JP6653000B1 - Applied pressure vibration device - Google Patents

Abstract

Provided is a pressurized vibration applying apparatus capable of improving a drug delivery rate by applying pressurized vibration to a medicine airflow in consideration of a patient's respiratory state. The apparatus includes a main body for generating a gas flow, a gas supply hose for supplying a gas flow from the main body into the nasal cavity, and a nosepiece attached to a distal end of the gas supply hose. An opening 6 that opens at a boundary with the proximal end 4a of the nebulizer nosepiece 4, a pressure line 7 having the opening 6 as a downstream end, and an upstream end of the pressure line 7 connected to the upstream of the pressure line 7 to apply a pressure , A valve device 9 provided in the middle of the pressure line 7 and between the pressure pump 8 and the opening 6, and controlling the opening and closing of the valve device 9, 8 is provided with a control unit 10 for converting the pressure into a desired pressurized vibration waveform and a temperature sensor 11 for measuring parameters reflecting the expiration and inspiration of the patient. [Selection diagram] Fig. 1

Description

The present invention relates to a pressurized vibration applying device that applies pressurized vibration to a drug airflow generated by a nebulizer device, and in particular, synchronizes the timing of pressurized vibration with respiration to reduce the drug delivery rate into the paranasal sinuses. The present invention relates to a pressurized vibration applying device which can be improved and can be easily attached to an existing nebulizer device.

Conventionally, for diseases such as sinusitis that cause bacterial inflammation or pus in the sinuses, one of the treatment means is to atomize the drug and generate a drug airflow, and this drug airflow is sent to the paranasal sinuses. Nebulizer devices for delivery have been used. According to this nebulizer device, it is possible to administer the drug airflow at a constant pressure and flow rate into the left and right nasal cavities at a time. However, since the paranasal sinuses were closed cavities, the drug airflow administered intranasally was hardly delivered into the paranasal sinuses, and the particles of the drug airflow did not adhere to the nasal mucosa because they were not enough to adhere to the mucous membrane. There is a problem that the drug is excreted out of the body with respiration. As a result, there have been cases where the symptoms become chronic or become severe and require surgical treatment.
In order to solve such a problem, a pressure difference of gas is generated between the nasal cavity and the paranasal sinuses by applying a pressurized vibration to the pharmaceutical airflow at a constant cycle, thereby improving the delivery rate of the pharmaceutical airflow into the paranasal sinuses. A pressurized vibration type nebulizer device (manufactured by Paris, Germany) has been commercialized. However, this pressurized vibration type nebulizer device has to be operated for each side of the nostril, the rotation rate of the patient is reduced by half compared to the conventional one, and the noise of the pressurized vibration actuator is large, so the narrow consultation room of the otolaryngology It is not widely used because it causes problems when used in treatment rooms. In addition, since the application method of the pressurized vibration is a sinusoidal wave with a constant period, the drug airflow cannot be pressurized in a good bolus shape, and the drug delivery rate into the paranasal sinuses cannot be sufficiently improved. could not.
Therefore, in recent years, a technique has been developed in which the method of applying the pressurized vibration is improved in order to improve the drug delivery rate, and the invention has already been disclosed with respect thereto.

Patent Literature 1 discloses an invention under the name of “operation method of aerosol delivery device and aerosol delivery device”, which relates to an operation method of an aerosol delivery device that efficiently delivers an aerosol to a paranasal sinus.
Hereinafter, the invention disclosed in Patent Document 1 will be described. The invention disclosed in Patent Document 1 discloses an aerosol generator for generating an aerosol, and an aerosol generator for inducing a transport flow in an aerosol delivery device for transporting at least a portion of the generated aerosol out of the aerosol delivery device. The gas transport element is characterized in that the transport flow is triggered and stopped intermittently by repeatedly activating and deactivating the gas transport element during the aerosol generation step.
According to the invention having such features, the transport flow induced by repeatedly activating and stopping the gas transport element has a rectangular wave shape as shown in FIGS. By such a transport flow, the aerosol can be transported to the paranasal sinuses in a well-rised bolus shape. In addition, by repeatedly inducing and stopping the conveyance flow, the aerosol is intermittently delivered to the paranasal sinuses, thereby making it possible to improve the rate of drug delivery into the paranasal sinuses as compared with the related art.

