High-flow respiratory therapy device by respiratory synchronization and control method thereof

Abstract

The present invention relates to an apparatus capable of high flow respiratory treatment through respiratory synchronization, and a high flow respiratory treatment apparatus according to one embodiment of the present invention includes a respiratory pattern monitoring unit that monitors flow rate and pressure changes of a mixed gas supplied to a patient to collect information on the patient's breathing pattern, an inspiration effort point detection unit that detects an inspiration effort point at which the patient makes an effort to start inhaling from the patient's breathing pattern information, an exhaust effort point detection unit that detects an exhaust effort point at which the patient makes an effort to start exhaling from the patient's breathing pattern information, and a supply flow rate control unit that increases the flow rate of the mixed gas when the patient's breathing reaches the inspiration effort point and decreases the flow rate of the mixed gas when the patient's breathing reaches the exhaust effort point.

Description

Technical Field

[0001] The present invention relates to a high-flow respiratory therapy device, and in particular, to detecting the time when a patient starts to inhale and the time when the patient starts to exhale, supplying a high-flow mixed gas during inhalation to reduce dead space, and reducing the flow rate of the mixed gas during exhalation to reduce the patient's effort breathing. The present invention relates to a high-flow respiratory therapy device and method based on respiratory synchronization.

Background Art

[0002] High-flow respiratory therapy refers to a treatment that relatively reduces the dead space where gas exchange does not occur by administering high-concentration heated and humidified air higher than the oxygen concentration in the atmosphere at a rate more than 2 to 3 times higher than the patient's respiratory volume, thereby assisting the patient's breathing.

[0003] Generally, most of the air enters the alveoli for gas exchange, and a part remains in the respiratory tract. The volume of air remaining in the airway is called dead space. Dead space does not undergo gas exchange during actual breathing.

[0004] For example, when the tidal volume of a normal person is 500 ml and the volume of dead space is about 150 ml, the actual tidal volume is 350 ml. However, for a patient with poor respiratory ability whose tidal volume is only 300 ml, excluding the 150 ml of dead space, the actual tidal volume is 150 ml, so the tidal volume is less than half of the normal level. Thus, when the patient's tidal volume is not sufficiently larger than the dead space, respiratory failure (insufficient breathing phenomenon) occurs in the patient.

[0005] Therefore, the patient will breathe faster or consume a lot of energy to maintain a normal oxygen saturation, which is a factor that further deteriorates the patient's condition.

[0006] To solve this problem, a method of introducing a higher flow rate breathing therapy device than before and administering a constant mixed gas flow rate to the patient has been used. As an administration method, a nasal cannula in the form of inserting thin tubes into both nostrils and placing them over the ears can be used, or an oxygen mask can be used.

[0007] However, in a conventional high flow rate breathing therapy device, since the supply flow rate administered to the patient is larger than the flow rate that the patient inhales during spontaneous breathing, it reduces the patient's breathing effort during inhalation. However, during exhalation, due to the high flow rate nasal input, the air resistance increases compared to spontaneous breathing, and a burden can be imposed on the patient's exhalation effort.

[0008] Also, the start of the patient's inhalation mainly depends on the patient's will to breathe. In contrast, a conventional high flow rate breathing therapy device administers a mixed gas at the same flow rate regardless of the inhalation and exhalation times that can change depending on the patient's condition. Although there is an effect of the high flow rate therapy method, there is a problem that the burden on the patient's inhalation effort or exhalation effort cannot be reduced.

[0009] In particular, in high flow rate breathing therapy using a nasal cannula, even when supplying a mixed gas at the same flow rate, due to the size of the patient's nostrils, the wearing state of the cannula, and the anatomical characteristics of the nasal cavity and upper airway, it is detected that the resistance, bulk, and forced breathing are different, and there is a problem that it is difficult to perform an active breathing therapy that reduces the exhalation effort due to technical difficulties in synchronous detection (detection of inhalation and exhalation times).

Summary of the Invention

Problems to be Solved by the Invention

[0010] The present invention is for solving the above problems, detecting the time when the patient tries to start inhalation and the time when the patient tries to start exhalation, supplying a high flow rate mixed gas during inhalation to reduce dead space, and reducing the flow rate of the mixed gas during exhalation to reduce the patient's forced breathing. The object is to provide a high flow rate breathing therapy device and method by respiratory synchronization.

