JP2006280615A - Condition analysis apparatus and software program - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a condition analysis apparatus and a software program capable discriminating abnormality possibly to be present even though an object makes a periodic movement. <P>SOLUTION: This condition analysis apparatus is constituted to have a first condition discrimination means 24 discriminating whether the condition of the object 2 in a determination object time is abnormal or not according to data probability distribution related to the extent of the periodic movement in a second prescribed time T2 before a first prescribed time T1 before and after the determination object time based on measurement data indicating the condition of the object 2 making the periodic movement and the extent of the periodic movement in the first prescribed time T1. This condition analysis apparatus can determine the abnormality possibly to be present, even though the object makes the periodic movement. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to a state analysis device and a software program, and more particularly to a state analysis device and a software program that can discriminate an abnormality that may exist despite a periodic movement of an object.

2. Description of the Related Art Conventionally, a motion detection sensor has been proposed as a motion detection device that detects a motion of an object in a space, for example, a bathroom or a toilet, for example, a person. As a typical example, there is a monitoring device that monitors a sleeper's breathing by calculating a pattern movement amount from an image obtained by continuously projecting the projected pattern onto a sleeper on the bed. there were. (For example, refer to Patent Document 1).
JP 2002-175582 A (page 5-9, FIG. 1-13)

  With the conventional apparatus as described above, for example, it is possible to measure and monitor the increase or decrease and the amount of respiratory movement of a patient, and to detect the presence or absence of breathing. For example, nerves during artificial respiration such as muscular dystrophy patients There was a patient breathing monitoring device aimed at detecting ventilator circuit failure in patients with muscle disease. In this case, for example, in the monitoring device described in Patent Document 1, the generated signal related to respiratory motion is compared with a reference value for determination extracted from a value related to respiratory motion for a certain period before the determination target time point. There was something that judged the stop or decline of respiratory movement.

  However, for example, when the patient shifts to spontaneous breathing due to a disconnection of the breathing circuit, the patient acquires a large amount of data in a dangerous state, extracts feature quantities for determination, or assembles determination logic. Doing so puts a heavy burden on the patient and should be avoided ethically as much as possible to expose the patient to danger. That is, for example, since data acquisition when the patient's breathing is in an abnormal state places a heavy burden on the subject, there may be cases where sufficient data for forming a discrimination region between the normal state and the abnormal state cannot be acquired. Therefore, there has been a demand for an apparatus that can determine a patient's condition without imposing a heavy burden on the patient.

  Therefore, an object of the present invention is to provide a state analysis apparatus and a software program that can discriminate abnormalities that may exist even though the object has a periodic movement.

  In order to achieve the above object, the state analysis apparatus according to the first aspect of the present invention provides a determination target time point based on measurement data indicating a state of a target object 2 having a periodic motion, as shown in FIG. A probability distribution of data related to the magnitude of the periodic motion in the second predetermined period T2 (for example, see FIG. 3) before and after the first predetermined period T1 (for example, see FIG. 3), and the first predetermined period It is configured to include first state determination means 24 for determining whether or not the state of the object 2 at the determination target time point is abnormal according to the magnitude of the periodic movement in the period T1 (for example, see FIG. 3). Is done.

  If comprised in this way, the 1st state discrimination | determination means will be according to the probability distribution of the data regarding the magnitude | size of the periodic motion of the 2nd predetermined period, and the magnitude of the periodic motion of the 1st predetermined period, Since it is determined whether or not the state of the object at the determination target time is abnormal, it is possible to provide a state analysis apparatus that can determine the state of the object without imposing a burden on the object as much as possible. Furthermore, it can be set as the state analysis apparatus which can discriminate | determine the abnormality which may exist although there exists a periodic motion in a target object.

  Further, as described in claim 2, in the state analyzing apparatus according to claim 1, as shown in FIG. 1, for example, the first state determining means 24 is provided with the second predetermined period T2 (see, for example, FIG. 3). ) Of a predetermined range obtained from the distribution of data related to the magnitude of the periodic motion in the first predetermined period T1 (for example, see FIG. 3) based on the probability distribution of the data related to the magnitude of the periodic motion in FIG. A first probability of occurrence of the state may be estimated, and the abnormality of the object 2 may be determined using the first probability.

  If comprised in this way, a 1st state discrimination | determination means will be related with the magnitude | size of the periodic motion of the 1st predetermined period based on the probability distribution of the data regarding the magnitude | size of the periodic motion of the 2nd predetermined period. A first probability that a distribution state in a predetermined range determined from the data distribution occurs is estimated. Furthermore, since the first state determination means determines the abnormality of the object using the estimated first probability, for example, it is possible to determine the abnormality of the object without acquiring a large amount of data. .

  For example, a distribution state in a predetermined range obtained from a distribution of data relating to the magnitude of the periodic movement in the first predetermined period is a distribution in which the average of the magnitude of the periodic movement in the first predetermined period is a or less. It is assumed that it is in a state. In this case, if the average value of the data relating to the magnitude of the periodic movement in the second predetermined period is μ, the standard deviation is σ, and the number of data is n, if n is sufficiently large, the periodic value of the first predetermined period The distribution of the average value of the magnitudes of various movements can be regarded as a normal distribution having an average value μ and a standard deviation σ / √n. The first probability can be obtained as a probability equal to or lower than the value a of the normal distribution, that is, a lower probability of the value a of the normal distribution. For example, the distribution state of a predetermined range obtained from the distribution of data regarding the magnitude of the periodic movement in the first predetermined period is represented by the maximum value of the periodic movement magnitude in the first predetermined period as a ′. Even in the case of the following distribution state, the first probability can be similarly obtained from the data distribution in the second predetermined period (see, for example, FIG. 4).

  Further, as described in claim 3, in the state analyzing apparatus described in claim 1, as shown in FIG. 1, for example, the first state determining means 24 is provided with the second predetermined period T2 (see, for example, FIG. 3). ) Based on the probability distribution of the data regarding the magnitude of the periodic motion in (1), with respect to the magnitude of the periodic motion in the first predetermined period T1 (for example, see FIG. 3), the distribution of the predetermined range obtained from the distribution The predetermined range in which the occurrence probability of the state is equal to or less than the second probability is estimated, and the distribution state of data relating to the magnitude of the periodic motion in the first predetermined period T1 (for example, see FIG. 3) is the predetermined range. It may be configured to determine abnormality of the object based on whether or not it is included.

  If comprised in this way, a 1st state discrimination | determination means will be related with the magnitude | size of the periodic motion of a 1st predetermined period based on the probability distribution of the data regarding the magnitude | size of the periodic motion of a 2nd predetermined period. The predetermined range in which the occurrence probability of the distribution state in the predetermined range obtained from the distribution is equal to or less than the second probability is estimated. Further, the first state determination means determines abnormality of the object based on whether or not the distribution state of the data relating to the magnitude of the periodic movement in the first predetermined period is included in the predetermined range. For example, the abnormality of the target can be determined without acquiring a large amount of learning data. Note that the second probability is, for example, an arbitrary probability set in advance, such as an arbitrary probability derived from a medical viewpoint, a false alarm frequency targeted by the state analysis apparatus, or the like.

  Further, as described in claim 4, in the state analyzing apparatus described in claim 3, as shown in FIG. 1, for example, the first state determining means 24 is provided with a second predetermined period T2 (see, for example, FIG. 3). ) To calculate a threshold value based on the probability distribution of the data related to the periodic motion magnitude and the second probability, and the magnitude of the periodic motion magnitude within the first predetermined period T1 (for example, see FIG. 3). When the maximum value falls below a threshold value, the object may be determined to be abnormal.

  With this configuration, the threshold value is set based on the probability distribution of the data related to the magnitude of the periodic movement in the second predetermined period and the second probability, and as much as possible according to the condition specific to the object. Since a high threshold can be set, it is possible to prevent omission of detection while preventing false alarms.

For example, referring to FIG. 4B, which is an example of a probability distribution of data related to the magnitude of the periodic movement in the second predetermined period, the threshold value is the respiration rate n _v / min = 20 times / min. once false alarm frequency as the second probability 30 days _{(t e} s = 2592000 sec), i.e., 1 / in 2592000, the first predetermined time period T1, the length of the second predetermined time period T2 _{t 0} seconds = Assuming 30 seconds, the probability P _t ≈0.488 from equation (1) described later. If P _t ≈0.488, using the cumulative frequency distribution diagram of FIG. 4 (b), the corresponding class is about “4.8”. Here, the determination threshold is “5” in consideration of safety. do it.

  In addition, as described in claim 5, in the state analysis apparatus described in any one of claims 1 to 4, for example, as shown in FIG. You may comprise so that the 2nd state discrimination | determination means 25 which discriminate | determines whether the state of the target object 2 in a determination object time point is abnormal according to the comparison result with a reference value.

  If comprised in this way, a 1st state determination part and a 2nd state determination part are combined, and it can discriminate | determine comprehensively and without a leak and with few false alarms.

  Further, as described in claim 6, in the state analysis apparatus described in claim 5, for example, as shown in FIG. 1, the spectrum calculating means 26 for calculating the spectrum for the third predetermined period based on the measurement data, A spectrum comparison unit 27 that compares a low frequency component and a high frequency component of the spectrum based on the spectrum; the second state determination unit 25 determines whether the object is based on the comparison result of the spectrum comparison unit 27; You may comprise so that abnormality may be discriminate | determined.

  If comprised in this way, a spectrum calculation means will calculate a spectrum based on the measurement data which show the state of the target object with a periodic motion, and a spectrum comparison means will compare the low frequency component and high frequency component of a spectrum. Since the second state determination means determines the abnormality of the object based on the comparison result, it is possible to provide a state analysis apparatus that can more reliably determine the state of the object. For example, when the object is a breathing person, the low frequency component is a component having a frequency close to respiration, and the high frequency component is typically a noise frequency component other than respiration.

  Note that the second state determination unit typically has an abnormal object when the sum of the spectra of the low-frequency components continuously falls below the sum of the spectra of the high-frequency components for a fourth predetermined period. It may be configured to discriminate. In this case, the state of the object can be determined more reliably.

  Further, the second state determination unit typically has a case where the average of the fifth predetermined period of the sum of the low-frequency component spectra falls below the average of the fifth predetermined period of the sum of the high-frequency component spectra. In addition, it may be configured to determine that the object is abnormal. In this case, the state of the object can be determined more reliably and quickly.

  Further, as described in claim 7, in the state analysis apparatus according to any one of claims 1 to 6, the first state determination unit 24 further includes a periodic motion at a determination target time point. You may comprise so that it may discriminate | determine that a target object is abnormal when a period changes.

  If comprised in this way, since the 1st state discrimination | determination means will discriminate | determine that a target object is abnormal when the period of the periodic motion at the time of judgment object fluctuates, it can prevent incorrect discrimination. .

  Further, as described in claim 8, in the state analysis apparatus according to any one of claims 1 to 7, for example, as shown in FIG. 1, it occurs with periodic movement based on measurement data. A non-periodic motion detecting means 28 for determining and detecting a non-periodic movement is provided; the first state determining means 24 is a first predetermined period T1 (for example, see FIG. 3) or a second predetermined period T2. (For example, refer to FIG. 3) may be configured to be a period excluding the period in which the aperiodic motion detection unit 28 detects the aperiodic motion.

  With this configuration, the non-periodic motion detection unit determines and detects the non-periodic motion that occurs along with the periodic motion based on the measurement data, and the first state determination unit includes the first predetermined period. Alternatively, since the second predetermined period is a period excluding the period in which the non-periodic motion is detected, accurate determination can be performed. For example, when the object is a breathing person, the non-periodic movement is a body movement such as turning over.

  Further, as described in claim 9, in the state analysis device according to any one of claims 1 to 8, the magnitude of the periodic movement is obtained by integrating measurement data from zero cross to zero cross. You may comprise so that the value obtained by may be used.

  With this configuration, the value obtained by integrating the measurement data from zero cross to zero cross is used for the magnitude of the periodic movement, so changes in both amplitude and period of the measurement data Therefore, the abnormality can be determined with higher accuracy.

  Further, as described in claim 10, the state analysis apparatus according to any one of claims 1 to 9 includes a measurement apparatus 10 that acquires measurement data, for example, as shown in FIG. The apparatus 10 projects a plurality of bright spots 11b (see, for example, FIG. 10) onto the target area 3 (see, for example, FIG. 10), and a target area in which the plurality of bright spots 11b (see, for example, FIG. 10) are projected. 3 (for example, see FIG. 10), and the amount of movement between two frames of a plurality of bright spots 11b (for example, see FIG. 10) is calculated from two frames of images acquired at different times by the imaging device 12. The movement amount calculation unit 141 may be configured to include the movement amount waveform generation unit 142 that generates movement amount waveform data in which the movement amounts are arranged in time series.

  If comprised in this way, since a measuring apparatus is provided and measurement data are acquired from the measuring apparatus, the state of a target object can be measured correctly. Further, since the measuring device is configured to include the projection device, the imaging device, the movement amount calculating means, and the movement amount waveform generating means, it is possible to accurately measure the state of the object without contact, for example.

  In order to achieve the above object, a software program according to an eleventh aspect of the present invention is a software program that is installed in a computer and operates as a state analysis device, for example, as shown in FIG. A second predetermined period T2 (for example, FIG. 3) before the first predetermined period T1 (for example, see FIG. 3) before and after the determination target time point based on the measurement data indicating the state of the object having a periodic movement. The state of the object at the determination target time point according to the probability distribution of the data regarding the magnitude of the periodic motion of (see FIG. 3) and the magnitude of the periodic motion during the first predetermined period T1 (for example, see FIG. 3). Is configured to control the computer to execute a process (S108) for determining whether or not the abnormality is abnormal.

