A device according to any one of claims 1-3, wherein:

The depth of the first jet channel at the end part of the chip main body is 50-75 mu m, and the width of the first jet channel is 100-150 mu m; and/or the number of the groups of groups,

The second ejection channel has a depth of 50 μm to 75 μm and a width of 100 μm to 150 μm at an end of the chip body.

9. A device according to any one of claims 1-3, wherein:

the micro-channel chip is manufactured by etching, bonding and cutting processes.

10. A device according to any one of claims 1-3, wherein:

The clamping sleeve is made of high-pressure resistant materials.