[0011] Furthermore, the present invention detects only the time when a patient starts to exhale, and normally supplies a mixed gas at a basic flow rate. However, when the patient's inhalation is completed and exhalation begins, a mixed gas with an exhaust assist flow rate lower than the basic flow rate is supplied to reduce the patient's exhalation effort, and the flow rate is increased in proportion to the reduction of the patient's exhalation effort and returned to the basic flow rate. An object thereof is to provide a high-flow respiratory therapy apparatus and method by respiratory synchronization.

Means for Solving the Problems

[0012] In order to solve the above-described problems, a high-flow respiratory therapy apparatus by respiratory synchronization according to an embodiment of the present invention includes a respiratory pattern monitoring unit that monitors changes in the flow rate and pressure of a mixed gas supplied to a patient to collect the patient's respiratory pattern information, an inhalation effort point detection unit that detects an inhalation effort point at which the patient tries to start inhalation from the patient's respiratory pattern information, an exhalation effort point detection unit that detects an exhalation effort point at which the patient tries to start exhalation from the patient's respiratory pattern information, and a supply flow rate control unit that increases the flow rate of the mixed gas when the patient's respiration reaches the inhalation effort point and decreases the flow rate of the mixed gas when the patient's respiration reaches the exhalation effort point and supplies it.

[0013] Moreover, a high-flow respiratory therapy apparatus by respiratory synchronization according to an embodiment of the present invention includes the respiratory pattern monitoring unit, the inhalation effort point detection unit, and the exhalation effort point detection unit, and further includes a respiratory synchronization unit that synchronizes the extracted inhalation effort point and exhalation effort point with the patient's respiratory pattern information, and the supply flow rate control unit can perform the flow rate control of the mixed gas in synchronization with the inhalation effort point and exhalation effort point synchronized by the respiratory synchronization unit.

[0014] On the one hand, a high-flow respiratory therapy device according to another embodiment of the present invention includes a respiratory pattern monitoring unit that monitors one or more of the flow rate change and pressure change of the mixed gas supplied to a patient to collect the respiratory pattern information of the patient, an exhaust effort point detection unit that detects an exhaust effort point at which the patient attempts to start exhaling from the collected respiratory pattern information, and a supply flow rate control unit that supplies a mixed gas at a determined basic flow rate when the patient's respiration starts and reduces the flow rate of the mixed gas by an exhaust assist flow rate when the respiration reaches the exhaust effort point to reduce the patient's exhaust effort.

[0015] Moreover, a high-flow respiratory therapy device according to another embodiment of the present invention includes the respiratory pattern monitoring unit and the exhaust effort point detection unit, and may further include a respiratory synchronization unit that synchronizes the extracted exhaust effort point with the respiratory pattern information of the patient. At this time, the supply flow rate control unit synchronizes and performs the flow rate control of the mixed gas with respect to the exhaust effort point synchronized by the respiratory synchronization unit.

[0016] On the one hand, a high-flow respiratory therapy method according to an embodiment of the present invention is a therapy method using a high-flow respiratory therapy device. In the respiratory pattern monitoring unit of the control unit in the device, it includes a step of monitoring the flow rate change and pressure change of the mixed gas supplied to a patient to collect the respiratory pattern information of the patient, a step of detecting, in the detection unit of the control unit, an inhalation effort point at which the patient attempts to start inhaling and an exhaust effort point at which the patient attempts to start exhaling from the respiratory pattern information of the patient, or only detecting the exhaust effort point, and a step of actively controlling the flow rate of the mixed gas corresponding to the inhalation effort point or the exhaust effort point in the supply flow rate control unit of the control unit.

[0017] After the detecting step, in the respiration synchronization unit of the control unit, a step of synchronizing the detected inspiration effort point or expiration effort point with the respiration pattern information of the patient can be further included. In this case, in the step of controlling the flow rate of the mixed gas, the supply flow rate control unit of the control unit synchronizes and performs the flow rate control of the mixed gas with respect to the inspiration effort point and expiration effort point synchronized in the respiration synchronization unit.

Advantages of the Invention

[0018] According to such a present invention, by supplying a mixed gas having a high flow rate sufficient to ventilate the patient's nasal cavity with fresh air during inspiration of the patient, clinically, the dead space is reduced, and during expiration of the patient, the effort of expiratory breathing is reduced, so that the effort breathing of the patient can be reduced.

Brief Description of the Drawings

[0019]

Figure 1

Figure 2

Figure 3

Figure 4

Figure 5

Figure 6

Figure 7

Figure 8

Figure 9

Figure 10

Figure 11

Embodiments for Carrying Out the Invention

[0020] Hereinafter, specific embodiments of the present invention will be described in detail with reference to the accompanying drawings.