  According to this configuration, the state of the object at the determination target time point according to the probability distribution of the data related to the magnitude of the periodic movement in the second predetermined period and the magnitude of the periodic movement in the first predetermined period. Therefore, it is possible to provide a software program that can determine the state of an object without imposing a burden on the object as much as possible. Furthermore, it can be set as the software program which can discriminate | determine the abnormality which may exist although there exists a periodic motion in a target object.

  In order to achieve the above object, a state analysis apparatus according to a twelfth aspect of the present invention provides a determination target time point based on measurement data indicating a state of a target object 2 having a periodic motion, as shown in FIG. The state of the object 2 at the determination target time point is abnormal based on the comparison between the maximum value and the maximum threshold value of the data relating to the magnitude of the periodic movement in the first predetermined period T1 before and after (for example, see FIG. 3) It is comprised so that the 1st state determination means 24 which discriminate | determines may be provided.

  If comprised in this way, a 1st state discrimination | determination means will be the magnitude | size of the periodic motion of the 1st predetermined period before and behind a determination object time based on the measurement data which show the state of the target object with a periodic motion. The maximum value of the data regarding the thickness is compared with the maximum threshold value. Furthermore, since it is determined whether or not the state of the object at the determination target time point is abnormal based on the result of the comparison, it is possible to determine an abnormality that may exist despite a periodic movement of the object. It is possible to provide a state analysis apparatus that can perform this.

  As described above, according to the present invention, based on the measurement data indicating the state of an object with periodic movement, the periodicity of the second predetermined period before the first predetermined period before and after the determination target time point. First state determination means for determining whether or not the state of the object at the determination target time point is abnormal according to the probability distribution of the data relating to the amount of movement and the periodic movement amount in the first predetermined period. Therefore, it is possible to provide a state analysis apparatus that can determine an abnormality that may exist even though the object has a periodic movement.

  Embodiments of the present invention will be described below with reference to the drawings. In addition, in each figure, the same code | symbol is attached | subjected to the mutually same or equivalent member, and the overlapping description is abbreviate | omitted.

  FIG. 1 is a block diagram showing a configuration example of a respiration monitor 1 as a state analysis apparatus according to an embodiment of the present invention. The respiratory monitor 1 includes an arithmetic device 20 and an FG sensor 10 as a measuring device that acquires measurement data indicating the state of an object with periodic motion. The arithmetic unit 20 is, for example, a computer such as a personal computer or a microcomputer. The computing device 20 also has an input device 35 for inputting information for operating the respiration monitor 1 and a display 40 for displaying the processing state of the respiration monitor 1. The input device 35 is, for example, a touch panel, a keyboard, or a mouse. The display 40 is typically an LCD (Liquid Crystal Display, liquid crystal display device). The processing state of the respiratory monitor 1 displayed on the display 40 includes, for example, measurement data acquired by an FG sensor 10 described later, a spectrum compared by a spectrum comparison unit 27 described later, a first state determination unit 24 described below, and a second state determination unit 24 described later. Is a result of determining the state of the object 2 by the state determining unit 25. In this figure, the input device 35 and the display 40 are illustrated as being externally attached to the arithmetic device 20, but may be incorporated. The FG sensor 10 will be described in detail with reference to FIG.

  The computing device 20 relates to the magnitude of the periodic motion in the second predetermined period before the first predetermined period before and after the determination target time point based on the measurement data indicating the state of the object with periodic movement. First as first state determination means for determining whether or not the state of the object at the determination target time point is abnormal according to the probability distribution of the data and the magnitude of the periodic movement in the first predetermined period. A state determination unit 24 is provided.

  Further, the arithmetic unit 20 determines whether or not the state of the object at the determination target time point is abnormal according to the comparison result with the reference value based on the measurement data of the third predetermined period. A second state determination unit 25 is provided as means. In addition, the arithmetic device 20 typically has a spectrum calculation unit 26 as a spectrum calculation unit that calculates a spectrum for a third predetermined period based on measurement data indicating the state of the object 2 having a periodic motion. And a spectrum comparison unit 27 as spectrum comparison means for comparing the low-frequency component and the high-frequency component of the spectrum based on the spectrum. An abnormality of the object 2 is determined based on the comparison result.

  Further, the arithmetic unit 20 includes a body motion detection unit 28 as a non-periodic motion detecting means for determining and detecting a non-periodic motion that occurs with the periodic motion based on the measurement data, The state determination unit 24 is configured so that the first predetermined period or the second predetermined period is a period excluding the period in which the non-periodic motion is detected by the body motion detection unit 28.

  The main predetermined period of the present embodiment includes the first predetermined period to the eighth predetermined period. These predetermined periods will be sequentially described later. However, the order is not necessarily number order.

  In addition, here, the first state determination unit 24 and the second state determination unit 25 are described as being configured separately, but may be configured integrally.

  Here, although the target object is described as being the person 2 in the present embodiment, it may be a domestic animal such as a cow or a pig. Livestock includes pets such as cats and dogs. Hereinafter, the object is described as a person 2. Here, the case where the person 2 is performing artificial respiration on the bed 3 will be described. Here, the periodic motion is, for example, the respiratory motion of the human 2, and the non-periodic motion is, for example, a body motion other than the respiratory motion of the human 2 (hereinafter referred to as “body motion unless otherwise noted”). "). It should be noted that the respiratory motion of the human 2 is actually unstable in later-described waveform data indicating the respiratory motion, such as its period and amplitude. In extreme cases, the amplitude may be lost, but there is some instability. If so, it can be ignored and analyzed. The body movement of the person 2 is a movement of the person 2 that is less periodic than breathing, such as turning over, and is larger than the breathing. Further, the movement of the person 2 larger than the respiration is characterized by respiration, for example, by the magnitude of the movement or the magnitude of the change in movement.

  Here, the person 2 is abnormal in the present embodiment, a state in which the artificial respiration circuit of the person 2 performing artificial respiration is abnormal, typically a state in which artificial respiration does not substantially work. Say. That is, the respiration monitor 1 is a device that detects an abnormality in the artificial respiration circuit of the person 2 who is performing artificial respiration, and monitors artificial respiration such as a muscular dystrophy patient or an amyotrophic lateral sclerosis (ALS) patient. However, the device is intended to prevent accidents of artificial respiration.

  Although artificial respiration plays an important role in prolonging the lives of patients with muscular dystrophy and amyotrophic lateral sclerosis (ALS), troubles of artificial respiration frequently occur. Especially for patients with low spontaneous breathing and communication ability, ventilator troubles directly lead to serious accidents, so not only rely on the ventilator (not shown) alarm function, but also double and triple safety measures. is necessary.

  Therefore, the respiratory monitor 1 that monitors artificial respiration needs to detect some abnormalities and dangers. For example, the first is detection of respiratory stop when a patient who has little spontaneous breathing, such as a patient undergoing artificial respiration by tracheostomy, becomes unable to breathe due to disconnection of an artificial respiration circuit or the like. In this case, a respiratory motion waveform acquired by the FG sensor 10 to be described later disappears, and discovery and notification are required as soon as possible. The second is a case where artificial respiration substantially fails in a patient with a certain spontaneous breathing. In this case, the patient's breathing state changes, in other words, modulation of breathing is expected, but is not as clear and difficult to detect as breathing arrest. Instead, it is desirable to find it as early as possible, but even if it takes a little time to find it, it will not cause a serious accident immediately.

  More specifically, in the present embodiment, the person 2 is abnormal, for example, a state in which the respirator of the person 2 without spontaneous breathing has been removed and the breathing has stopped, or a person with some spontaneous breathing The state in which the second ventilator is removed and the artificial respiration does not substantially work, in other words, the state in which the person 2 has trouble in the artificial respiration.

  In the present embodiment, the measurement data is data measured by the FG sensor 10. The measurement data indicating the state of the person 2 is the amount related to the movement of the person 2 within a certain time within the measurement range (for example, the range including the chest and abdomen of the person 2), more specifically, the vertical movement of the body surface. It is a quantity related to speed. The measurement data indicating the state of the person 2 is data based on the measurement results obtained by measuring the movement of the person 2 at a plurality of points, and is the first measurement data based on the sum of the measurement values at the plurality of points. And / or body motion data as second measurement data, which is data of the sum of absolute values of measurement values at a plurality of points. The sum of absolute values is a concept including the sum of the squares of the measured values. Here, the measurement data includes both respiration data and body movement data. Further, the respiration data and the body movement data may be data obtained by further dividing the number of measurement points or the number of measurement points in which the measurement value has changed more than a certain value.

  FIG. 2 is a schematic diagram showing an example of a waveform pattern formed by respiration data and body motion data used in the respiration monitor according to the embodiment of the present invention. For example, the measurement data forms a waveform pattern as shown in FIG. FIG. 2A is an example in which the respiration data when the normal respiration of the person 2 is measured is simplified. FIG. 2B is a typical example of respiratory data including data indicating body movement, and FIG. 2C is a typical example of body movement data including data indicating body movement. As shown in FIGS. 2 (b) and 2 (c), when there is a body movement (body movement) other than breathing, the body movement data has a large distribution, and at the same time, the fluctuation width of the breathing data is also large. Grows and loses periodicity. Here, the sampling interval of measurement data (acquisition interval of one data) is, for example, 0.1 to 0.25 seconds. Further, here, each measurement value obtained by measuring the movement of the person 2 at a plurality of points is a value related to the movement of the person 2 within a predetermined time, in other words, the movement speed of the person 2. Therefore, by adding the measurement values at each measurement point, it is possible to obtain data relating to the overall average position change in a certain direction within a certain period (breathing data). Further, if the absolute values of the respective measured values are added together, data relating to the total amount of the entire movement can be obtained (body movement data). Here, the case where both respiration data and body motion data are used will be described. However, for example, all processes described below can be performed using only respiration data.

  The determination of the state of the measurement data acquired from the FG sensor 10 by the present apparatus may be performed after the measurement data for a certain period is acquired, or the data may be acquired along with the state transition of the person 2. However, it may be performed in real time. In the present embodiment, as described above, since the respiratory monitor 1 is a device that detects an abnormality in the artificial respiration circuit of the person 2 who is performing artificial respiration, the state determination is accompanied by the state transition of the person 2. The case where data acquisition is performed in real time will be described.

Here, the determination target time point is a time point at which the abnormality of the person 2 is determined, and the time point sequentially moves with time. The intervals between the determination target times are set at almost equal intervals at each time point, and may be appropriately determined according to, for example, the sampling interval of measurement data. That is, here, the interval of the determination target time points (1 data acquisition interval) is, for example, about 0.1 to 0.25 seconds.
Hereinafter, each of the above-described configurations will be described in detail with reference to FIG. 1 again.

  Specifically, the first state determination unit 24 determines the distribution of the respiratory motion magnitude in the first predetermined period based on the probability distribution of the data related to the respiratory motion magnitude in the second predetermined period. A predetermined range in which the occurrence probability of the distribution state in the predetermined range obtained from the second probability (the first probability will be described later) is estimated, and the magnitude of the periodic motion in the first predetermined period An abnormality of the person 2 is determined based on whether or not the data distribution state is included in the predetermined range.

  Here, FIG. 3 is a diagram for explaining the observation period T1 as the first predetermined period and the reference data acquisition period T2 as the second predetermined period, which are used in the respiratory monitor 1 according to the embodiment of the present invention. . In the figure, the left side is a time series of the past side and the right side is the future side.

  The first predetermined period is a period before and after the determination target time point, and is a period during which data relating to the magnitude of breathing movement is actually observed in order to determine the abnormality of the person 2 at the determination target time point. In the present embodiment, since the respiratory monitor 1 is a device that determines the state in real time, the first predetermined period is a period before the determination target time point. Note that if the determination is not made in real time, the first predetermined period may be a period that crosses the determination target time point. Hereinafter, the first predetermined period is referred to as an observation period T1 unless otherwise specified.

  The second predetermined period is a period before the observation period T1, and is used for acquiring data serving as a reference for estimating a distribution range in which the probability of occurrence of the probability distribution of the data in the observation period T1 is equal to or less than the second probability. It is a period. In the present embodiment, the first state determination unit 24 estimates a distribution range in which the probability of occurrence of the probability distribution of the data in the observation period T1 is less than or equal to the second probability from the probability distribution of the data in the second predetermined period. Therefore, the second predetermined period is set to a period as close as possible to the observation period T1, that is, a period immediately before the observation period T1, so that more reliable estimation can be performed. Note that the second predetermined period may be a period slightly spaced from the observation period T1 as long as it is a period before the observation period T1. Note that the reference data acquisition period T2 may partially overlap the observation period T1. Hereinafter, the second predetermined period is referred to as a reference data acquisition period T2 unless otherwise specified.

  Note that the lengths of the observation period T1 and the reference data acquisition period T2 are typically set to the same length in order to accurately perform the determination by the first state determination unit 24. The period may be, for example, about 30 seconds to 5 minutes, preferably about 30 minutes to 3 minutes. In the present embodiment, the length of the observation period T1 and the reference data acquisition period T2 is about 30 seconds to 1 minute.

  Here, the magnitude of the breathing movement of the person 2 is, for example, the amplitude of the breathing data (see FIG. 2A) within a certain period (for example, 5 to 15 seconds) including a period of at least one cycle. A peak value, a bottom value, an amount corresponding to a tidal volume, and the like can be used. Here, the peak is the peak portion of the waveform pattern formed by the measurement data, and the bottom is the valley portion (see FIG. 2A). Here, the amplitude is the difference between the peak and the bottom.