JP-T-2013-524960

However, in the aerosol delivery device disclosed in Patent Literature 1, although the transport flow is formed in a rectangular wave shape and the aerosol can be intermittently delivered to the paranasal sinuses, this delivery takes into account the respiratory condition of the patient. is not. Therefore, when the aerosol is delivered at the timing of inhalation, the drug airflow quickly flows into the nasal cavity. However, at the timing of expiration, there is a possibility that the inflow of the drug airflow may be obstructed due to the resistance caused by this. Actually, depending on the patient, the breathing is unstable, and the ratio between the period of expiration and the period of inspiration is not constant, or the breathing state differs for each patient. Therefore, even if the aerosol is delivered uniformly without taking such circumstances into account, the deposition rate varies, and the reproducibility of the drug delivery rate for each treatment or for each patient may not be good.
The aerosol delivery device disclosed in Patent Document 1 will be described with reference to FIGS. 1 to 4 and reference numerals shown in these drawings. In FIG. 1, a compressor 1 and a pulsator 2 are a main body. It is connected to the aerosol generator 3 via a connector 12 built in the device 10. In FIG. 2, the compressor 1 is connected to a nebulizer chamber 32 via a connector 12 built in the main body 10, and the pulsator 2 is directly connected to the nebulizer chamber 32. In FIG. 3, the compressor 1 and the pulsator 2 are connected to the adaptive element 14 built in the main body 10 via the connector 12 built in the main body 10 and the nebulizer chamber 32. Subsequently, in FIG. 4, the compressor 1 and the pulsator 2 are connected to the housing of the main body 10 via the connector 12.
That is, in FIGS. 1 to 4, the compressor 1 and the pulsator 2 are both connected to the main body 10 and various components housed therein. From such a structure, it is understood that when the compressor 1 and the pulsator 2 are added to, for example, an existing nebulizer device, it is necessary to modify the main body. Therefore, when purchasing the aerosol delivery device disclosed in Patent Literature 1, the cost for new installation or the cost for remodeling the existing device is required, and it may not be possible to easily introduce the device.

  The present invention has been made in view of such a conventional situation, and improves the drug delivery rate by applying a pressurized vibration to a drug airflow in consideration of a patient's respiratory condition, and improves the reproducibility thereof. It is an object of the present invention to provide a pressurized vibration applying apparatus which is favorable and can be easily mounted on an existing nebulizer apparatus, so that the introduction cost can be suppressed.

In order to achieve the above object, a first aspect of the present invention provides a main body for generating a drug airflow, an air supply hose for supplying a drug airflow from the main body into the nasal cavity, and a distal end of the air supply hose. Of a nebulizer device provided with a nosepiece to be opened, an opening opening at a boundary between a distal end of an air supply hose and a proximal end of the nosepiece, a pressurizing line having the opening as a downstream end, and a pressurizing line. A pressure pump connected to the upstream end of the pressure line for applying pressure to the medicine airflow, a valve device provided in the middle of the pressure line between the pressure pump and the opening, and opening and closing of the valve device And a controller for converting the pressure of the pressure pump into a desired pressure vibration waveform.
In the invention having such a configuration, as the boundary between the distal end of the air supply hose and the proximal end of the nosepiece, for example, in addition to an attachment for connecting them, the distal end of the air supply hose and the nosepiece May be directly connected to each other. The opening may be provided in the above-mentioned attachment, or may be a hole penetrating the distal end of the air supply hose. In any case, no modification is made to the body of the nebulizer device.
Further, as the pressurizing pump and the valve device, for example, a pneumatic pump and an electromagnetic valve are used. Further, the pressurizing line is, specifically, a pipe having a hollow structure.