[0021] FIG. 1 and FIG. 2 are diagrams showing the configuration of a high-flow respiratory therapy device according to an embodiment of the present invention.

[0022] The high-flow respiratory therapy device 100 by respiratory synchronization according to the embodiment of the present invention can include a mixed gas generation unit that generates a mixed gas containing oxygen and air, a flow rate sensor (110 in FIGS. 1 and 2), a blower (120 in FIGS. 1 and 2), a pressure sensor (130 in FIGS. 1 and 2), a humidifying unit (HF1 in FIGS. 1 and 2), a nasal cannula (C1 in FIGS. 1 and 2) provided with a supply hose (140 in FIGS. 1 and 2), and a control unit (150 in FIGS. 1 and 2).

[0023] The flow rate sensor FS1 can be installed at the front end of the blower 120 (see FIG. 1) or the rear end of the blower 120 (see FIG. 2) depending on the position and configuration to be sensed.

[0024] The pressure sensor 130 can be further arranged close to the patient, such as P2 in FIGS. 1 and 2. The pressure sensor 160 at the rear end has the advantage that it can measure the flow rate and pressure supplied to the patient so as to be close to the actual values. However, the measurement results can vary significantly depending on whether the nasal cannula 140 is detached or the state of wearing the cannula 140. With such a configuration, the high-flow respiratory therapy device 100 administers a heated and humidified mixed gas at a concentration higher than the oxygen concentration in the atmosphere to the patient, and is characterized in that it participates in the patient's breathing time and adjusts the flow rate and flow volume of the mixed gas according to the inhalation time and the exhalation time for administration.

[0025] In addition, the high-flow respiratory therapy device 100 according to the embodiment of the present invention solves the problem that it is detected that the sizes of the patient's nostrils, the wearing state of the cannula, the resistance, bulk, and forced breathing due to the anatomical characteristics of the nasal cavity and upper airway are different, and detects the inhalation time and the exhalation time based on the pressure and flow rate supplied to the patient and synchronizes with the patient's breathing cycle. For this purpose, the control unit 150 must be preceded by a breathing synchronization process of monitoring and synchronizing the patient's breathing before treatment.

[0026] Therefore, the high-flow respiratory therapy device 100 according to the embodiment of the present invention reduces the patient's forced breathing by increasing or decreasing the flow rate of the mixed gas at each inhalation time or exhalation time with reference to the inhalation time and the exhalation time synchronized by the control unit 150.

[0027] Specifically, two synchronization methods of the high-flow respiratory therapy device 100 according to the breathing synchronization according to the embodiment of the present invention are provided.

[0028] First Embodiment FIG. 3 is a diagram showing the configuration of a high-flow respiratory therapy device according to breathing synchronization according to the first embodiment of the present invention in the devices of FIGS. 1 and 2, FIG. 4 is a graph showing the values of monitoring the flow rate change of the mixed gas according to the first embodiment of the present invention, and FIGS. 5 and 6 are waveform diagrams showing examples of extracting the patient inhalation effort point and the exhalation effort point according to the change of the patient's breathing according to the first embodiment of the present invention.

[0029] For the sake of convenience of understanding, FIG. 3 will be described with reference to the waveforms shown in FIGS. 4 to 6.

[0030] The control unit 150A of the high-flow respiratory therapy device according to the first embodiment of the present invention includes a respiratory pattern monitoring unit 1511, a respiratory synchronization unit 1510 including an inspiration effort detection unit 1512 and an expiration effort detection unit 1513, and an intake and exhaust supply flow rate control unit 1520.

[0031] Here, the intake and exhaust supply flow rate control unit 1520 is configured to control the supply flow rate in conjunction with the respiratory synchronization unit 1510, and even if it is a control unit that controls the flow rate with the same function, it is classified according to the functional role.

[0032] The respiratory pattern monitoring unit 1511 monitors the flow rate change and pressure change of the mixed gas supplied to the patient using the flow rate sensor and pressure sensor of the high-flow respiratory therapy device (100 in FIGS. 1 and 2). Through such monitoring, the respiratory pattern information of the patient is collected.

[0033] Also, the respiratory pattern information and the effort breathing information in FIG. 5 can include the flow rate and pressure information detected from the flow rate sensor and the pressure sensor. It can be confirmed that the patient's flow rate increases at the inspiration effort point and decreases at the expiration effort point in the patient respiration-related waveform shown in FIG. 5.