  In the present embodiment, the magnitude of the breathing motion of the person 2 uses an amount corresponding to the tidal volume of the person 2, that is, a so-called quasi-tidal volume. The quasi-tidal volume is a value obtained by integrating the measurement data from zero cross to zero cross, here respiration data (Fig. 2 (a)). However, the area is ignored as it does not change.) Zero cross means that the value of periodic movement also becomes zero. For example, as shown in FIG. 2A, the horizontal axis is time, the vertical axis is speed, and the horizontal axis crosses the vertical axis at speed 0. , The speed intersects the time axis, or the intersected point. That is, the point where the speed becomes zero or zero. Here, “from zero cross to zero cross” means a period in which measurement data has a predetermined positive or negative sign between two consecutive zero crosses. The quasi-tidal volume is not a strict tidal volume but is a value corresponding to the tidal volume, so it is described as “quasi”.

  That is, the 1st state discrimination | determination part 24 calculates the quasi-tidal volume obtained by integrating the respiration data (FIG. 2 (a)) from a zero cross to a zero cross as a magnitude | size of the respiration motion of the person 2. Configured as follows.

  By using the quasi-tidal volume as the magnitude of the breathing movement of the person 2, changes in both the amplitude and interval of the breathing data can be reflected. That is, if the amplitude becomes smaller and the interval becomes shorter, the quasi-tidal volume becomes smaller, and it can be said that the change in the magnitude of the respiration movement is reflected more accurately than when only the amplitude is used.

  FIG. 4 is a diagram showing an example of the distribution of data related to the quasi-tidal volume used in the respiratory monitor 1 according to the embodiment of the present invention. FIG. 4A shows a histogram, an average value, and a standard deviation approximately. An equal normal distribution probability density curve, (b) shows a cumulative distribution curve. By dividing each frequency by the total frequency in the histogram, a relative frequency of each class (class), that is, a probability distribution can be obtained. Similarly, by dividing the cumulative frequency distribution by the total frequency, a cumulative relative frequency distribution, that is, a cumulative distribution can be obtained. Here, the probability distribution typically indicates the correspondence between a certain event and the probability that the event occurs for all the events that can occur. The probability distribution and cumulative distribution obtained from the measured values are discontinuous because the number of data is limited. When obtaining the determination threshold value described later using these, if you want a finer or continuous value, fit the probability distribution of the measured value to a normal distribution in which the mean and standard deviation are approximately equal, and calculate the cumulative distribution curve. Obtain or use the cumulative distribution curve.

  The histogram is the factor and characteristic data that can be quantified. The horizontal axis is the characteristic value, here the magnitude of the movement of breathing of the person 2, and the range in which the data exists is classified into several classes (classes). In this class, columns (rectangles) having an area proportional to the frequency of data included in the class are arranged with the width of the class as the base. In the histogram of FIG. 4A, the horizontal axis represents class (class), the vertical axis represents frequency (right side), and probability density of normal distribution (left side). In this figure, the bar graph shows the frequency distribution, and the solid line shows the normal distribution.

  The class (class) corresponds to, for example, the magnitude of the output of the measurement data (FIG. 2 (a)). In this embodiment, the magnitude of the movement of the person 2 breathing, that is, quasi-one time. This value corresponds to the ventilation volume. In the figure, the classes are set at equal intervals based on the data distribution. The class width may be divided into N from 0 to the average value + standard deviation × 2 based on the average value and standard deviation of all measurement data within a certain period. Here, N may be determined based on the total number of data. For example, it is usually 10 to several tens. Alternatively, it may be possible to divide 50 times by 4 times the frequent value obtained by the provisionally set class width. The class width can also be appropriately determined from the number of data in a certain period, the pre-measured overnight (about 7 to 10 hours) data distribution range, variation, and the like.

  The relative frequency is obtained by dividing the frequency of each class (class) by the total frequency, and the relative frequency distribution corresponds to the probability distribution of each class. The cumulative relative frequency is the cumulative relative frequency, and this distribution curve corresponds to the cumulative distribution function. The cumulative frequency is a frequency obtained by accumulating the frequencies. Here, the frequency is equal to or less than a predetermined class (class). In the cumulative relative frequency distribution diagram of FIG. 4B, the horizontal axis represents the class (class) and the vertical axis represents the occurrence probability (relative frequency) of the class (class). As the cumulative relative frequency distribution diagram, the relative frequency distribution itself may be used, or a complementing method may be further used as described above. A normal distribution may be assumed from the average value and standard deviation of the data. In this figure, the plotted relative frequency distribution is plotted with dots, and the normal distribution is plotted with solid lines. For example, when the cumulative relative frequency distribution is used, the probability of occurrence of a class (class) of “5” or less is about 0.6 × 100 = 60%.

  As described above, the first state determination unit 24 is based on the probability distribution of the data related to the quasi-tidal volume in the reference data acquisition period T2 (see FIG. 3), and the quasi-unique of the observation period T1 (see FIG. 3). Regarding the tidal volume, the predetermined range in which the occurrence probability of the distribution state in the predetermined range obtained from the distribution is less than or equal to the second probability is estimated.

  In the case of a patient whose respiratory muscles have weakened, during the artificial respiration, a large amount of breathing is often mixed as a fluctuation of each time in the fluctuation of the average ventilation amount. On the other hand, in the case of spontaneous breathing, it is considered that large breathing cannot be performed, and the maximum value of the ventilation volume is reduced as the average ventilation volume is lowered. Therefore, in the present embodiment, it is preferable to use the probability that the maximum value of the quasi-tidal volume during the period corresponding to the preset detection time falls below a certain level for the determination by the first state determination unit 24. Therefore, this is used.

  First, the first state determination unit 24 sets an observation period T1 (see FIG. 3) on the past side from the determination target time point, and further has a length equivalent to the observation period T1 from the start point of the observation period T1 to the past side. Is taken as a reference data acquisition period T2 (see FIG. 3). Furthermore, the first state determination unit 24 determines whether the state in the reference data acquisition period T2 is the observation period T1 based on the probability distribution (see FIG. 4) of the data related to the quasi-tidal volume in the reference data acquisition period T2. When it is assumed that it has continued, the determination threshold is determined so that the probability that the maximum value of the quasi-tidal volume during the observation period T1 is equal to or less than the determination threshold is equal to or less than the second probability assumed in advance. In other words, the first state determination unit 24 performs quasi-one time in the observation period T1 based on the probability distribution of the data regarding the quasi-tidal volume in the reference data acquisition period T2 (see FIG. 3) and the second probability. The threshold value for the maximum value of ventilation is calculated.

  The second probability is typically a probability that the maximum value of the quasi-tidal volume within the observation period T1 does not exceed the determination threshold. In other words, the determination threshold is set such that the second probability is a probability that the maximum value of the quasi-tidal volume within the observation period T1 does not exceed the determination threshold. As the second probability, for example, an arbitrary probability derived from a medical point of view or a false alarm frequency targeted by the respiratory monitor 1 may be used. In this embodiment, the false alarm frequency targeted by the respiratory monitor 1 is used. I will do it. Hereinafter, unless otherwise specified, the second probability will be described as a target false alarm frequency.

Specifically, the determination threshold value can be calculated based on the following equation (1). That is, the length of the observation period T1 and the reference data acquisition period T2 is set to t ₀ seconds, the respiration rate is set to n _v / min, and the target false alarm frequency is set to once per _te seconds, and within the reference data acquisition period T2 Let P _t be the probability that the quasi-tidal volume for one stroke is less than or equal to the determination threshold. If the quasi-tidal volume shall require at each exhalation → intake and intake → expiration, the number of data of the quasi-tidal volume in the observation period T1 _{(n v · t 0/60} ) · 2 = n v · Since t _0/30 , the following equation (1) can be obtained.
The left side represents the probability that the quasi-tidal volume below the judgment threshold will continue for the observation period T1, and the right side represents the target value of the false alarm frequency (the reciprocal of the number of quasi-tidal volume data during the average false alarm interval). To express.

Determination threshold can be determined based on (1) quasi-tidal volume probability distribution of the data relating to the and P _t obtained reference data acquisition period T2 from equation (see FIG. 4). For example, respiratory rate _{n v} / min = 20 times / min, once the false alarm frequency of the target 30 days _{(t e} s = 2592000 sec), i.e., at 1/2592000, the observation period T1, the reference data acquisition period T2 Is set to t ₀ seconds = 30 seconds, the probability P _t ≈0.488. For example, if P _t ≈0.488, using the cumulative relative frequency distribution diagram of FIG. 4B, the corresponding class is about “4.8”, and the determination threshold is “ 5 ”. Therefore, if the quasi-tidal volume class (class) that is the maximum value in the actual observation period T1 is “5” or less, the probability distribution of the data related to the quasi-tidal volume in the actual observation period T1 is the standard. The occurrence probability of the distribution state of the data in the observation period T1 estimated from the probability distribution in the data acquisition period T2 is included in the distribution state in a predetermined range that is equal to or lower than the target false alarm frequency.

That is, by substituting the target false alarm frequency into the equation (1), the probability P _t that the quasi-tidal volume for one time is equal to or less than the determination threshold value within the reference data acquisition period T2 is calculated, and the calculated probability P _The determination threshold is calculated from the probability distribution of the data related to the quasi-tidal volume in _t and the reference data acquisition period T2, based on the probability distribution of the data related to the quasi-tidal volume in the reference data acquisition period T2. Regarding the quasi-tidal volume of T1, the predetermined range of the data distribution state is estimated such that the occurrence probability of the distribution state of the predetermined range obtained from the distribution is equal to or less than the target false alarm frequency. The range below the determination threshold is the predetermined range of the data distribution state where the occurrence probability is below the target false alarm frequency.

  The first state determination unit 24 compares the maximum value of the quasi-tidal volume within the actual observation period T1 with the determination threshold value calculated from the data of the corresponding reference data acquisition period T2, and the maximum value is If the determination threshold value is exceeded, it is determined that the person 2 is abnormal. That is, comparing the maximum value of the quasi-tidal volume within the actual observation period T1 and the determination threshold value indicates that the distribution state of data regarding the quasi-tidal volume during the actual observation period T1 is as described above. It is a judgment whether it is included in the estimated predetermined range.

  Specifically, the fact that the distribution state of the data in the actual observation period T1 is included in the predetermined range of the estimated distribution state is a distribution in which the probability of occurrence is less than the target false alarm frequency, that is, as described above. For example, the class (class) of the maximum value of the quasi-tidal volume within the actual observation period T1 is included in the distribution range of class (class) = “5” or less. That is, referring to FIG. 4B, the probability distribution of the actual observation period T1 is in a state where it is confined on the left side in the figure with class (class) = “5” as a boundary. After all, paying attention to the maximum value of the quasi-tidal volume in the observation period T1, if the maximum value is equal to or less than the determination threshold, the distribution state of the data regarding the quasi-tidal volume in the actual observation period T1 is the occurrence probability. Is included in a distribution state of a predetermined range of distributions such that is less than or equal to the target false alarm frequency.

  Therefore, when the maximum value of the quasi-tidal volume within the observation period T1 falls below the threshold, the first state determination unit 24 stores the data regarding the quasi-tidal volume during the determination period at the observation period T1. Since the distribution state is a distribution range in which the probability of occurrence of the distribution state is a unique probability that is less likely to occur than a preset target false alarm frequency, it can be determined that the person 2 is in an abnormal state.

The first state determination unit 24 _{obtains a} determination threshold value from the probability P _t calculated from the above-described equation (1), and when performing abnormality determination, the first state determination unit 24 applies to a patient whose spontaneous breathing ability is low and respiratory depression is large. When the observation period T1 and the reference data acquisition period T2 are shortened with emphasis on early detection, the probability _Pt becomes small and the determination threshold becomes a relatively low value. On the other hand, in the case of a patient who has a high ability of spontaneous breathing or a symptom of sleep disordered breathing accompanied by a long periodic respiratory decline, the probability P _t becomes 1 when the observation period T1 and the reference data acquisition period T2 are long. Accordingly, the determination threshold approaches the peak value of the quasi-tidal volume during the observation period T1, so even a slight decrease in quasi-tidal volume can be detected as abnormal if it continues.

For example, as discussed above, respiration rate _{n v} / min = 20 times / min, once the false alarm frequency of the target 30 days _{(t e} s = 2592000 sec), i.e., at 1/2592000, the observation period T1, When the length of the reference data acquisition period T2 is t ₀ seconds = 30 seconds, the probability P _t ≈0.488. On the other hand, when the length of the observation period T1 and the reference data acquisition period T2 is t ₀ seconds = 240 seconds, P _t ≈0.914. This means that even if the length of the observation period T1 and the reference data acquisition period T2 is t ₀ seconds = 30 seconds, the threshold is It shows that it is determined to be abnormal when breathing below the threshold value is almost close to the average value so far and continues for 30 seconds. Also, the observation period T1, when the length of the reference data acquisition period T2 was set to t ₀ seconds = 240 seconds, the threshold approaches the peak of the far, if it continues 240 seconds respiratory depression is even slightly, as abnormal It can be detected. Thereby, it becomes possible to perform the determination by the highest threshold value according to the length of the observation period T1, the reference data acquisition period T2 to t _0. Moreover, in the case of a patient who causes periodic respiratory decline or respiratory stop such as symptoms of sleep breathing disorder, it is possible to avoid false alarms by setting the observation period T1 longer than this period.

FIG. 5 is a diagram showing a first specific example of the transition of the measurement data used in the respiratory monitor 1 according to the embodiment of the present invention and the maximum value of the quasi-tidal volume, and (a) is the measurement data. (B), (c) shows the transition of the maximum value of the quasi-tidal volume. In FIG. 5 (a), the upper part is respiration data (Respiratory movement, see FIG. 2 (a)) as measurement data, and the lower part is body movement data (Body movement, see FIG. 2 (c)) as measurement data. 5 (b) and 5 (c) show the transition of the quasi-tidal volume corresponding to the measurement data of FIG. 5 (a). In this figure, the dark solid line indicates the observation period. Transition of the maximum value (evaluation value; Evaluation value) of the quasi-tidal volume within T1, and the thin solid line indicates the transition of the determination threshold (Threshold). The difference between (b) and (c) is that the length t ₀ of the observation period T1 and the reference data acquisition period T2 is different, as will be described later.