In the invention having the above configuration, the pressure of the pressurized pump converted into the pressurized vibration waveform from the opening that opens to the boundary portion with respect to the drug airflow that has been continuously supplied with a constant amount by the air supply hose. As a result, the waveform of the drug airflow is also converted to a waveform similar to this pressure waveform. For example, when the pressurized vibration waveform is a waveform in which a pulse-like signal is continuously generated at fixed intervals, a pressure change with respect to a time change (hereinafter, referred to as a pressure gradient) at each pulse generation. appear. This creates a pressure difference between the nasal cavity and the paranasal sinuses, i.e., the drug airflow is delivered into the paranasal sinuses by the drug airflow pressure in the nasal cavity being stronger than the gas pressure in the paranasal sinuses. .
In addition, since the pressure oscillation waveform can adjust factors such as frequency, amplitude, and pulse width to desired values by the control unit, by appropriately setting the values of these factors, the delivery rate of the drug airflow can be improved. Can be expected to improve.

Next, a second invention according to the first invention, further comprises a respiration sensor for measuring a parameter reflecting the expiration and inspiration of the patient, and the respiration sensor transmits a signal reflecting the measured parameter to the control unit. The control unit generates time series data of expiration and inspiration from the received signal, and outputs the pressure of the pressurizing pump as a rectangular wave pulse at a desired timing based on the time series data.
In the invention having such a configuration, as the respiration sensor, for example, a temperature sensor that measures the temperature of expiration, a flow sensor that measures the flow rate of expiration, or the like can be considered.
Therefore, in the invention having the above configuration, in addition to the operation of the first invention, at least information relating to the start and end of the exhalation can be obtained from the signal reflecting the measured parameter. Time series data showing the status can be created.
Next, the control unit performs an appropriate process on the time-series data to determine a point in time at which exhalation and inspiration are switched, and further controls the opening and closing of the valve device based on the determined result to change the pressure of the pressurizing pump into a rectangular waveform. Can be output as a pulse.

Next, according to a third aspect of the present invention, in the second aspect, the square-wave pulse is generated by: (1) during the stop of breathing from the end of inspiration to the start of expiration, or (2) the start of expiration from the start of inspiration. Until the data is output.
In the invention having such a configuration, in addition to the operation of the first or second invention, a rectangular wave pulse is output during a short period of time (1) while breathing is stopped or during a few seconds in (2). Is done. Of these, at least in (2), a plurality of rectangular wave pulses are output at regular intervals. Therefore, the inflow of the drug airflow into the nasal cavity is not inhibited.

Further, according to a fourth aspect, in any one of the first to third aspects, an attachment having a hollow structure is interposed between a distal end of the air supply hose and a proximal end of the nosepiece, and the opening is And an opening inside the attachment.
In the invention having such a configuration, in addition to the operation of the invention described in any of the first to third aspects, since the opening is opened inside the attachment, for example, the opening is pierced through the distal end of the air supply hose. The pressurizing line, the pressurizing pump, and the like are easily connected to the attachment as compared with the case where the hole is an opening.

  In a fifth aspect based on the fourth aspect, the attachment includes a cylindrical cover having a front end connected to the proximal end of the nosepiece, one end fitted into the internal space of the cover, and the other end fed to the other end. The cover has a cylindrical adapter to which the distal end of the air hose is connected.The cover has a tapered through-hole whose internal space tapers toward the front end, and the opening opens in the side wall near the rear end of the cover. The adapter is provided with a protrusion having a tapered outer shape tapering toward one end, and the protrusion has a predetermined gap between the adapter and the inner circumferential surface of the cover when inserted into the internal space. The output of the pressurizing pump applied through the opening is a swirling flow traveling toward the front end of the cover while swirling inside the gap.

In the invention having such a configuration, the inner space of the cover and the outer peripheral shape of the protruding portion are all formed in a tapered shape, but the outer peripheral shape of the cover and the inner space of the protruding portion are not necessarily tapered. Is also good.
In the invention having the above configuration, in addition to the operation of the invention described in the fourth aspect, the output of the pressurizing pump rotates inside the gap between the through hole of the cover and the protrusion of the adapter toward the front end of the cover. As it progresses, a negative pressure region is generated at the center at the front end of the cover. Therefore, the drug airflow is sucked at the timing when the negative pressure region is formed, and becomes a bolus shape. Therefore, a larger amount of the bolus-shaped drug airflow is delivered to the inside of the paranasal sinuses when it rises.