[0034] The inspiration effort detection unit 1512 detects an inspiration effort point (A in FIG. 5) at which the patient tries to start inspiration from the patient's respiratory pattern information collected by the respiratory pattern monitoring unit 1511.

[0035] At the same time, the expiration effort detection unit 1513 detects an expiration effort point (B in FIG. 5) at which the patient tries to start expiration from the respiratory pattern information collected by the respiratory pattern monitoring unit 1511.

[0036] Specifically, the inspiratory effort detection unit 1512 extracts, from the patient's respiratory pattern information, the maximum inspiratory effort point (C in FIG. 5) where the change in inspiratory flow rate is the largest, and the expiratory effort stop point (E in FIG. 5) where breathing stops for a while before inspiration resumes after exhalation. Then, with reference to the extracted expiratory effort stop point (E in FIG. 5) and the maximum inspiratory effort point (C in FIG. 5), the inspiratory effort point (A in FIG. 5) at which the patient starts (initiates) the inspiratory effort between them is detected.

[0037] At this time, the inspiratory effort detection unit 1512 adds the patient's respiratory flow rates during one cycle, divides by the number, and detects the expiratory effort stop point from the average value. Using the expiratory effort stop point as zero, it can extract the relative positions of the maximum inspiratory effort point and the maximum expiratory effort point.

[0038] Also, the inspiratory effort detection unit 1512 calculates the scalar value between the expiratory effort stop point (E in FIG. 5) in the first cycle and the maximum inspiratory effort point (C in FIG. 5) in the second cycle with reference to at least two cycles, and detects, based on the calculated scalar value, the value corresponding to the range of 10 - 30% from the maximum inspiratory effort point (C in FIG. 5) as the inspiratory effort point (A in FIG. 5). Alternatively, the inspiratory effort detection unit 1512 may calculate the slope between the expiratory effort stop point (E in FIG. 5) in the first cycle and the maximum inspiratory effort point (C in FIG. 5) in the second cycle, and detect the inspiratory effort point (A in FIG. 5) based on the calculated slope.

[0039] The range of 10 - 30% may be set to vary depending on the patient's condition, the wearing state of the cannula, etc.

[0040] The effort point and the stop point are calculated in relation to the following formula.

[0041] [Formula 1] Effort = Pressure × Volume / time = Pressure × FlowL / min

[0042] The exhalation effort detection unit 1513 extracts, from the patient's respiration pattern information, the maximum exhalation effort point (D in FIG. 5) where the change in the patient's exhalation flow rate is the largest, and the exhalation effort stop point (E in FIG. 5) where respiration temporarily stops after exhalation and before inhalation. Then, with reference to the extracted maximum exhalation effort point (D in FIG. 5) and the exhalation effort stop point (E in FIG. 5), it detects the exhalation effort point (B in FIG. 5) at which the patient starts the exhalation effort (starts).

[0043] The exhalation effort stop point (E in FIG. 5) can be extracted from the average value obtained by adding the patient's respiration flow rates during one cycle and dividing by the number of them.

[0044] The exhalation effort detection unit 1513 can extract where the maximum exhalation effort point is relatively located with the exhalation effort stop point (E in FIG. 5) as the zero point.

[0045] Also, the exhalation effort detection unit 1513 calculates the scalar value between the exhalation effort stop point (E in FIG. 5) in the first cycle and the maximum exhalation effort point (D in FIG. 5) in the second cycle with reference to at least two cycles, and based on the calculated scalar value, it can detect as the exhalation effort point a value that falls within a predetermined range of 10% to 30% or less from the maximum exhalation effort point (D in FIG. 5). Alternatively, it may calculate the slope between the exhalation effort stop point (E in FIG. 5) in the first cycle and the maximum exhalation effort point (D in FIG. 5) in the second cycle, and detect the exhalation effort point based on the calculated slope.

[0046] The inhalation effort point A and the exhalation effort point B detected in this way correspond to the time points before each maximum inhalation effort point C and maximum exhalation effort point D in terms of time. Therefore, if the flow rate is controlled and supplied at the time points of the inhalation effort point and the exhalation effort point, when the patient inhales or exhales maximally, the patient's inhalation effort or exhalation effort can be effectively reduced.

[0047] The respiration synchronization unit 1510 includes a respiration pattern monitoring unit 1511, an inspiration effort detection unit 1512, and an expiration effort detection unit 1513, and synchronizes the inspiration effort point and the expiration effort point extracted from the inspiration effort detection unit 1512 and the expiration effort detection unit 1513 with the respiration pattern information of the patient, respectively. Thus, the respiration synchronization unit 1510 synchronizes the inspiration timing and the expiration timing with the respiration cycle of the patient.