  The maximum value and determination threshold value of the quasi-tidal volume in the observation period T1 shown in FIGS. 5B and 5C are plotted at the end of the observation period T1 and the reference data acquisition period T2, respectively. The state determination unit 24 determines whether or not the maximum value at the determination target time point is equal to or less than the determination threshold value by comparing with the determination threshold value at the past time point by the length of the observation period T1.

The first specific example shown in FIG. 5 is an example of patient breathing with periodic apnea due to sleep breathing disorder or the like, as is apparent from the breathing data shown in FIG. In (b), the length of the observation period T1 and the reference data acquisition period T2 is set to t ₀ = 60 seconds. In this case, the maximum value of the quasi-tidal volume within the observation period T1 at the determination target time point indicated by the arrow in the figure is below the determination threshold value. Therefore, the first state determination unit 24 determines that the person 2 is in an abnormal state at that time. On the other hand, in (c), the length t _{0 of} the observation period T1 and the reference data acquisition period T2 is set to 90 seconds. In this case, the maximum value of the quasi-tidal volume within the observation period T1 at the determination target time point indicated by the arrow in the figure exceeds the threshold value. Therefore, the first state determination unit 24 does not determine that the person 2 is in an abnormal state at that time. In other words, it is not an erroneous judgment.

  Here, for example, when the ventilator is removed and sufficient air is not sent to the patient, the patient with spontaneous breathing starts spontaneous breathing, but the spontaneous breathing is generally weak, so the respiratory rate tends to increase. There is. That is, the respiratory cycle at the determination target time tends to be short. Therefore, as described above, the first state determination unit 24 is configured such that the maximum value of the quasi-tidal volume within the observation period T falls below the determination threshold, and in addition, the respiratory motion cycle at the determination target time point, for example, The person 2 may be determined to be abnormal when the breathing interval changes.

  The respiration cycle (respiration interval) at the determination target time point may be calculated from the respiration data (see FIG. 2A) for the sixth predetermined period immediately before the determination target time point. In addition, instead of the breathing interval, the person 2 may be determined to be abnormal when the reciprocal of the breathing interval, that is, the breathing rate (breathing rate) fluctuates instead of the breathing interval. Hereinafter, unless otherwise specified, a sixth predetermined period that is a period for calculating a respiratory cycle is referred to as a respiratory cycle calculating period T6.

Respiratory cycle calculation period T6 typically may be a period including at least normal breathing one period, for example, or equal to ₀ seconds to 5～T. Here, the respiratory cycle calculation period T6 is about 60 seconds. Incidentally, the range of normal breathing for adults is about 2.4 to 6 seconds for the breathing cycle (breathing interval), and about 10 to 25 times per minute for the breathing rate (breathing rate). is there.

  The first state determination unit 24 has a breathing cycle (breathing interval) at the determination target time point that is, for example, about ± 30% or more with respect to the breathing cycle (breathing interval) at the previous determination target time point. Specifically, it is configured to determine that the respiratory cycle has fluctuated when there is a deviation of about ± 20% or more. In particular, only when the breathing interval is shortened (when the respiratory rate is increased) may be set as the condition for determining abnormality. Further, as the period of the determination target time point, an average value of the respiration cycle obtained for each determination target time point in the observation period T1 may be used.

  In this case, the first state determination unit 24 determines that the maximum value of the quasi-tidal volume within the observation period T has fallen below the determination threshold, and further changes the respiration cycle (respiration interval) at the determination target time point. In such a case, it is determined that the person 2 is abnormal, and if there is no change in the cycle, it becomes evidence that the artificial respiration is normally performed. Even if only fluctuates, it can be determined that no abnormality in artificial respiration has occurred. As a result, when it is difficult to determine abnormalities in breathing only by whether or not the maximum value of the quasi-tidal volume within the observation period T falls below the determination threshold, for example, normal artificial respiration is performed. Nevertheless, erroneous discrimination can be prevented when the magnitude of breathing may decrease. In addition, periodic respiratory decline or respiratory stop due to sleep disordered breathing is not accompanied by an increase in the respiratory rate in many cases, so when monitoring a patient with a long-period respiratory decline, the observation period T1 is set to Even if it is set to be shorter than the cycle, it is possible to determine spontaneous breathing, that is, decrease in respiration, and it is possible to more quickly determine abnormality.

  In the present embodiment, the first state discriminating unit 24 uses the observation period T1 and the reference data acquisition period T2 to indicate data indicating body movement detected by a body movement detection unit 28 (FIG. 2A). , (B)) is configured to be a period excluding the body movement period.

  FIG. 6 is a diagram illustrating a case where the body movement period overlaps the observation period T1 in the respiratory monitor 1 according to the embodiment of the present invention. As shown in FIG. 6A, when a body movement period detected by a body movement detection unit 28 described later and an observation period T1 overlap, the remaining measurement data excluding the measurement data of the body movement period are included. Then, measurement data for a period corresponding to the excluded period is added to obtain measurement data for the observation period T1. Specifically, for example, when the body movement period overlaps with the observation period T1, measurement data for a period corresponding to the excluded period is added from the measurement data on the past side of the observation period T1 (1 minute). This may be done (see FIG. 6B). Similarly, when the person 2 is not monitored in real time, or when there is a time lag between the acquisition of the measurement data and the analysis of the state by the first state determination unit 24, the body movement period overlaps the observation period T1 similarly. At this time, measurement data of a period corresponding to the excluded period may be added from the measurement data on the future side following the determination target time point of the observation period T1 (1 minute) (FIG. 6C). That is, it is possible to secure measurement data for one continuous minute (observation period T1) that does not include a body movement period. The same applies when the reference data acquisition period T2 and the body movement period overlap.

  By removing the body movement period from the observation period T1 and the reference data acquisition period T2, the first state determination unit 24 can exclude data when body movements other than breathing occur, and the influence of body movements Therefore, it is possible to determine the abnormality of breathing without receiving the error, and to prevent erroneous determination. Note that once the body movement is detected, the first state determination unit 24 does not determine the breathing state for a certain period (for example, 3 to 5 seconds) after the body movement is not detected until the body movement is settled. You may comprise as follows. In addition, when a long body movement of 5 seconds or more occurs, it is assumed that the sensitivity of the respiratory data may have changed, and the previous respiratory data is reset, and data accumulation in the observation period T1 is started again. Also good.

  In the above description, the maximum value of the semi-tidal volume and the determination threshold in the observation period T1 shown in FIGS. 5B and 5C are plotted at the end of the observation period T1 and the reference data acquisition period T2, respectively. Therefore, the first state determination unit 24 determines whether or not the maximum value at the determination target time is equal to or less than the determination threshold by comparing with the determination threshold at the past time by the length of the observation period T1. As described above, when there is a body movement period, the maximum value at the determination target time point is compared with the determination threshold value at the past time point by the length of the observation period T1 + body movement period. It will be. 5B and 5C, the body movement period (Invalid period by body movement) is indicated by a broken line.

  As described above, the first state determination unit 24 determines the person at the determination target time according to the probability distribution of the data related to the quasi-tidal volume during the reference data acquisition period T2 and the quasi-tidal volume during the observation period T1. By determining whether or not the state of 2 is abnormal, the present invention can safely determine the state of breathing without imposing a burden on the person 2 as much as possible. That is, the abnormality determination can be performed with a small number of false alarms without taking the data of the person 2 in a dangerous state. In addition, by setting a determination threshold according to the probability distribution of data related to the quasi-tidal volume during the reference data acquisition period T2 and the target false alarm frequency, depending on the situation such as symptoms of sleep disordered breathing peculiar to the person 2 Since a threshold value as high as possible can be set, it is possible to prevent detection errors while preventing false alarms. In addition, the determination based on the maximum value of quasi-tidal volume as described above makes it difficult for patients with neuromuscular disease, etc. to take a large breath when artificial ventilation ceases. This is preferable because the maximum value does not increase.

  In the above description, the first state determination unit 24 has been described as determining the state based on the probability that the maximum value of the quasi-tidal volume within the observation period T1 is taken. Estimated from the probability distribution of the data in the reference data acquisition period T2, such as the sum of the values and the data of the observation period T1, for example, the probability that the sum of all frequencies is less than a certain value, the product of the occurrence probability of each data in the observation period T1 The probability of data distribution in various observation periods T1 can be used.

  By the way, in the above description, by calculating the determination threshold, the quasi-tidal volume during the observation period T1 is obtained from the distribution based on the probability distribution of the data regarding the quasi-tidal volume during the reference data acquisition period T2. By estimating the predetermined range in which the occurrence probability of the distribution state of the predetermined range is equal to or less than the target false alarm frequency, and comparing the maximum value of the quasi-tidal volume within the actual observation period T1 with the determination threshold, Although it was determined whether or not the distribution state of the data related to the quasi-tidal volume during the actual observation period T1 falls within the estimated predetermined range, the abnormality of the person 2 was determined, but the determination was made without obtaining the determination threshold. May be.

  In other words, the first state determination unit 24 is determined based on the distribution of data related to the quasi-tidal volume during the actual observation period T1 based on the probability distribution of data related to the quasi-tidal volume during the reference data acquisition period T2. A first probability that the range distribution state occurs may be estimated, and the abnormality of the person 2 may be determined based on the first probability.

  Here, the predetermined range obtained from the distribution of data regarding the quasi-tidal volume during the actual observation period T1 is defined by the maximum value of the quasi-tidal volume within the actual observation period T1 as described above, for example. This is the range of the distribution state of the data to be processed.

  For example, when the cumulative relative frequency distribution diagram of FIG. 4B is used as the probability distribution of data related to the quasi-tidal volume during the reference data acquisition period T2, the maximum quasi-tidal volume within the actual observation period T1 is used. If the value class is “5”, the probability of occurrence of quasi-tidal volume that is equal to or less than the maximum value is about 0.6 × 100 = 60%. If all the quasi-tidal volumes within the observation period T1 are less than or equal to the maximum value, the distribution state of data regarding the quasi-tidal volume during the observation period T1 is a predetermined value that the maximum value is “5” or less. It becomes the distribution state of the data included in the distribution state of the range. Then, the probability that the distribution state of the predetermined range occurs, that is, the first probability can be obtained as the quasi-tidal volume that is equal to or less than the maximum value occurs independently for all frequencies within the observation period T1. From this, it is possible to calculate by multiplying the occurrence probability of quasi-tidal volume that is not more than the maximum value = 0.6 by the total frequency. For example, when the total frequency in the observation period T1 is 30 times, the first probability is about 0.0000000221, which is the 30th power of 0.6 corresponding to the class (class) = “5”. Thus, the 1st state discrimination | determination part 24 can estimate a 1st probability based on the probability distribution of the data regarding the quasi-tidal volume in reference | standard data acquisition period T2.

  That is, the first probability is estimated from the probability distribution of the data in the reference data acquisition period T2 when it is assumed that the distribution of data related to the quasi-tidal volume in the reference data acquisition period T2 continues in the observation period T1. The distribution of data related to the actual quasi-tidal volume within the observation period T1 within a predetermined range obtained from the distribution of data related to the actual quasi-tidal volume within the observation period T1. The probability of being included in the state.

  The first state determination unit 24 compares the calculated first probability with the target false alarm frequency, and when the first probability falls below the target false alarm frequency, the first probability is determined as the target. It is possible to determine that the person 2 is abnormal because it has a unique probability that is less likely to occur than the false alarm frequency.

  Here, the first probability is a probability estimated based on the probability distribution of data related to the quasi-tidal volume during the reference data acquisition period T2, and is the actual quasi-tidal ventilation within the observation period T1. The distribution state of the data related to the amount has been described as the probability of being included in the predetermined range of the distribution state of the data obtained from the maximum value of the quasi-tidal volume within the actual observation period T1, for example, the average value, the minimum value Alternatively, the probability may be a probability distribution included in the range of the probability distribution of the data obtained from the median (Median) and the mode (Mode).

  In the above description, based on the probability distribution of the data related to the quasi-tidal volume during the reference data acquisition period T2 (for example, 30 seconds), the distribution regarding the quasi-tidal volume during the observation period T1 (for example, 30 seconds) is derived from the distribution. In contrast to estimating a predetermined range (for example, a class = “5” or lower range) in which the occurrence probability of the distribution state of the predetermined range to be obtained is equal to or lower than a target false alarm frequency (for example, 1/259200), Here, the first probability that a distribution state in a predetermined range that is obtained from the maximum value of the quasi-tidal volume data in the actual observation period T1 in the observation period T1 is estimated. However, the abnormality of the person 2 is actually determined according to whether or not the maximum value of the quasi-tidal volume within the actual observation period T1 is equal to or less than a certain value. As for the quasi-tidal volume during the observation period T1, a predetermined range is estimated such that the occurrence probability of the distribution state within the predetermined range obtained from the distribution is less than or equal to the target false alarm frequency, and the quasi-tidal volume during the actual observation period T1 is estimated. This is equivalent to determining whether or not the distribution state of the data related to the tidal volume falls within a predetermined range of the estimated distribution state.

  Similarly, the first state discriminating unit 24 substitutes the target false alarm frequency into the formula (1), and performs a single batch when the occurrence probability of the data distribution state in the predetermined range is equal to or less than the target false alarm frequency. The occurrence probability of the quasi-tidal volume range is calculated, and the maximum value of the quasi-tidal volume in the observation period T1 is actually based on the probability distribution of the data regarding the quasi-tidal volume in the reference data acquisition period T2. The probability of being less than or equal to the maximum value of the quasi-tidal volume within the measured observation period T1 may be calculated, and the occurrence probability may be compared with each other to determine the abnormality of the person 2. However, in this case as well, the abnormality of the person 2 is determined according to whether or not the maximum value of the quasi-tidal volume within the actual observation period T1 is below a certain value.