According to a sixth aspect of the present invention, in any one of the second to fifth aspects, the respiration sensor is a temperature sensor installed at a mouth of a patient.
In the invention having such a configuration, the respiratory sensor may be installed so as to be able to perform wired communication or wireless communication with the control unit. In addition to the independent installation of the respiratory sensor alone at the mouth, and the installation supported by the attachment, It is considered that the attachment is performed or the attachment is supported by a holding device that holds the attachment. As the temperature sensor, for example, a thermocouple or a thermistor is used, and it is desirable that the temperature sensor has a high-speed thermal response.
In the invention having the above configuration, since the temperature of the exhaled air is measured in real time from the temperature sensor installed at the mouth, the pressure of the pressurizing pump with good temporal accuracy is generated according to the measurement result.

  According to the first aspect, a pressure difference is generated between the nasal cavity and the paranasal sinuses, and the drug airflow is delivered into the paranasal sinuses, so that the delivery rate of the drug airflow can be improved. Further, the pressurizing vibration applying device can be easily mounted without modifying the main body of the nebulizer device, and the introduction cost can be suppressed. Furthermore, since the control unit can adjust factors such as the frequency of the pressurized vibration waveform to desired values, by appropriately setting the values of these factors, it is possible to further improve the delivery rate of the drug airflow. Can be expected.

  According to the second invention, in addition to the effect of the first invention, by providing a respiration sensor and a control unit, the opening and closing of the valve device is controlled to output the pressure of the pressurizing pump as a rectangular wave pulse. Therefore, it is possible to apply rectangular wave-shaped pressurized vibration to the medicine airflow at a desired timing.

  According to the third invention, in addition to the effect of the second invention, it is possible to generate a rectangular wave pulse at a timing other than the exhalation. Therefore, the reproducibility of the drug delivery rate for each single treatment or for each patient is improved as compared with the case where the rectangular wave pulse is generated without considering inspiration and expiration. In addition, if the patient is pressurized and vibrated during expiration, the patient may feel uncomfortable. According to the third aspect, this discomfort can be prevented.

  According to the fourth aspect, in addition to the effects of any of the first to third aspects, by providing the attachment, the pressurizing line, the pressurizing pump, and the like can be easily attached.

  According to the fifth aspect, in addition to the effect of the fourth aspect, since a larger amount is delivered to the inside of the paranasal sinuses at the time of the rise of the pharmaceutical stream, the delivery rate of the pharmaceutical stream to the paranasal sinuses is improved. I do.

  According to the sixth aspect, in addition to the effects of any of the second to fifth aspects, the respiratory condition of the patient can be known by a simple measuring means such as a temperature sensor. Further, by selecting a temperature sensor having a high-speed thermal response, the pressure of the pressurizing pump can be generated by accurately following the waveform of the actual breathing.

FIG. 4 is a block diagram illustrating a configuration of a pressure vibration applying device according to an example. (A) is time-series data of expiration and inspiration created by a control unit constituting the pressurized vibration applying apparatus according to the embodiment, and (b) is a waveform of a rectangular pulse output based on (a). is there. (A) is a graph showing a pressure change in the paranasal sinus when the pressurized vibration is applied, and (b) is a graph showing the drug flow when the rectangular wave pulse-shaped pressurized vibration is applied. 6 is a graph showing a reaching rate of reaching. (A) is a perspective view of an attachment which constitutes a pressurized vibration applying device according to an example, and (b) is an external view of the device. It is an external appearance perspective view of the attachment which comprises the pressurization vibration addition apparatus which concerns on the modification of an Example. (A) and (b) are each a sectional view of an attachment constituting a pressurized vibration applying device according to a modified example of the embodiment, and (c) is a sectional view for explaining the operation thereof.

A pressure vibration applying apparatus according to a first embodiment of the present invention will be described in detail with reference to FIGS. FIG. 1 is a block diagram illustrating a configuration of a pressure vibration applying device according to an embodiment.
As shown in FIG. 1, the pressurized vibration applying apparatus 1 according to the embodiment is configured to atomize a medicine to generate a medicine airflow, and attach the nebulizer apparatus 5 to deliver the medicine airflow to the paranasal sinuses. This is a device for applying pressure vibration to the pressure.
First, the nebulizer device 5 is attached to a main body 2 for generating a medicine airflow, an air supply hose 3 for supplying the medicine airflow from the main body 2 into the nasal cavity, and a distal end of the air supply hose 3. The nosepiece 4 is provided.