[0048] The supply flow rate control unit 1520 also synchronizes and performs the flow rate control of the mixed gas with respect to the inspiration effort point and the expiration effort point synchronized by the respiration synchronization unit 1510.

[0049] That is, when the inspiration effort point is reached in the respiration cycle of the patient, the supply flow rate control unit 1520 increases the flow rate of the mixed gas in synchronization at this time point, and when the expiration effort point is reached, the flow rate of the mixed gas is decreased and supplied.

[0050] At this time, the supply flow rate control unit 1520 determines the flow rate at a level that can ventilate the patient's nasal cavity with fresh air as the basic flow rate (bias flow), and normally supplies it at the basic flow rate, and increases the supply by the assist flow rate portion to the basic flow rate during inspiration.

[0051] The assist flow rate can vary depending on the patient's condition, the magnitude of the patient's respiration, the wearing state of the cannula, and the like.

[0052] The flow rate at a level that fills the nasal cavity with fresh air can be determined based on clinical or anatomical criteria.

[0053] Therefore, when the patient's respiration starts or the operation starts after the cannula is attached, the high-flow respiration treatment device according to the first embodiment of the present invention supplies the mixed gas at the basic flow rate through the control of the control unit 150A, and supplies the inspiration flow rate increased by the assist flow rate portion to the basic flow rate when the inspiration effort point is reached. The inspiration flow rate is continuously supplied, and when the patient's inspiration ends and the expiration effort point is detected, the operation of decreasing the inspiration flow rate and switching to the basic flow rate is performed.

[0054] Such an operation results in a supply flow rate like the waveform shown in FIG. 4.

[0055] On the other hand, the waveform shown in the lower part of FIG. 5 shows the waveform for the patient's spontaneous breathing as a result of performing the breathing synchronization process of the device according to the first embodiment of the present invention with respect to the bias flow.

[0056] In FIG. 5, the reference line at the start of the cycle is a value corresponding to the bias flow.

[0057] On the other hand, FIG. 6 shows the waveform for the patient's spontaneous breathing as a result of performing the breathing synchronization process of the device according to the first embodiment of the present invention not only with respect to the bias flow but also with respect to the inspiratory flow rate.

[0058] That is, the first half of the cycle is the waveform obtained by performing the breathing synchronization process with the bias flow, and the second half of the cycle is the waveform obtained by performing the breathing synchronization process with the inspiratory flow rate (bias flow + assist flow). It can be confirmed that the reference line between the first half of the cycle and the second half of the cycle has changed.

[0059] Such a synchronization method is applicable when the treatment flow rate is changed and is considered to be a process of breathing synchronization in accordance with the new flow rate.

[0060] In the embodiment of FIG. 6, when detecting the inspiratory effort point and the expiratory effort point, if they are matched with the mixed gas flow rate in FIG. 4, the inspiratory effort point occurs when supplying the bias flow, and the expiratory effort point occurs when supplying the inspiratory flow rate. Therefore, when detecting each effort point, especially when detecting the inspiratory effort point, it is advantageous to synchronize the bias flow and detect it from the bias flow, and when detecting the expiratory effort point, it is advantageous to detect it from the inspiratory flow rate. This is an example of the detection method and is not limited thereto, and it may be detected from the bias flow regardless of the flow rate.

[0061] On the one hand, FIG. 7 is an operation flowchart for explaining a high-flow respiratory therapy method by respiratory synchronization according to the first embodiment of the present invention.

[0062] First, in step S100A, the control unit 150A performs a respiratory synchronization process to sense the patient's spontaneous breathing.

[0063] Specifically, the respiratory pattern monitoring unit 1511 in the control unit 150A monitors the flow rate change and pressure change of the mixed gas supplied to the patient to collect the patient's respiratory pattern information.

[0064] After that, the detection unit of the control unit 150A detects the inspiration effort point at which the patient tries to start inspiration and the expiration effort point at which the patient tries to start expiration from the patient's respiratory pattern information collected in the above process, or detects only the expiration effort point.

[0065] For example, the inspiration effort point detection unit 1512 of the control unit 150A detects the inspiration effort point, and the expiration effort point detection unit 1513 of the control unit 150A detects the expiration effort point.

[0066] Thereafter, the respiratory synchronization unit 1510 of the control unit 150A synchronizes the detected inspiration effort point and expiration effort point with the patient's respiratory pattern information.