  Reference is again made to FIG. As described above, the second state determination unit 25 determines whether or not the state of the person 2 at the determination target time point is abnormal according to the comparison result with the reference value of the value based on the measurement data of the third predetermined period. Configured to discriminate. Furthermore, in the present embodiment, the second state determination unit 25 is configured to determine the abnormality of the person 2 based on the comparison result of the spectrum comparison unit 27 as described above.

  As described above, the spectrum calculation unit 26 calculates the spectrum for the third predetermined period based on the measurement data indicating the state of the person 2 with the movement of breathing, here, the breathing data (FIG. 2A). . Here, the spectrum may be an amplitude spectrum or a power spectrum. In the present embodiment, the spectrum uses a power spectrum corresponding to the sum of squares of the real part and the imaginary part of the spectrum. Since the frequency distribution of the power spectrum is emphasized more than the amplitude spectrum, it is suitable for determining an abnormality of the person 2 by comparing the low frequency component and the high frequency component of the spectrum.

  Specifically, the spectrum calculation unit 26 performs discrete Fourier transform on the respiration data (FIG. 2A) for the third predetermined period immediately before the determination target time point, typically FFT (Fast Fourier Transform, Fast Fourier Transform). The power spectrum at the determination target time is calculated by conversion.

  Further, the third predetermined period is a time for accumulating respiration data (FIG. 2A) for executing FFT, for example, a period including at least one cycle before the determination target time point, for example, 5 to 60 seconds, preferably 5 to 32 seconds, and here, 8 seconds immediately before the determination target time point. Hereinafter, unless otherwise specified, a third predetermined period, which is a time for accumulating respiratory data (FIG. 2A), is referred to as a data accumulation time T3.

  FIG. 7 is a diagram illustrating an example of a power spectrum calculated by the spectrum calculation unit 26 of the respiratory monitor 1 according to the present embodiment. When there is actually a normal respiratory motion, the power spectrum of a frequency in the range close to the normal respiratory rate is increased, and when the normal respiratory motion is lost, the power spectrum is decreased. On the other hand, the change in the power spectrum of the frequency that is not in the respiratory motion, that is, the frequency in the noise range is small regardless of the presence or absence of normal respiratory motion. Here, the frequency in the range close to the normal respiration rate is, for example, a frequency component of 10 to 50 times / minute, and the frequency in the range of other noise components is typically the normal respiration rate. It becomes a frequency component of a range higher than a near frequency component. Therefore, by comparing the low-frequency component and the high-frequency component of the power spectrum, it is possible to determine the abnormality of the object 2, that is, here, the presence or absence of normal breathing of the person 2, or a decrease to a level close to stopping. it can.

  Here, typically, the range of the low frequency component is 60 times / minute or less, and the range of the high frequency component is 60 times / minute or more. In the present embodiment, the range of the low frequency component is 10 as described above. -50 times / minute, and the range of the high frequency component is 80-120 times / minute. The range of the low frequency component and the range of the high frequency component may partially overlap. For example, the range of the low frequency component is 10 to 70 times / minute, and the range of the high frequency component is 60 to 120 times. / Min.

  Specifically, the spectrum comparison unit 27 calculates the sum of the power spectra of the low frequency components (hereinafter referred to as “signal components” unless otherwise specified) and the sum of the power spectra of the high frequency components (hereinafter, unless otherwise specified). (Referred to as “noise component”). The sum of the power spectrum of each component may be simply added up from the power spectrum of each component or may be calculated by integrating the power spectrum of each component with respect to the frequency. The spectrum comparison unit 27 compares the calculated signal component with the noise component. The spectrum comparison unit 27 transmits a signal of the comparison result to the display 40 and displays the comparison result on the display 40.

  FIG. 8 shows a predetermined time (about 6 minutes) of the waveform pattern of the respiratory data acquired by the actual measurement of the respiratory monitor 1 according to the present embodiment, the signal component compared by the spectrum comparison unit 27, and the noise component data. This is an example.

  When the signal component falls below the noise component for a fourth predetermined period based on the comparison result between the signal component compared by the spectrum comparison unit 27 and the noise component, the second state determination unit 25 The person 2 is abnormal. Here, the person 2 is configured to determine that the breathing has stopped.

  That is, here, the sum of the power spectra of the low frequency components obtained by performing FFT on the respiration data (FIG. 2A) of the data accumulation time T3, that is, the signal component is a value based on the measurement data of the data accumulation time T3. The sum of the power spectrum of the high frequency component, that is, the noise component is a reference value for comparison. That is, the second state determination unit 25 determines whether or not the state of the person 2 at the determination target time is abnormal based on whether or not the signal component falls below the noise component. In other words, the second state determination unit 25 determines whether the signal component as data regarding the magnitude of the periodic movement at the determination target time point is less than the noise component as the minimum threshold value. Thus, it is determined whether or not the state of the person 2 at the determination target time is abnormal.

  Here, the fourth predetermined period is a period sufficient to evaluate the stoppage of breathing. Typically, the period includes at least one cycle before the determination target time, for example, 5 to 32 seconds, preferably Is from 5 to 16 seconds, here 8 seconds. Hereinafter, unless otherwise specified, a fourth predetermined period, which is a period for evaluating and discriminating an abnormality of the person 2, is referred to as a discrimination evaluation period T4. Here, the term “discrimination evaluation period T4 continuously falling” does not necessarily mean that the condition must not be deviated from the condition, but it may be substantially continuous. If there is no influence, it is good. The same applies to the following description unless otherwise specified.

  As described above, the second state discriminating unit 25 discriminates the stop of breathing based on the relative comparison result between the signal component and the noise component without using one fixed threshold value, for example. Even when the detection sensitivity and noise level of measurement data acquired by the FG sensor 10 to be described later change due to environmental conditions such as the posture of the person 2, the situation of the top cover, the situation of ambient light, etc., the change is appropriately handled. More accurate discrimination can be made. In addition, since the second state determination unit 25 performs the determination based on the relative comparison result between the signal component and the noise component, for example, when the artificial respiration circuit is disconnected at the time of the posture change of the person 2 or removed at the time of care If the person 2 forgets or the posture of the person 2 changes due to body movement such as turning over, it is not necessary to set a threshold again over a certain amount of time, and the respiratory stop of the person 2 can be detected quickly. .

  Furthermore, the respiratory monitor 1 according to the present embodiment combines the first state determination unit 24 and the second state determination unit 25, so that the first state determination unit 24 or the second state determination unit 25 Since either one can detect the respiratory abnormality of the person 2, the respiratory abnormality can be detected, so that a comprehensive and leak-free determination can be made. The respiratory monitor 1 may be configured to detect a respiratory abnormality only when both the first state determination unit 24 and the second state determination unit 25 determine a respiratory abnormality of the person 2. Good. In this case, false alarms can be reduced.

  In the above description, the second state determination unit 25 determines that the respiration of the person 2 is abnormal when the signal component continuously falls below the noise component for the determination evaluation period T4. In addition to the method of simply comparing the size of the component and the noise component, various comparison methods such as using a difference or a ratio can be selected. The relative relationship between the signal component and the noise component may differ depending on how to select the range of the low frequency component and the range of the high frequency component of the power spectrum. Therefore, for example, depending on how to select the respective ranges, by applying a bias or applying a coefficient to one or both of the signals at the time of comparison, before the signal component falls below the noise component, the person 2 It can be configured to discriminate abnormalities in breathing.

  In the above description, the data accumulation time T3 for calculating the power spectrum from the respiratory data by discrete Fourier transform is assumed to be about 8 seconds. As shown in FIG. 7, when a power spectrum is obtained by sampling respiratory data for 8 seconds, the power spectrum can be obtained with a respiration rate resolution of about 7.5 times / minute. If you want to know more precise breathing rate, it is necessary to take a long sampling time of data, and with such a short sampling time, you can not know the precise precise breathing rate, but here the rough high frequency component and low frequency component Since it is sufficient to know the amount, it is possible to sufficiently determine respiration abnormality with data obtained by short-time sampling. Therefore, as a result, it is possible to more quickly determine abnormalities in breathing. In the embodiment described above, it is possible to determine whether or not to stop breathing in about 16 seconds in total for about 8 seconds as the data accumulation time T3 and about 8 seconds as the discrimination evaluation period T4.

  The second state discriminating unit 25 determines whether the average of the fifth predetermined period of the sum of the low-frequency component spectra falls below the average of the fifth predetermined period of the sum of the high-frequency component spectra. You may comprise so that it may discriminate | determine that the person 2 is abnormal. The fifth predetermined period only needs to include a plurality of past determination target time points. For example, the fifth predetermined period is 5 to 30 seconds, preferably 5 to 15 seconds, typically 8 seconds, similarly to the discrimination evaluation period T4. . More preferably, it is a time that does not interfere with real-time monitoring of the person 2 by the respiratory monitor 1. Hereinafter, unless otherwise specified, the fifth predetermined period, which is a period for taking the average value of the sum of the spectra, is referred to as a spectrum averaging period T5.

  That is, in this case, the spectrum comparison unit 27 calculates the signal component and the noise component at the determination target time point, and further uses the signal component and the noise component within the spectrum averaging period T5 immediately before the determination target time point to calculate the respective averages. Calculate the value. The signal component and noise component in the spectrum averaging period T5 immediately before the determination target time point are the signal component and noise component calculated at the past determination target time point. The spectrum comparison unit 27 compares the calculated average value of the signal components with the average value of the noise components.

  By doing so, the second state discriminating unit 25 shortens the discriminant evaluation period T4 described above or sets the discriminant evaluation period T4 in an extreme case, depending on the length of the spectrum averaging period T5. It can be configured to determine that the person 2 is abnormal without waiting for the elapse of the discrimination evaluation period T4 when the average value of the signal component falls below the average value of the noise component.

  Moreover, the data (refer FIG. 2) which show the body movement mentioned above appear in the part enclosed with the broken line in the figure of FIG. For example, when there is body movement due to body posture change or nursing care, the noise component may increase as shown by the portion surrounded by a broken line in the figure. At this time, since the noise component may exceed the signal component, it may be erroneously determined that breathing has stopped. Therefore, the second state determination unit 25 determines that the movement at the determination target time point is the body movement by the body movement detection unit 28 (see FIG. 1) described later, that is, the body movement described later. If it is a period, it may not be determined whether to stop breathing. Thereby, erroneous determination can be prevented. At that time, once body movement is detected, it may not be determined whether or not to stop breathing for a certain period (for example, 3 to 5 seconds) after the body movement is not detected until it is settled. Further, the data accumulation time T3, the discrimination evaluation period T4, the spectrum averaging period T5, and the like may be set to a period excluding the body movement period, similarly to the observation period T1 and the reference data acquisition period T2.

  Also here, as in the case of the determination by the first state determination unit 24, if the person 2 is a patient having a respiratory abnormality not caused by artificial respiration, such as sleep apnea, the respiratory abnormality The discriminant evaluation period T4 may be longer than the longest apnea time of the patient so as not to erroneously discriminate the person 2 from stopping breathing. That is, the discriminant evaluation period T4 may be arbitrarily adjusted according to the characteristics of the target object 2 by operating the input device 35 (see FIG. 1). In addition, even if the period during which the signal component is below the noise component continues for the determination evaluation period T4, if the continuous period is shorter than the longest apnea time, the determination by the second state determination unit 25 is not performed. You may do it. Thereby, similarly, the determination error by the second state determination unit 25 can be prevented. In this case, the above-described spectrum averaging period T5 is also preferably slightly longer than the longest apnea time.

  In the above description, the second state determination unit 25 uses the signal component of the power spectrum as a value based on the measurement data of the data accumulation time T3, and based on whether the signal component falls below the noise component, That is, although it has been described that it is determined whether or not the state of the person 2 at the determination target time is abnormal according to the comparison result of the signal component with the noise component, the reference value of the value based on the measurement data of the data accumulation time T3 and Another configuration may be used as long as it determines whether or not the state of the object at the determination target time point is abnormal according to the comparison result. For example, in the simplest case, the second state determination unit 25 uses the quasi-tidal volume as a value based on the measurement data, sets a fixed minimum threshold for the quasi-tidal volume, and sets the reference value In addition, it may be configured to determine whether or not the state of the person 2 is abnormal based on whether or not the quasi-tidal volume at the determination target time falls below the threshold value. In other words, it may be configured to determine whether or not the state of the person 2 at the determination target time point is abnormal according to the minimum value of the quasi-tidal volume. Also, the difference between the signal component and the noise component is used as a value based on the measurement data, a minimum threshold is provided for the difference, and the difference between the signal component and the noise component falls below the threshold as a reference value. Based on the above, it may be configured to determine whether or not the state of the person 2 is abnormal.

  Refer to FIG. 1 again. As described above, the body motion detection unit 28 is based on the measurement data indicating the state of the object having a periodic motion, that is, the person 2 having the respiratory motion, and the non-periodic motion that occurs with the respiratory motion, that is, the body motion. And detecting a body movement period which is a period in which data indicating the body movement of the object exists from the measurement data.

  In the present embodiment, the body motion detecting unit 28 is based on the distribution status of measurement data within the seventh predetermined period immediately before the determination target time point, here, the body motion data (see FIG. 2C). A reference value is calculated. Hereinafter, unless otherwise specified, a seventh predetermined period that is a period for calculating the body movement reference value is referred to as a body movement reference value calculation period T7. The body movement reference value calculation period T7 is a period for calculating the body movement reference value, and may be, for example, about 1 to 2 minutes immediately before the determination target time point.