Next, the pressurizing vibration applying apparatus 1 opens the opening 6 at the boundary between the distal end of the air supply hose 3 and the proximal end of the nosepiece 4, and pressurizes the opening 6 at the downstream end. A pressurizing pump 8 connected to the upstream end of the pressurizing line 7 for applying air pressure to the medicine airflow, and a pressurizing pump 8 and an opening 6 The apparatus includes a valve device 9 provided therebetween and a control unit 10 for controlling the opening and closing of the valve device 9 to convert the pressure of the pressurizing pump 8 into a desired pressurizing vibration waveform.
Specifically, the pressure line 7 is a pipe having airtightness. The pressurizing pump 8 is preferably a pneumatic pump having a silent design. Further, the valve device 9 is an electromagnetic valve capable of high-speed response, and changes the attitude of the valve element under the control of the control unit 10 so that the compressed air output from the pressurizing pump 8 is compressed. Can pass or cannot pass through.

Further, the pressurized vibration applying apparatus 1 includes a respiration sensor that measures a parameter that reflects a patient's expiration and inspiration. In the present embodiment, the respiration sensor is a temperature sensor 11 that is installed at the mouth of the patient and that is connected to the control unit 10 in a wired communication manner. Therefore, the temperature sensor 11 automatically transmits the measured parameter, that is, a signal of the strength reflecting the temperature of the patient's expiration and inspiration to the control unit 10. Of course, the measurement interval of the temperature sensor 11 and the transmission interval to the control unit 10 are freely set by the control unit 10.
Further, the pressurized vibration applying apparatus 1 includes an attachment 12 having a hollow structure interposed between the distal end of the air supply hose 3 and the proximal end of the nosepiece 4. The part 6 opens inside the attachment 12. The detailed configuration of the pressure vibration applying device 1 will be described later with reference to FIG.

Subsequently, the operation of the control unit configuring the pressure vibration applying device will be described with reference to FIG. FIG. 2A is time-series data of expiration and inspiration created by a control unit included in the pressurized vibration applying apparatus according to the embodiment, and FIG. 2B is output based on FIG. 2A. It is a waveform of a square wave pulse.
The control unit 10 creates expiration and inspiration time-series data from the received signal of the temperature sensor 11. As shown in FIG. 2A, the created time-series data is roughly expressed by plotting the time t on the horizontal axis and the intensity of the signal S of the temperature sensor 11 (normalized at room temperature) on the vertical axis. Is considered to have a waveform in which an upwardly convex quadratic curve is repeated at regular intervals. Among them, the quadratic curve is the measurement result of the temperature of the expiration, and the substantially flat portion between the quadratic curves is the measurement result of the temperature of the inspiration.

  Therefore, the control unit 10 performs, for example, a differentiation process on the time-series data illustrated in FIG. 2A, and determines that a time point at which the differential value changes from zero to a positive value is a time point at which switching from inspiration to expiration occurs. It can be determined that the point in time when the differential value changes from a negative value to zero is the point in time when switching from exhalation to inspiration. Therefore, it is possible to output the pressure of the pressurizing pump 8 as a rectangular wave pulse P at a desired timing based on the time-series data, for example, during intake.

As a specific example, in the present embodiment, as shown in FIG. 2B, the rectangular wave pulse P is (1) during the end of respiration from the end of inspiration to the start of expiration, or (2) during inspiration. Is output from the start to the start of exhalation. That is, in any case, the rectangular pulse P is not output during expiration. Note that the maximum amplitude A _max and the frequency of the rectangular wave pulse P can be arbitrarily set.