[0067] Generally, the start of the patient's inspiration depends on the patient's will to breathe. Through such a respiratory synchronization process, the actual inspiration time and expiration time of the patient can be synchronized with the respiratory cycle respectively.

[0068] Next, in step S200A, the supply flow rate control unit 1520 of the control unit 150A actively controls the flow rate of the mixed gas corresponding to the inspiration effort point or the expiration effort point. In particular, the flow rate control can also be performed in synchronization with the inspiration effort point and expiration effort point synchronized by the respiratory synchronization unit.

[0069] Specifically, when the patient's breathing starts, the supply flow control unit 1520 supplies a mixed gas at a determined basic flow rate (bias flow). When it reaches the inspiration effort point, it increases the supply by the amount of the assist flow on top of the basic flow rate. When it reaches the expiration effort point, it decreases the supply from the basic flow rate.

[0070] Next, at step S300A, if there is a synchronization addition command by the operation of the user or doctor, the control unit 150A moves back to step S100A and operates. If the synchronization end is operated, this operation ends.

[0071] Second Embodiment FIG. 8 is a diagram showing the configuration of a breathing synchronization device according to the second embodiment of the present invention. FIG. 9 is a graph showing the values obtained by monitoring the flow rate change of the mixed gas according to the second embodiment of the present invention. FIG. 10 is a waveform diagram showing an example of extracting the patient's expiration effort point due to the change in the patient's breathing according to another second embodiment of the present invention.

[0072] First, referring to FIG. 8, the high-flow breathing treatment device according to the second embodiment of the present invention includes, as the control unit 150B, a breathing pattern monitoring unit 1511, a breathing synchronization unit 1510 including an expiration effort point detection unit 1513, and a supply flow control unit 1520.

[0073] The functions of each part perform the same functions as the components according to the first embodiment. However, in the second embodiment, only the expiration effort point is detected to control the flow rate of the mixed gas, and only the operation of the supply flow control unit 1520 is different.

[0074] The breathing pattern monitoring unit 1511 monitors one or more of the flow rate change and pressure change of the mixed gas supplied to the patient to collect the patient's breathing pattern information.

[0075] The expiration effort point detection unit 1513 detects the expiration effort point at which the patient tries to start expiration from the breathing pattern information collected by the breathing pattern monitoring unit 1511. The detection method is the same as the one described above.

[0076] The breathing synchronization unit 1510 is configured to include a breathing pattern monitoring unit 1511 and an expiration effort detection unit 1513, and synchronizes the expiration effort from the expiration effort detection unit 1513 with the breathing pattern information of the patient. As a result, the expiration timing is synchronized with the breathing cycle of the patient.

[0077] The supply flow rate control unit 1520 also synchronizes and performs the flow rate control of the mixed gas with respect to the expiration effort point synchronized by the breathing synchronization unit 1510.

[0078] That is, when the patient starts breathing, the supply flow rate control unit 1520 supplies and maintains at a determined basic flow rate (bias flow), and when it reaches the expiration effort point, it supplies at an expiration flow rate obtained by reducing the flow rate of the mixed gas by the amount of the expiration assist flow rate (relief flow) to reduce the expiration effort of the patient. After that, when the expiration effort decreases, the flow rate is increased in proportion to the reduction of the expiration effort as shown in FIG. 9. When it is increased to the basic flow rate, the basic flow rate is maintained until the next expiration effort point is detected.

[0079] In the second embodiment, the basic flow rate (bias flow) is determined to include a flow rate at a level that can ventilate the patient's nasal cavity with fresh air and the maximum inspiration flow rate of the patient.

[0080] Clinically, the maximum inspiration flow rate of the patient can be determined to be 3 to 4 times the respiratory volume per minute. The respiratory volume per minute is calculated by [one breath volume] × [respiratory rate per minute].

[0081] For example, assuming that the one breath volume is 500 ml and the average respiratory rate per minute is 14 times based on an adult, the respiratory volume per minute is approximately 7 L / min, and thereby the maximum inspiration flow rate is determined to be 20 to 30 LPM.

[0082] In this way, the flow rate at a level to fill the nasal cavity with fresh air and the maximum inspiration flow rate of the patient can be determined based on clinical or anatomical criteria.

[0083] FIG. 10 shows waveforms with respect to the patient's expiratory effort as a result of performing the breathing synchronization process of the apparatus according to the second embodiment of the present invention based on the bias flow.

[0084] Hereinafter, the operation of the high-flow respiratory therapy apparatus according to the second embodiment of the present invention will be described.