  Here, the distribution state of the body motion data is calculated by, for example, the average value of the body motion data (measured value) in the body motion reference value calculation period T7 + standard deviation × a, and this is used as the body motion reference value. Here, a is a constant. If this a is 3, for example, and the data has a Gaussian distribution, 99.85% of the body movement data (measured value) falls within the range of values calculated by this equation. It can be determined that the body motion is not a normal distribution. That is, when the body motion data (measured value) at the determination target time exceeds the body motion reference value calculated as described above, the body motion detection unit 28 determines that the motion at the determination target time is a body motion. judge.

  When the body motion detection unit 28 determines that the motion of the person 2 at the determination target time point is a body motion, the body motion detection unit 28 further determines a body motion period that is a period in which data indicating the body motion of the person 2 exists from the measurement data. Configured to detect. The body movement period may be a period in which it is determined that there is actually body movement. However, as described above, measurement data (for example, respiratory data) becomes somewhat unstable for several seconds before and after the period in which body movement is detected. Therefore, it is preferable to set a period obtained by adding several seconds before and after the period to the period in which it is determined that there is actually body movement as the body movement period. Note that, as described above, the body motion detection unit 28 detects whether or not the movement at the determination target time point is a body motion, in other words, determines whether or not the determination target time point is a body motion period. It is also a thing.

  In addition, if this work is carried out sequentially from the data of the determination target time points that change in real time, it is known that the previous determination target time point is a body movement, so it is known at the next determination target time point. It is preferable to exclude the time point, that is, the period showing body movement from the body movement reference value calculation period T7. That is, it is preferable that measurement data indicating body movement is not included in the subsequent calculation of the body movement reference value. By doing so, body movement can be detected more accurately. The body motion detection unit 28 determines that the body motion is detected when the body motion data (measured value) continuously exceeds the body motion reference value calculated as described above, for example, for about 1 to 5 seconds. You may comprise.

  Here, since the respiratory monitor 1 according to the present embodiment monitors the person 2 in real time, it is preferable that the body motion reference value used for the determination target time has already been calculated at the determination target time. In the present embodiment, as the body motion reference value actually used at the determination target time point, data in the body motion reference value calculation period T7 up to the previous time point (the determination target time point that goes back one point in the past) is used. The body motion reference value calculated in the above is used. That is, in other words, the body motion reference value used at the determination target time point is different from the body motion reference value calculated using the data within the body motion reference value calculation period T7 up to the determination target time point.

  The body motion detection unit 28 calculates a body motion determination value for determining the body motion of the person 2 at the determination target point based on measurement data (for example, body motion data) within the eighth predetermined period, The calculated body motion determination value may be compared with a body motion reference value that is a criterion for body motion determination, and the body motion of the person 2 may be determined based on the comparison result. Hereinafter, unless otherwise specified, an eighth predetermined period that is a period for calculating the body movement determination value is referred to as a body movement determination value calculation period T8.

  In this case, the body motion determination value calculation period T8 is within a time zone having a width sufficient to determine whether the movement of the person 2 is periodic or aperiodic. For example, the body motion determination value In the case where information entropy or CV value is used for the calculation of the value as will be described later, it may be set to about 5 to 10 seconds. Furthermore, the body motion determination value calculation period T8 is typically a device immediately before the determination target time point because the respiratory monitor 1 according to the present embodiment is a device that monitors the state transition of the person 2 in real time. The body movement determination value is a secondary parameter at each time point obtained from measurement data (for example, body movement data).

  Further, in this case, the body motion determination value may be an amount related to variation in measurement data (for example, body motion data) within the body motion determination value calculation period T8. The amount related to variation is, for example, information entropy or variation coefficient (CV value). First, the CV value can be calculated by “CV value = standard deviation / average value”, and has the meaning of normalizing the magnitude of the fluctuation with the bias level. Therefore, it does not react greatly to fluctuations in the bias level of the measurement data or slow changes compared to the calculation period, but reacts to sudden fluctuations that are large compared to the bias state.

Information entropy refers to the entropy used in physics as the uncertainty of an event, and if the decrease in uncertainty due to certain information is the amount of information, the relative value of uncertainty before and after receiving the information. It is. For example, when rolling a dice, the uncertainty or information entropy is maximal since it is not known at all what the eye came out before looking at the result. Upon receiving the information that an odd number of eyes have appeared, the information entropy decreases. If it is known that the first eye has come out, the result is uniquely determined and the information entropy is minimized. The amount of information is a monotonically decreasing function with respect to the probability. Knowing that an unusual event has occurred, the amount of information is large, but of course an unusual event rarely occurs. Each time you know that something unusual has happened, but it is not unusual, the total amount of information observed over time can be large. From this point of view, the average amount of information for a long time is information entropy. Specifically, the information entropy H (X) is calculated by the following equation (2), for example. Here, p (x) indicates the probability that the event x will occur in the set X of a plurality of events.

  Information entropy can be obtained from a histogram of measurement data. The histogram is, for example, as shown in FIG. In FIG. 9, the vertical axis represents frequency, and the horizontal axis represents class (class). The class corresponds to, for example, the magnitude of the output of measurement data, and is set at equal intervals based on the distribution of measurement data in the drawing. Specifically, the class width may be divided into N from 0 to the average value + standard deviation × 2 based on the average value and standard deviation of all measurement data. Here, N may be determined based on the total number of data. For example, it is usually 10 to several tens. Alternatively, it may be possible to divide 50 times by 4 times the frequent value obtained by the provisionally set class width. Here, the occurrence probability p (x) of x of a certain class = frequency of class / total number of data. In the rightmost class (N class) in the figure, since all data of N class or more are counted, the frequency is large.

  In this case, as shown in FIG. 9, when obtaining a histogram with the vertical axis representing the frequency and the horizontal axis representing the class (class), the class width (horizontal axis) is preferably a log scale histogram. As a result, the class width changes in proportion to the center value of the class, and information entropy that is invariant to fluctuations in the sensitivity of the signal (for example, measurement data) can be obtained. The width of the class of the histogram is obtained from the number of data in the body motion determination value calculation period T8, the distribution range of the body motion data in the overnight (about 7 to 10 hours), variation, and the like. be able to.

The body movement determination value may be calculated from the frequency distribution around the determination target time point. Here, the periphery of the determination target time is, for example, the body motion determination value calculation period T8 including or adjacent to the determination target time, and typically the body motion determination value calculation period immediately before the determination target time. T8. The frequency distribution is reflected in, for example, an output through a high-pass filter, a distribution of frequency components by Fourier transform, and an output distribution with respect to a scale by wavelet transform. The body motion determination value may be calculated based on the distribution of the magnitude (output value or the like) of the measurement data (for example, body motion data) thus extracted.

  In addition, the body motion reference value used as a reference when calculating and comparing the body motion determination value as described above is a single value as a reference value regardless of individual measurement data (for example, body motion data). The distribution of a plurality of body movement determination values for each determination target time point that changes in real time, or the body movement determination values for one night (about 7 to 10 hours) measured in advance. It may be determined from the distribution. Further, the body motion detection unit 28 is based on measurement data (for example, body motion data) within the body motion reference value calculation period T7 before the determination target time point, which is a body motion reference value serving as a reference for determining the body motion of the person 2. May be configured to compare the body motion determination value at the determination target time point with the body motion reference value, and determine the body motion of the person 2 based on the comparison result.

  The determination of body movement by the body movement detection unit 28 is performed by setting a body movement threshold value from the distribution of measurement data (for example, body movement data) in the body movement reference value calculation period T7 to obtain a body movement reference value. The determination may be made by comparing the movement threshold value with the body movement data at the determination target time point. Here, the body motion threshold value Thm (shown in FIG. 9) is, for example, the mode to the position where the frequency of the mode of the histogram in FIG. It is possible to determine a position obtained by adding a certain multiple (for example, three times) of the distance from the value to the mode value. In addition, since the right side of the peak of the histogram in the figure is affected by body movement, the ratio of the frequency to the peak may be evaluated on the left side.

  The respiratory monitor 1 according to the embodiment of the present invention is an alarm that issues an alarm when the person 2 is determined to be abnormal by the first state determination unit 24 or the second state determination unit 25. A device 36 may be provided. The alarm device 36 (see FIG. 1) has means for emitting an alarm sound such as a speaker, for example. When the person 2 is determined to be abnormal, the alarm device 36 (see FIG. 1) emits the alarm sound and informs a doctor, nurse, or the like. Notify 2 abnormalities. In this case, the first state determination unit 24 and the second state determination unit 25 transmit an alarm signal to the alarm device 36 (see FIG. 1) when determining that the breathing of the person 2 is abnormal. Configure. The alarm device 36 (see FIG. 1) is configured to emit an alarm sound when receiving an alarm signal. In this case, the first state determination unit 24 and the second state determination unit 25 are different from the first state determination unit 24 and the second state determination unit 25 even if the first state determination unit 24 and the second state determination unit 25 are not configured to generate an alarm signal. It is good also as a structure which produces | generates an alarm signal by the alarm means not shown of a body. That is, when the first state determination unit 24 and the second state determination unit 25 determine that the breathing of the person 2 is abnormal, the respiratory monitor 1 generates an alarm signal based on the determination of the abnormality. The alarm signal may be provided to the alarm device 36 (see FIG. 1). In FIG. 1, the alarm device 36 is illustrated as being externally attached, but may be provided internally.

  Further, the arithmetic unit 20 (see FIG. 1) may be configured to notify the occurrence of an alarm to the outside via an interface (not shown) when the alarm device 36 (see FIG. 1) is activated. . The notification is based on, for example, the intensity of light including voice, characters, symbols, and indoor lighting, or vibration. The interface (not shown) has a function of connecting to a communication line such as a general telephone line, an ISDN line, a PHS line, a mobile phone line, or a LAN.

  FIG. 10 is a schematic perspective view of the FG sensor 10 of the respiratory monitor 1 according to the embodiment of the present invention. With reference to this figure, the FG sensor 10 which is a measuring apparatus suitable for the respiration monitor 1 is demonstrated. The FG sensor 10 includes a projection device 11 that projects a predetermined illumination pattern 11a, in other words, a plurality of bright spots 11b, on the bed 3 as a target area, and light projected by the projection apparatus 11, that is, a plurality of bright spots 11b. Is configured to include an imaging device 12 that images the bed 3 on which the image is projected, and a measurement unit 14 that generates measurement data indicating the state of the person 2 based on an image captured by the imaging device 12. In the present embodiment, the measurement unit 14 is described as being configured integrally with the arithmetic device 20.

  FIG. 11 is a block diagram showing a schematic configuration of the FG sensor 10 of the respiratory monitor 1 according to the embodiment of the present invention. The measurement unit 14 includes a movement amount calculation unit 141 serving as a movement amount calculation unit that calculates a movement amount between the two frames of a plurality of bright spots from two frames of images acquired at two different times by the imaging device 12; A movement amount waveform generation unit 142 is provided as movement amount waveform generation means for generating movement amount waveform data in which movement amounts calculated by the movement amount calculation unit 141 are arranged in time series.

  Here, the measurement of the movement of the bright spot based on the images at two different time points will be described. The images at two different time points may be an arbitrary time point and a slightly previous time point. “Slightly before” only needs to be a time interval sufficient to detect the movement of the person 2. In this case, when a slight movement of the person 2 is desired to be detected, the time is short, for example, the movement of the person 2 does not become too large, and the time can be regarded as substantially no movement, for example, about 0.1 seconds. . Or it is good to set it as the 1-10 period (1 / 30-1 / 3) of a television period. Further, when it is desired to detect a rough movement of the person 2, it may be long, for example, about 10 seconds. However, in the case of detecting the respiration of the person 2 as in the present embodiment, if it is too long, accurate detection of respiration cannot be performed. Hereinafter, an image acquired at an arbitrary time (current) is described as an acquired image, and an image acquired slightly before (past) the acquired image is described as a reference image. The reference image is stored in a storage unit (not shown).

  Further, in the present embodiment, the images at two different time points are an acquired image (N frame) and an image acquired immediately before the acquired image (N-1 frame). That is, the reference image is an image acquired immediately before the acquired image. The image acquisition interval may be appropriately determined depending on, for example, the processing speed of the apparatus and the content of the motion to be detected as described above. For example, the interval is 0.1 to 3 seconds, preferably about 0.1 to 0.5 seconds. It is good to do. Here, it is set to 0.1 to 0.25 seconds. In addition, it is effective to acquire images at shorter time intervals and perform averaging or filtering to reduce the influence of random noise, for example. The measuring unit 14 will be described in detail later.

  Returning to FIG. 10, an installation example of the FG sensor 10 will be described. On the bed 3 in the figure, the person 2 lies in a sleeping state. Here, the bedding 4 is further hung on the person 2 and covers a part of the person 2 and a part of the bed 3. In this case, the FG sensor 10 measures the amount related to the movement of the upper surface of the bedding 4 in the height direction within a certain time. When the bedding 4 is not used, the FG sensor 10 measures an amount related to the movement of the person 2 in the height direction within a certain time. Note that the movement of the person 2 in the height direction is, for example, movement accompanying the breathing or body movement of the person 2.

  The projection device 11 and the imaging device 12 constituting the FG sensor 10 are arranged above the bed 3 that is the measurement range in the vertical direction. The measurement range is set to a range including the chest and abdomen of the person 2. In the drawing, the projection device 11 is disposed approximately above the head of the person 2, and the imaging device 12 is disposed approximately at the center of the bed 3 or slightly above the head from the center. The projection device 11 projects a pattern 11 a as an illumination pattern on the bed 3. The pattern 11a is a plurality of bright spot lights. In addition, the angle of view of the imaging device 12 is set so that an approximately central portion of the bed 3 including a portion corresponding to the upper half of the person 2 can be captured. The imaging device 12 is installed so as to look down on the bed 3 substantially vertically, but may be installed with a certain degree of inclination. Here, each position of the plurality of bright spots 11b projected on the person 2 that can be imaged by the imaging device 12 corresponds to each measurement point.