Further, the effect of pressure application to the paranasal sinus by the pressure pump will be described with reference to FIG. FIG. 3A is a result of a preliminary experiment showing a change in pressure in the paranasal sinuses when pressure is applied by a pressurizing pump, and FIG. 3B is a diagram in which rectangular wave pulse-like pressurizing vibration is applied. 9 is an experimental result showing the rate of arrival of a drug airflow into a paranasal sinus in each case.
First, an experimental method will be described. In FIG. 3A, a simple human nasal paranasal sinus model (not shown), and a flow meter and a pressure gauge for measuring a flow rate and a pressure of a gas, respectively, are used. The human nasal paranasal sinus model is provided with a substantially spherical hollow portion made of glass, an air supply pipe diametrically penetrating the hollow portion, and a communication port communicating with the upstream side of the air supply pipe in the middle thereof. It consists of a tube that is placed orthogonal to the trachea. As a method of measuring the flow rate, pressurized air was sent in a bolus form from one open end of the tube, and the flow rate was measured with a flow meter over time. Then, because the part of the air sent to the pipe flowing from the communicating port to the hollow portion, and the pressure p ₁ of the air flowing into the hollow portion, the pressure p ₂ of the air flowing out of the hollow portion, flues The time was measured with a pressure gauge installed at each end of the sample. Then, to determine the pressure p in the sinuses ₍₌ p 1 -p _2).
FIG. 3A plots the waveform (broken line) of the air flow rate Q at one open end of the tubular body and the pressure p (solid line) in the paranasal sinuses on the vertical axis, with time t on the horizontal axis. . According to this result, the air flows into the paranasal sinuses only at the initial stage when the pressure gradient in the paranasal sinuses is large, and the state in which the pressure p in the paranasal sinuses is maximum even when the flow rate Q becomes zero. You can see that it is continuing.

In FIG. 3 (b), using a model similar to that of FIG. 3 (a), an atomized gas stream colored at a certain concentration is sent as a rectangular wave pulse from one open end of the pipe body, and The concentration of the dye deposited on the sample was measured by colorimetry, and the degree of drug delivery (%) was calculated. At this time, the number of times of applying the rectangular wave pulse per minute (frequency of applying pressure vibration) was changed from 1 to 10 times. In addition, the pigment particle diameter of the atomization airflow was 5.9 (μm), the communication aperture was 5 (mm), and the pressure gradient was 78.2 (kPa / s).
In FIG. 3 (b), the horizontal axis represents the pressure application frequency (times / minute), and the vertical axis represents the drug delivery rate (maxillary sinus drug delivery rate:%). According to this result, when the frequency of pressurized vibration application was 10 (times / minute), the drug delivery degree was about 25 (%). On the other hand, when a conventional sinusoidal pressurized vibration was performed by the same method, the degree of drug delivery was about 2 to 3 (%). Therefore, it is understood that the degree of drug delivery can be drastically improved to about 10 times that of the related art by the pressurized vibration in the form of a rectangular wave pulse.

Next, a detailed configuration of the pressure vibration applying device 1 will be described with reference to FIG. FIG. 4A is a perspective view of an attachment constituting the pressure vibration applying device according to the embodiment, and FIG. 4B is an external view of the device. The same reference numerals are given to the components shown in FIGS. 1 and 2 in FIG. 4 and the description thereof is omitted.
As shown in FIGS. 4A and 4B, the pressurized vibration applying device 1 includes a distal end 3 a of an air supply hose 3 and a proximal end 4 a of a nosepiece 4, one end 12 a and the other end, respectively. Attachment 12 to which 12b is connected, holder 13 holding both side surfaces 12c, 12c and bottom 12d of attachment 12, flexible arm 14 composed of a hollow metal tube supporting holder 13 from the back thereof, It comprises a base 15 to which the lower end of the arm 14 is attached.

The attachment 12 is a hollow tube made of a transparent hard resin or glass, and is formed in a stepped shape having two bent portions 12e and 12f bent at substantially right angles as shown in FIG. An opening 6 having a tapered shape is opened at a bent portion 12f near one end 12a.
As shown in FIG. 4B, the holder 13 is made of a hard resin, and has an insertion hole 13b into the opening 6 immediately below the clip portion 13a that sandwiches both side surfaces 12c of the attachment 12. Further, a base 11a of the temperature sensor 11 is attached therebelow.
The base 15 is also made of a hard resin or metal, and houses a control unit 10 (see FIG. 1) including a pressurizing pump 8, a valve device 9, and a control board.
Although not shown, a pressure line 7 for sending the pressure of the pressure pump 8 to the opening 6 passes through the flexible arm 14, and the tip of the pressure line 7 is inserted into the insertion port 13 b of the holder 13. It is open to. Further, a wiring (not shown) for transmitting an output signal of the temperature sensor 11 to the control unit 10 also passes through the inside of the flexible arm 14.
The power supply to the pressurizing pump 8, the valve device 9, the control unit 10, and the temperature sensor 11 is performed by a built-in power supply or an AC adapter (not shown).