[0085] Referring to FIG. 11, at the S100B stage for the first time, the control unit 150B performs a breathing synchronization process to detect the patient's spontaneous breathing.

[0086] Specifically, the breathing pattern monitoring unit 1511 in the control unit 150B monitors the flow rate change and pressure change of the mixed gas supplied to the patient to collect the patient's breathing pattern information.

[0087] Thereafter, the expiratory effort detection unit 1513 of the control unit 150B detects only the expiratory effort point at which the patient tries to start exhaling from the patient's breathing pattern information collected through the above process.

[0088] Thereafter, the breathing synchronization unit 1510 of the control unit 150B synchronizes the detected expiratory effort point with the patient's breathing pattern information.

[0089] At the next S200B stage, the supply flow rate control unit 1520 of the control unit 150B actively controls the flow rate of the mixed gas corresponding to the expiratory effort point. In particular, the flow rate control can also be performed in synchronization with the expiratory effort point synchronized by the breathing synchronization unit 1510.

[0090] Specifically, when the patient's breathing starts, the supply flow rate control unit 1520 supplies the mixed gas at a predetermined bias flow rate. When it reaches the expiratory effort point, the flow rate of the mixed gas is decreased by the relief flow rate and supplied. Thereafter, the flow rate is increased in proportion to the reduction of the expiratory effort, and when the basic flow rate is reached, the basic flow rate is maintained until the next expiratory effort is detected.

[0091] In the next S300B stage, if there is an additional synchronization command by a user or an operation of intention, the control unit 150B moves back to the S100B stage and operates, and if the synchronization end is operated, this operation ends.

[0092] The above description is only an exemplary explanation of the present invention, and various modifications are possible within the scope not departing from the technical idea of the present invention by those with ordinary knowledge in the technical field to which the present invention belongs. Therefore, the embodiments disclosed in the specification of the present invention do not limit the present invention. The scope of the present invention should be construed by the following claims, and various equivalents and modifications that could be substituted at the time of filing this application should be construed as belonging to the scope of the present invention.

[0093] Various embodiments have been described as the best mode for carrying out the present invention.

Industrial Applicability

[0094] The present invention is used in the field related to high-flow respiratory therapy devices by respiratory synchronization.

[0095] It is obvious to those skilled in the art that various changes and modifications can be made to the present invention without departing from the spirit and scope of the present invention. Therefore, the present invention is intended to include the changes and modifications of the present invention provided within the scope of the appended claims and their equivalents.

Claims

1. A respiratory pattern monitoring unit that monitors changes in the flow rate and pressure of a mixed gas supplied to a patient to collect respiratory pattern information of the patient; An inspiration effort point detection unit that detects an inspiration effort point at which the patient tries to start inspiration from the respiratory pattern information of the patient; An expiration effort point detection unit that detects an expiration effort point at which the patient tries to start expiration from the respiratory pattern information of the patient; A supply flow rate control unit that increases the flow rate of the mixed gas when the patient's respiration reaches the inspiration effort point and decreases the flow rate of the mixed gas when the patient's respiration reaches the expiration effort point for supply; The inspiration effort point detection unit: Extracts, from the respiratory pattern information of the patient, an inspiration maximum effort point at which the change in inspiration flow rate is the largest and an expiration effort stop point at which respiration stops for a while before inspiration starts again after expiration, and detects the inspiration effort point at which the patient starts inspiration effort between them with reference to the extracted expiration effort stop point and inspiration maximum effort point; The expiration effort point detection unit: Extracts, from the respiratory pattern information of the patient, an expiration maximum effort point at which the change in expiration flow rate is the largest and an expiration effort stop point at which respiration stops for a while before inspiration starts again after expiration, calculates a scalar value between the expiration effort stop point in the first cycle and the expiration maximum effort point in the second cycle with reference to at least two cycles, and detects, based on the calculated scalar value, a value corresponding to a predetermined range of 10% to 30% or less from the expiration maximum effort point as the expiration effort point; The expiration effort stop point is extracted as a point at which the respiratory flow rate temporarily stops from the average value obtained by adding the respiratory flow rates of the patient in one respiratory cycle for a plurality of respiratory cycles and dividing by the number of added respiratory cycles. A high-flow respiratory therapy device by respiratory synchronization.

2. Comprising the respiratory pattern monitoring unit, the inspiration effort point detection unit, and the expiration effort point detection unit, and further comprising a respiratory synchronization unit that synchronizes the inspiration effort point extracted by the inspiration effort point detection unit and the expiration effort point extracted by the expiration effort point detection unit with the respiratory pattern information of the patient; The supply flow rate control unit: The high-flow respiratory therapy device by respiratory synchronization according to claim 1, characterized in that the flow rate control of the mixed gas is synchronized and performed for the inspiration effort point and expiration effort point synchronized by the respiratory synchronization unit.