  The projection device 11 and the imaging device 12 may be installed with a certain distance. By doing so, the distance d (baseline length d, see FIG. 13) becomes longer, so that the change can be detected sensitively (detection sensitivity is improved). The base line length is preferably long, but may be short. However, in this case, it is difficult to detect small movements such as respiration, but small movements (breathing) can be detected by detecting the barycentric position of the bright spot as described later.

  Here, the baseline length d (see FIG. 13) will be described. Here, the FG sensor 10 measures the movement of a bright spot forming a pattern, as will be described later with reference to FIG. At this time, for example, the greater the movement of the object (here, the person 2) in the height or height direction, the greater the movement amount of the bright spot. For this reason, according to the concept described later with reference to FIG. 13, if the amount of movement of the bright spot is large, a phenomenon may occur in which the bright spot adjacent to the bright spot to be compared is skipped. In this case, it is determined that the light has moved from the adjacent bright spot, and the amount of movement of the bright spot to be measured may be small. That is, the movement amount of the bright spot cannot be measured accurately. When the base line length is short, the amount of movement of the bright spot is small and the above jump is unlikely to occur, but it is difficult to distinguish it from noise for minute movements. In addition, when the base line length d (see FIG. 13) is long, even a slight movement of the object is greatly reflected in the amount of movement of the bright spot. Can be measured, but jumping may occur when there is a large movement, for example.

  FIG. 12 is a schematic perspective view for explaining the projection device 11 of the respiratory monitor 1 according to the embodiment of the present invention. With reference to this figure, the projection apparatus 11 suitable for the respiration monitor 1 is demonstrated. Here, for the sake of explanation, a case where the measurement range is the plane 102 and a laser beam L1 described later is projected perpendicularly to the plane 102 will be described. The projection apparatus 11 includes a light beam generation unit 105 serving as a light beam generation unit that generates a coherent light beam, and a fiber grating 120 (hereinafter simply referred to as a grating 120). The coherent light beam projected by the light beam generation unit 105 is typically an infrared laser. The light beam generation unit 105 is configured to generate a parallel light beam. The light flux generation unit 105 is typically a semiconductor laser device including a collimator lens (not shown), and the generated parallel light flux is a laser light flux L1. The laser light beam L1 is a light beam having a substantially circular cross section. Here, the parallel light flux only needs to be substantially parallel, and includes a nearly parallel light flux. The substantially circular shape includes a substantially elliptical shape.

  Further, here, the grating 120 is disposed in parallel to the plane 102 (perpendicular to the Z axis). Laser light L1 is incident on the grating 120 in the Z-axis direction. Then, the laser light L1 is collected in a plane having the lens effect by each optical fiber 121, then spreads as a diverging wave, interferes, and a plurality of bright spots on the plane 102 which is a light projecting surface. The pattern 11a which is an array is projected. Note that the arrangement of the grating 120 in parallel with the plane 102 means, for example, that the plane including the axis of each optical fiber 121 of the FG element 122 constituting the grating 120 and the plane 102 are parallel.

  The grating 120 includes two FG elements 122. In the present embodiment, the planes of the FG elements 122 are parallel to each other. Hereinafter, the plane of each FG element 122 is referred to as an element plane. In the present embodiment, the axes of the optical fibers 121 of the two FG elements 122 are substantially orthogonal to each other.

  The FG element 122 is configured by arranging, for example, several tens to several hundreds of optical fibers 121 having a diameter of several tens of microns and a length of about 10 mm in parallel in a sheet shape. Further, the two FG elements 122 may be arranged in contact with each other, or may be arranged at a distance from each other in the normal direction of the element plane. In this case, the distance between the two FG elements 122 is set so as not to interfere with the projection of the pattern 11a. The laser beam L1 is typically incident perpendicular to the element plane of the grating 122.

  Thus, since the grating 120 configured to include the two FG elements 122 serves as an optical system, the optical housing can be downsized without requiring a complicated optical system. Furthermore, by using the grating 120, the projection device 11 can project a plurality of bright spots 11b as patterns 11a onto the target area with a simple configuration. The pattern 11a is typically a plurality of bright spots 11b arranged in a square lattice pattern. The bright spot has a substantially circular shape including an ellipse.

FIG. 13 is a conceptual perspective view for explaining the concept of the bright spot movement of the respiratory monitor 1 according to the embodiment of the present invention. The imaging device 12 will be described with reference to this figure. The imaging device 12 has an imaging optical system 12 a and an imaging element 15. The image sensor 15 is typically a CCD image sensor. In addition to the CCD, an element having a CMOS structure has recently been actively announced as the imaging element 15, and these can naturally be used. In particular, some of the elements themselves have inter-frame difference calculation and binarization functions, and it is preferable to use these elements.
Is preferred.

  In addition, the imaging device 12 may include a filter 12b that attenuates light having a wavelength other than the peripheral portion of the wavelength of the laser light beam L1 generated by the light beam generation unit 105 (see FIG. 12). The filter 12b is typically an optical filter such as an interference filter, and may be disposed on the optical axis of the imaging optical system 12a. In this way, the imaging device 12 can reduce the influence of disturbance light because the light intensity of the pattern 11a projected from the projection device 11 out of the light received by the imaging device 15 is relatively increased. Further, the laser beam L1 (see FIG. 12) generated by the beam generation unit 105 (see FIG. 12) is typically an infrared laser beam. Further, the laser beam L1 (see FIG. 12) may be irradiated continuously or may be irradiated intermittently. When irradiating intermittently, imaging by the imaging device 12 is performed in synchronization with the timing of irradiation.

  Here, the concept of bright spot movement will be described. Here, it is easy to understand, and the target area will be described as the plane 102 and the target object as the object 103. Further, here, for description, the reference image is an image of the pattern 11a when the object 103 is not present on the plane 102, and the acquired image is described as the pattern 11a when the object 103 is present on the plane 102. To do.

  In the figure, an object 103 is placed on the plane 102. Further, the orthogonal coordinate system XYZ is taken so that the XY axis is placed in the plane 102, and the object 103 is placed in the first quadrant of the XY coordinate system. On the other hand, a projection device 11 and an imaging device 12 are arranged above the plane 102 on the Z axis in the drawing. The imaging device 12 images the plane 102 on which the pattern 11 a is projected by the projection device 11. In other words, the object 103 placed on the plane 102 is imaged.

  Here, the imaging lens 12a as the imaging optical system of the imaging device 12 is disposed so that its optical axis coincides with the Z-axis. The imaging lens 12 a forms an image of the pattern 11 a on the plane 102 or the object 103 on the imaging surface 15 ′ (image plane) of the imaging device 15 of the imaging device 12. The image plane 15 'is typically a plane orthogonal to the Z axis. Further, an xy orthogonal coordinate system is taken in the image plane 15 'so that the Z axis passes through the origin of the xy coordinate system. The projection device 11 is arranged at a distance equal to the imaging lens 12a from the plane 102 and a distance d (baseline length d) from the imaging lens 12a in the negative direction of the Y axis. A pattern 11 a formed by a plurality of bright spots 11 b is projected onto the object 103 and the plane 102 by the projection device 11.

  The pattern 11 a projected onto the plane 102 by the projection device 11 is blocked by the object 103 and does not reach the plane 102 in a portion where the object 103 exists. Here, if the object 103 exists, the bright spot 11 b to be projected onto the point 102 a on the plane 102 is projected onto the point 103 a on the object 103. Since the bright spot 11b has moved from the point 102a to the point 103a and the imaging lens 12a and the projection device 11 are separated by a distance d (baseline length d), the point 102a is formed on the imaging plane 15 ′. An image to be imaged at '(x, y) is imaged at a point 103a' (x, y + δ). That is, when the object 103 does not exist and when the object 103 exists, the image of the bright spot 11b moves by a distance δ in the y-axis direction.

  For example, as shown in FIG. 14, the bright spot imaged on the imaging surface 15 ′ of the image sensor 15 is moved in the y-axis direction by δ by the object 103 having a height.

  Thus, by calculating the moving amount δ of the bright spot, the position of the point 103a on the object 103 can be specified three-dimensionally. That is, for example, the height of the point 103a is known. Thus, by calculating the difference between a point that should be imaged on the imaging plane 15 ′ if the object 103 is not present and the actual imaging position on the imaging plane 15 ′, The height distribution of the object 103, in other words, the three-dimensional shape can be measured. Alternatively, the three-dimensional coordinates of the object 103 can be measured. Further, if the pitch of the pattern 11a, that is, the pitch of the bright spot 11b is made fine enough that the correspondence relationship of the bright spot 11b is not unknown, the height distribution of the object 103 can be measured in detail.

  Based on the above concept, the height of the object can be measured by calculating the movement amount of the bright spot. However, here, since the movement in the height direction is measured based on the acquired image and the image acquired immediately before the acquired image, that is, the reference image, the movement amount of the bright spot is observed. For this reason, for example, the absolute height of the person 2 cannot be measured, but there is no problem because the purpose is to detect the movement of the person 2 in the height direction.

  Returning to FIG. 11 again, the measurement unit 14 will be described in detail. As described with reference to FIG. 14, the movement amount calculation unit 141 calculates the movement amount of the bright spot. The movement amount calculation unit 141 is configured to calculate the movement amount of the bright spot as described above for each of the plurality of bright spots forming the pattern 11a. That is, the positions of a plurality of bright spots are measurement points. The movement amount calculation unit 141 outputs the movement amount of the bright spot calculated for each of the plurality of bright spots forming the pattern 11 a to the movement amount waveform generation unit 142. That is, the calculated movement amount of each bright spot becomes a measurement value at each measurement point. In other words, here, each measured value obtained by measuring the movement of the person 2 at a plurality of points corresponds to the amount of movement of each bright spot.

  It should be noted that a waveform (for example, a sum of bright spot movement amounts) obtained by measuring bright spot movement based on an image at an arbitrary time point and two time points slightly different from the previous time point is a differential waveform of distance, The waveform represents the speed change. For example, when it is desired to obtain a waveform representing a change in height, if the waveform is integrated, a waveform of distance, that is, a waveform indicating a change in height is obtained.

  Here, the acquired image and the reference image are images picked up by the image pickup device 12, for example, and are concepts including the position information of the bright spot on each image. In other words, the acquired image and the reference image are images of the pattern 11a formed by the projection of the projection device 11 at each time point. In the present embodiment, the reference image is not stored as a so-called image, for example, but is stored in a storage unit (not shown) in the form of positional information such as coordinates regarding the position of each bright spot. In this way, when calculating the amount of movement of the bright spot, which will be described later, for example, it is only necessary to compare the coordinates and direction of the bright spot, so the processing becomes simple. Further, here, the position of the bright spot is the barycentric position of the bright spot. By doing so, a slight movement of the bright spot can be measured.

  Further, the movement amount of the bright spot can be calculated by comparing the position information of each bright spot on the reference image with the position information of each bright spot on the acquired image. Each amount of movement can be obtained, for example, by counting the number of pixels to which the position of the bright spot has moved (how many pixels have moved). However, if the position of the bright spot is obtained as the position of the center of gravity, the movement amount can be calculated in units smaller than one pixel. The calculated moving amount of the bright spot is a concept including the moving direction of the bright spot. In other words, the measured moving amount of the bright spot includes information on the moving direction. In this way, as will be described later, it is not necessary to generate a difference image, so that the processing can be simplified.

  In the above description, the position information of the bright spots is compared. However, a difference image between the reference image and the acquired image may be created. In this case, the movement amount of the bright spot is calculated from the difference image based on the position of the corresponding bright spot. In this way, since only the moved bright spot remains on the difference image, the processing amount can be reduced.

  The movement amount waveform generation unit 142 generates movement amount waveform data in which the movement amounts of the bright spots calculated by the movement amount calculation unit 141 are arranged in time series. Here, as described above, the movement amount of the bright spot calculated by the movement amount calculation unit 141 includes the acquired image (N frame) and the image acquired immediately before the acquired image (N-1 frame). Are calculated on the basis of images of two frames acquired at different points in time. In other words, the calculation is made based on images of two time points, which are different from an arbitrary time point and a slightly previous time point. For this reason, the generated movement amount waveform data (for example, when the total movement amount of each bright spot is taken) is a volume fluctuation waveform per unit time or a rough fluctuation waveform of average height per unit time. That is, the waveform represents a change in volume fluctuation or a change in average height. For example, when it is desired to obtain a waveform representing the transition of the height, the waveform of the distance, that is, the waveform indicating the transition of the height is obtained by integrating the waveform.

  Here, when the total amount of movement is taken, the volume fluctuation amount per unit time is generally shown. Since the movement of each bright spot indicates individual height fluctuations, taking the summation results in volume fluctuations. The amount of movement of each bright spot is a change in the bright spot position per unit time at each bright spot position (ie, bright spot moving speed), and roughly corresponds to a height change in unit time.

  The movement amount waveform generation unit 142 uses the movement amount waveform data generated as described above as measurement data, the first state determination unit 24 (see FIG. 1) of the computing device 20, the spectrum calculation unit 26 (see FIG. 1), This is output to the body motion detector 28 (see FIG. 1) and the like. That is, the movement amount waveform generation unit 142 is a body that is movement data waveform data that is at least the above-mentioned movement amount waveform data that is the sum of movement amounts of bright spots and the sum of absolute values of movement amounts of bright spots, for example. Measurement data including both waveform data and dynamic data is output.