According to the pressurized vibration applying apparatus 1 having the above configuration, the control unit 10 controls the opening and closing of the valve device 9 based on the temperature of the exhaled air measured by the temperature sensor 11, and sets the pressure of the pressurizing pump 8 as the rectangular pulse P. Output. Since this rectangular wave pulse P shows the maximum pressure gradient at the start of the output, the drug airflow can flow into the paranasal sinuses as described with reference to FIG.
In addition, since the rectangular wave pulse P can be set to a desired maximum amplitude and the number of outputs by the control unit 10, the delivery rate of the drug airflow to the paranasal sinuses is larger than that of the related art as described with reference to FIG. It is possible to improve.
Furthermore, according to the pressurized vibration applying apparatus 1, the rectangular wave pulse P is generated during (1) the end of respiration from the end of inspiration to the start of exhalation, or (2) from the start of inspiration to the start of exhalation. While it is output. Therefore, it is possible to prevent the drug airflow from receiving resistance due to exhalation, thereby improving the drug delivery rate and reducing the ratio of drug particles that have not been deposited on the paranasal sinus mucosa.
Since the output of the rectangular wave pulse P can be adjusted for each patient, unlike the conventional case where the medicine is uniformly administered, the optimal medicine administration method for the patient's condition can be finely determined, so that the treatment results can be determined. Improvement can be expected.

  In addition, according to the pressurized vibration applying device 1, it can be easily attached to the existing nebulizer device via the attachment 12. Therefore, no remodeling cost is required, and the above-described excellent effects can be exhibited at a low cost with respect to the existing nebulizer device. Further, by selecting a pressurized pump 8 of the pressurized vibration applying apparatus 1 which is designed to be silent, noise can be reduced as compared with the conventional case when the pressurized pump 8 is installed in a narrow consultation room for otolaryngology.

Subsequently, an attachment constituting a pressurized vibration applying apparatus according to a modification of the present embodiment will be described with reference to FIGS. 5 and 6. FIG. 5 is an external perspective view of an attachment constituting a pressurized vibration applying apparatus according to a modification of the embodiment. The same reference numerals are given to the components shown in FIGS. 1 to 4 in FIG. 5 and the description thereof is omitted.
As shown in FIG. 5, the attachment 16 includes a cylindrical cover 17 having a front end 17a connected to the proximal end 4a of the nosepiece 4, and an end 18a (see FIG. 6) having an internal space S ₁₇ (see FIG. 6). 6) and a cylindrical adapter 18 to which the distal end 3a (see FIG. 6) of the air supply hose 3 is connected to the other end 18b.
Of these, an opening 20 to which the tip of the pressure line 7 is connected is opened at one location on the side wall of the cover 17. The configuration and operation of the opening 20 will be described with reference to FIG.

6 (a) and 6 (b) are cross-sectional views of an attachment constituting a pressurized vibration applying apparatus according to a modification of the embodiment, and FIG. 6 (c) is a cross-sectional view for explaining the operation thereof. It is. The same reference numerals are given to the components shown in FIGS. 1 to 5 in FIG. 6 and the description is omitted. 6 (a) to 6 (c) are longitudinal sectional views in which the attachment is equally divided along its long axis X (see FIG. 6 (c)).
As shown in FIG. 6 (a) and 6 (b), the cover 17 has an opening 20 of the internal space _{S 17} with forming a tapered through hole inner space _{S 17} is tapered toward the front end 17a Along the tangential direction, the cover 17 opens to the side wall 17c near the rear end 17b.
In addition, the adapter 18 includes a protrusion 19 having a tapered outer shape that tapers toward one end 18a. The protrusion 19, when inserted into the internal space S _17, the gap g (see FIG. 6 (c)) at regular intervals between the inner peripheral surface 17d of the cover 17 is formed. Other configurations of the attachment 16 are the same as those of the attachment 12 of the embodiment.