3. The supply flow rate control unit defines a basic flow rate (bias flow) including a flow rate at a level capable of ventilating the nasal cavity of the patient with fresh air and the maximum inhalation flow rate of the patient, and when the patient starts breathing, supplies the mixed gas at the basic flow rate, and when it reaches the inhalation effort point, supplies the mixed gas with an increase of an assist flow rate added to the basic flow rate, and when it reaches the exhalation effort point, supplies the mixed gas with a decrease. The high-flow respiratory therapy device according to claim 1, characterized in that.

4. The high-flow respiratory therapy device according to claim 3, characterized in that the maximum inhalation flow rate of the patient is calculated as 3 to 4 times the respiratory volume per minute.

5. A control method for a high-flow respiratory therapy device, in the respiration pattern monitoring unit of the control unit in the device, monitoring the flow rate change and pressure change of the mixed gas supplied to the patient to collect the respiration pattern information of the patient; in the detection unit of the control unit, detecting an inhalation effort point at which the patient tries to start inhalation and an exhalation effort point at which the patient tries to start exhalation from the respiration pattern information of the patient, or detecting only the exhalation effort point; in the supply flow rate control unit of the control unit, when the patient's respiration reaches the inhalation effort point, increasing the flow rate of the mixed gas, and when the patient's respiration reaches the exhalation effort point, controlling to decrease the flow rate of the mixed gas, including, in the step of detecting the inhalation effort point and the exhalation effort point, or detecting only the exhalation effort point, the inhalation effort point detection unit extracts, from the respiration pattern information of the patient, a maximum inhalation effort point at which the change in inhalation flow rate is the largest and an exhalation effort stop point at which respiration stops for a while before inhalation again after exhalation, and referring to the extracted exhalation effort stop point and the maximum inhalation effort point, detects the inhalation effort point at which the patient starts inhalation effort between them. The exhalation effort detection unit extracts, from the respiration pattern information of the patient, an exhalation maximum effort point where the change in the exhalation flow rate is the largest and an exhalation effort stop point where respiration temporarily stops before inhalation again after exhalation, respectively, calculates a scalar value between the exhalation effort stop point in the first cycle and the exhalation maximum effort point in the second cycle with reference to at least two cycles, and detects, based on the calculated scalar value, a value falling within a predetermined range of 10% to 30% or less from the exhalation maximum effort point as the exhalation effort point. The exhalation effort stop point is characterized by being extracted as a point where the respiration flow rate temporarily stops from the average value obtained by adding the respiration flow rates of the patient in one respiration cycle for a plurality of respiration cycles and dividing by the number of added respiration cycles. A control method for a high-flow respiration treatment device by respiration synchronization.

6. After the step of detecting the inhalation effort point and the exhalation effort point, or only the exhalation effort point. The method further includes, in the respiration synchronization unit of the control unit, the step of synchronizing the detected inhalation effort point or the exhalation effort point with the respiration pattern information of the patient. In the step of controlling the flow rate of the mixed gas. The control method for a high-flow respiration treatment device by respiration synchronization according to claim 5, characterized in that the supply flow rate control unit of the control unit synchronizes and performs the flow rate control of the mixed gas with respect to the inhalation effort point and the exhalation effort point synchronized by the respiration synchronization unit.

7. When the inhalation effort point and the exhalation effort point are detected in the detecting step. In the step of controlling the flow rate of the mixed gas. When the respiration of the patient starts, a mixed gas with a determined basic flow rate is supplied, when it reaches the inhalation effort point, the supply is increased by an assist flow rate from the basic flow rate, and when it reaches the exhalation effort point, the supply is decreased from the basic flow rate. The control method for a high-flow respiration treatment device by respiration synchronization according to claim 5.

8. When only the exhalation effort point is detected in the detecting step. In the step of controlling the flow rate of the mixed gas. When the respiration of the patient starts, a mixed gas with a determined basic flow rate is supplied. When the respiration reaches the exhaust effort point, the flow rate of the mixed gas is decreased by an exhaust assist flow rate (relief flow). Thereafter, the flow rate is increased to the basic flow rate in proportion to the reduction of the exhaust effort and maintained, thereby reducing the exhaust effort of the patient. A control method of a high-flow respiration device by respiration synchronization according to claim 5, characterized in that.

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