  As shown in FIG. 6C, in the attachment 16, the output of the pressurizing pump 8 applied through the opening 20 advances toward the front end 17 a of the cover 17 while turning inside the gap g. It is a swirling flow (spiral arrow in the figure). Therefore, a negative pressure region is generated at the center of the front end 17a of the cover 17. Therefore, at the timing when the negative pressure region is formed, the medicine airflow is sucked, formed into a bolus shape, and sent into the nosepiece 4 from one end 18a of the adapter 18. Therefore, a larger amount of the bolus-shaped drug airflow is delivered to the inside of the paranasal sinuses when it rises. Therefore, by providing the attachment 16, the delivery rate of the drug airflow is improved as compared with the case where the attachment 12 is provided. Other functions and effects of the attachment 16 are the same as the functions and effects of the pressurizing pump 8.

  Note that the pressure vibration applying device according to the present invention is not limited to the one shown in the embodiment. For example, a flow sensor or a pressure sensor may be used as the respiration sensor, and a measurement result may be transmitted to the control unit 10 via a wireless communication unit. Further, the attachments 12 and 16 may be omitted, and in this case, the openings 6 and 20 may be formed by penetrating the distal end 3a of the air supply hose 3.

  INDUSTRIAL APPLICABILITY The present invention can be used as a pressurized vibration applying device that applies pressurized vibration to a medicine airflow generated by a nebulizer device.

DESCRIPTION OF SYMBOLS 1 ... Applied vibration device 2 ... Main body 3 ... Air supply hose 3a ... Distal end 4 ... Nosepiece 4a ... Proximal end 5 ... Nebulizer device 6 ... Opening 7 ... Pressurizing line 8 ... Pressurizing pump 9 ... Valve Apparatus 10 ... Control unit 11 ... Temperature sensor 11a ... Base 12 ... Attachment 12a ... One end 12b ... Other end 12c ... Side 12d ... Bottom 12e, 12f ... Bending part 13 ... Holder 13a ... Clip part 13b ... Insertion port 14 ... Flexible arm 15 ... base portion 16 ... attachment 17 ... cover 17a ... front 17b ... rear end 17c ... side wall 17d ... inner circumferential surface S _{17 ...} internal space 18 ... adapter 18a ... one end 18b ... the other end 19 ... protruding portion 20 ... opening g ... gap

Claims (3)

A nebulizer device including a main body for generating a medicine airflow, an air supply hose for supplying the medicine airflow from the main body into the nasal cavity, and a nosepiece attached to a distal end of the air supply hose is closed. A pressurized vibration applying device attached to improve the drug delivery rate into the paranasal sinuses,
A pressure line having an opening opening at a boundary between the distal end of the air supply hose and the proximal end of the nosepiece as a downstream end,
A pressurizing pump connected to the upstream end of the pressurizing line and applying pressure to the drug airflow, which has been continuously supplied with a certain amount by the gas supply hose ;
In the middle of the pressurizing line, a valve device provided between the pressurizing pump and the opening,
A control unit that controls the opening and closing of the valve device and converts the pressure of the pressure pump into a desired pressure oscillation waveform ;
Equipped with a respiratory sensor that measures parameters that reflect the patient's expiration and inspiration,
This respiration sensor transmits a signal reflecting the measured parameter to the control unit,
The control unit creates time-series data of the expiration and the inspiration from the received signal, and outputs the pressure of the pressurizing pump as a rectangular wave pulse at a desired timing based on the time-series data. Characteristic pressurized vibration applying device. The square-wave pulse is output during (1) during the respiratory stop from the end of the inspiration to the start of the expiration, or (2) during the period from the start of the inspiration to the start of the expiration. The pressure vibration applying device according to claim 1 , wherein: The apparatus according to claim 1 , wherein the respiratory sensor is a temperature sensor installed at a mouth of the patient.

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