  Note that the detection sensitivity and noise level of the measurement data acquired by the FG sensor may be affected by environmental conditions such as ambient light conditions and the posture and position of the person 2 on the bed 3. As a case where the posture or position of the person 2 on the bed 3 is affected, for example, the projection device 11 (see FIG. 10) is placed in the bed 3 (see FIG. 10) in order to increase the base line length d (see FIG. 13). The projection of the pattern 11a (see FIG. 10) is performed obliquely when installed off the center of the screen, and the density of bright spots on the bed 3, in other words, the bright spot interval is As the distance increases, the detection sensitivity and noise level may differ between a position close to and far from the projection device 11.

  FIG. 15 is a flowchart showing an outline of processing steps by the respiratory monitor 1 according to the embodiment of the present invention. A method for monitoring an abnormality of the person 2 by the respiratory monitor 1 will be described with reference to FIG. For the configuration of the respiratory monitor 1, refer to FIG. 1 or FIG. 11 as appropriate. In addition, the description which overlaps with the description of the structure of the respiration monitor 1 shall be omitted as much as possible.

  First, as the bright spot movement amount acquisition step, two frames acquired by the imaging device 12 at different time points for each of the plurality of bright spots 11b (see FIG. 10) projected on the bed 3 by the movement amount calculation unit 141. The amount of bright spot movement between the two frames of the plurality of bright spots 11b (see FIG. 10) is calculated from the image (S100). Next, as a measurement data generation step, the movement amount waveform generation unit 142 generates measurement data as movement amount waveform data in which the bright spot movement amounts calculated by the movement amount calculation unit 141 are arranged in time series (S102). Specifically, the movement amount waveform generation unit 142 generates respiratory data that is movement amount waveform data of the sum of bright spot movement amounts and body movement that is movement amount waveform data of the sum of absolute values of movement amounts of bright spots, for example. Generate data and.

  Next, the body motion reference value calculated by the body motion detection unit 28 based on the measurement data (for example, body motion data) within the body motion reference value calculation period T7 up to the previous determination target time point and the determination target time point Are compared with the body movement data (measured values) of the body, and it is determined whether or not the movement at the determination target time point is a body movement, that is, whether or not the determination target time point is included in the body movement period (S104). Here, when the determination target time point is the body movement period (S104; YES), it is determined whether or not the monitoring of the person 2 is continued without determining the abnormality of the person 2 by the respiration monitor 1 at the present time. (S114). When monitoring is continued (S114; YES), the process returns to the bright spot movement amount acquisition step (S100), and the subsequent processes are repeated. If the monitoring is not continued (S114; NO), the monitoring is terminated. When the determination target time point is not the body movement period (S104; NO), the process proceeds to the next stage body movement reference value calculation step (S106).

  In the case immediately after the start of monitoring by the respiratory monitor 1, the next body motion reference value calculation step (S106) has not yet been executed and the body motion reference value has not been calculated. It may be assumed that the determination target time is not a body movement period, and the process may proceed to the body movement reference value calculation step (S106), or a body movement reference value used only immediately after the start may be set in advance. .

  In the body movement reference value calculation step, the body movement reference value is calculated by the body movement detection unit 28 based on the measurement data (for example, body movement data) within the body movement reference value calculation period T7 up to the determination target time (S106). . The body movement reference value calculated using data up to the current determination target time (including data at the determination target time) is used for detection of body movement at the next determination target time. The body motion detection unit 28 calculates the body motion reference value without including the period already determined to be the body motion period in the body motion reference value calculation period T7. The body movement reference value calculation step (S106) may be performed before the step (S104) of determining whether or not the determination target time point is a body movement period. In this case, instead of using the body motion reference value calculated at the previous time point (determination target time point that goes back one point in time) as the body motion reference value actually used at the determination target time point, immediately before the determination target time point ( The body motion reference value is calculated based on the measurement data (for example, body motion data) within the body motion reference value calculation period T7 (not including data at the determination target time), and is used as it is for the determination target time. do it. This is because it is determined in the next stage whether or not the measurement data at the determination target time point is body movement. Here, whether or not the measurement data at the determination target time point may be used for calculation of the body movement reference value. I don't know.

  Next, as the first state determination step, based on the measurement data, the determination is made according to the probability distribution of the data related to the quasi-tidal volume in the reference data acquisition period T2 and the quasi-tidal volume in the observation period T1. It is determined whether or not the state of the person 2 at the target time is abnormal (S108). In the present embodiment, as described above, the first state determination unit 24 calculates the determination threshold based on the probability distribution of data related to the quasi-tidal volume during the reference data acquisition period T2 and the target false alarm frequency. The determination threshold value is compared with the maximum value of the quasi-tidal volume within the observation period T1. When the maximum value of the quasi-tidal volume falls below the determination threshold (S108; YES), the first state determination unit 24 determines that the breathing of the person 2 is abnormal and sends an alarm signal to the alarm device. 36, and the alarm device 36 issues an alarm (S118). When the maximum value of the quasi-tidal volume does not fall below the determination threshold (S108; NO), the process proceeds to the next power spectrum calculation step (S110).

  In S108, when the observation period T1 or the reference data acquisition period T2 and the body movement period overlap, the first state determination unit 24 obtains the measurement data of the body movement period from the observation period T1 or the reference data acquisition period T2. A period corresponding to the excluded period is added to the remaining period from the past side to obtain an observation period T1 or a reference data acquisition period T2.

  Further, in the case immediately after the start of monitoring by the respiration monitor 1, the determination threshold value may not be calculated because the reference data acquisition period T2 cannot be secured. In this case, it may be assumed that there is no abnormality at the current determination target time, and the process may proceed to the next power spectrum calculation step (S110), or a determination threshold value used only immediately after the start may be set in advance. It may be left.

  In the power spectrum calculation step (S110), the spectrum calculation unit 26 calculates the power spectrum at the determination target time point from the respiration data of the data accumulation time T3 (here, about 8 seconds) immediately before the determination target time point using FFT. Next, the spectrum comparison unit 27 calculates and compares the signal component by taking the sum of the power spectra of the low frequency components and the noise component by taking the sum of the power spectra of the high frequency components.

  Next, as a second state determination step, the second state determination unit 25 determines whether the signal component is below the noise component based on the comparison result between the signal component and the noise component by the spectrum comparison unit 27. If it is determined (S112) and the signal component does not fall below the noise component (S112; NO), the process proceeds to the next S114. When the signal component is below the noise component (S112; YES), the second state determination unit 25 determines that the period during which the signal component is below the noise component is the determination evaluation period T4 (here, 8 seconds). Degree) It is determined whether or not it has elapsed continuously (S116). If the discriminant evaluation period T4 has not elapsed (S116; NO), the process proceeds to S114. When the discrimination evaluation period T4 has elapsed (S116; YES), the second state discrimination unit 25 discriminates that the breathing of the person 2 is abnormal, transmits an alarm signal to the alarm device 36, and the alarm device 36 issues an alarm (S118). In S114, it is determined whether or not the monitoring is continued. When the monitoring is continued (S114; YES), the process returns to the bright spot movement amount acquisition step (S100), and the subsequent processes are repeatedly executed. If the monitoring is not continued (S114; NO), the monitoring is terminated.

  Here, each process in each part of the arithmetic unit 20 and the above-described method are installed as a software program to operate the computer as a respiratory monitor and control the computer to execute each process. It can be realized and can also be realized as a recording medium for recording the software program. The software program may be recorded and used in a program unit (not shown) built in the computer, recorded in an external storage device or CD-ROM, and read and used by the program unit (not shown). Alternatively, it may be downloaded from the Internet to a program unit (not shown) and used.

  According to the respiratory monitor 1 or the software program according to the embodiment of the present invention described above, the first state determination unit 24 includes the probability distribution of data related to the quasi-tidal volume during the reference data acquisition period T2, and By determining whether or not the state of the person 2 at the determination target time point is abnormal according to the quasi-tidal volume during the observation period T1, the state of breathing can be safely determined without imposing a burden on the person 2 as much as possible. can do. That is, the abnormality determination can be performed with few false alarms without acquiring a large amount of data in the dangerous state of the person 2. In addition, by setting a determination threshold according to the probability distribution of data related to the quasi-tidal volume during the reference data acquisition period T2 and the target false alarm frequency, depending on the situation such as symptoms of sleep disordered breathing peculiar to the person 2 Since a threshold value as high as possible can be set, it is possible to prevent detection errors while preventing false alarms. In addition, the determination based on the maximum value of quasi-tidal volume as described above makes it difficult for patients with neuromuscular disease, etc. to take a large breath when artificial ventilation ceases. This is preferable because the maximum value does not increase.

  Furthermore, the second state determination unit 25 determines the stop of breathing based on the relative comparison result between the signal component and the noise component without using one fixed threshold value, for example. Even when the detection sensitivity and noise level of the measurement data acquired by the FG sensor 10 to be described later change due to environmental conditions such as the posture of the camera, the state of the top cover, the situation of ambient light, etc. Accurate discrimination can be made. In addition, since the second state determination unit 25 performs the determination based on the relative comparison result between the signal component and the noise component, for example, when the artificial respiration circuit is disconnected at the time of the posture change of the person 2 or removed at the time of care If the person 2 forgets or the posture of the person 2 changes due to body movement such as turning over, it is not necessary to set a threshold again over a certain amount of time, and the respiratory stop of the person 2 can be detected quickly. .

  Further, by combining the first state determination unit 24 and the second state determination unit 25, either the first state determination unit 24 or the second state determination unit 25 can detect abnormal breathing of the person 2. Since a respiratory abnormality can be detected when it is determined, a comprehensive and leak-free determination can be made.

When the body motion period detected by the body motion detection unit 28 overlaps with the observation period T1, the reference data acquisition period T2, etc., the body motion period is excluded from the observation period T1, the reference data acquisition period T2, etc. Since discrimination is performed, more accurate discrimination can be performed.
By not using, more accurate discrimination can be made.

  Therefore, for example, when a patient who has little spontaneous breathing cannot breathe due to disconnection of the artificial respiration circuit, that is, when the patient's breathing stops or when there is a certain spontaneous breathing, It is possible to prevent the trouble of artificial respiration directly leading to a serious accident when it stops working.

  In addition, since the respiratory monitor 1 uses the FG sensor 10 as a measuring device, measurement data indicating the state of the person 2 can be acquired without touching the person 2, and the person 2 is not burdened, so that a healthy person can sleep. In addition to respiratory monitoring and in-patient respiration monitoring, it is optimal for muscular dystrophy and ALS patients who are constantly performing artificial respiration. Furthermore, even small movements of the person 2 such as breathing can be accurately measured. Further, there is no possibility that data in the natural state of the person 2 cannot be obtained, or that the sensor is detached during sleep and data is lost. In addition, since it is not necessary to attach sensors directly to the body of the person 2, less manpower is required for installation, and the load can be reduced both in terms of cost and psychology.

  Note that the first state determination unit 24 described above is based on the measurement data indicating the state of the person 2 having a periodic motion, and the observation period T1 before and after the determination target time point (for example, see FIG. 3). It can be said that it is determined whether or not the state of the person 2 at the determination target time point is abnormal based on a comparison between the maximum value of the data regarding the quasi-tidal volume and the determination threshold value as the maximum threshold value. That is, even when the person 2 is performing periodic breathing, even when the magnitude of the movement of breathing is small, an abnormality in breathing (for example, a decrease in breathing) can be determined. It is possible to discriminate abnormalities that may exist despite periodic movements. Furthermore, the second state determination unit 25 determines whether or not the state of the object 2 at the determination target time point is abnormal based on whether or not the data regarding the quasi-tidal volume at the determination target time point falls below the minimum threshold value. It can be said that it is to be discriminated. That is, here, the value of the noise component with respect to the signal component is the minimum threshold value. As a result, it is possible to prevent an abnormality detection failure.

  In the above description, the respiration monitor 1 is a device that detects an abnormality in the artificial respiration circuit of the person 2 who is performing artificial respiration, and is, for example, a device intended to prevent an accident of artificial respiration. Explained as a thing. However, the present invention is not limited to this, and it goes without saying that, for example, an apparatus that simply discriminates a state where breathing has stopped or a state where breathing has fallen may be used, even if the purpose is not to prevent an accident of artificial respiration. That is, in this case, that the person 2 is abnormal means a dangerous breathing state such as a state where the breathing is stopped or a state where the breathing is lowered.

It is a block diagram which shows the structural example of the respiration monitor which concerns on embodiment of this invention. It is the schematic shown about the example of the waveform pattern which the respiration data and body motion data which are used for the respiration monitor which concerns on embodiment of this invention form. It is a figure explaining the observation period and reference | standard data acquisition period which are used for the respiration monitor which concerns on embodiment of this invention. It is the figure which showed an example of distribution of the data regarding the quasi-tidal volume used for the respiration monitor which concerns on embodiment of this invention. It is the figure which showed the 1st specific example about transition of the measurement data used for the respiration monitor which concerns on embodiment of this invention, and a quasi-tidal volume. It is a figure explaining the case where a body movement period overlaps with an observation period in the respiration monitor concerning an embodiment of the invention. It is the figure which showed an example of the power spectrum calculated by the spectrum calculation part of the respiration monitor which concerns on embodiment of this invention. It is a diagram explaining the respiration data acquired by the actual measurement of the respiration monitor which concerns on embodiment of this invention, the signal component compared with a spectrum comparison part, and the data of a noise component. It is a diagram which shows the example of the histogram of the measurement data used when the respiration monitor which concerns on embodiment of this invention calculates | requires information entropy. It is a typical perspective view of the FG sensor of the respiration monitor which concerns on embodiment of this invention. It is a block diagram which shows schematic structure of the FG sensor of the respiration monitor which concerns on embodiment of this invention. It is a typical perspective view explaining the projection apparatus of the respiration monitor which concerns on embodiment of this invention. It is a conceptual perspective view explaining the concept of the movement of the bright spot of the respiratory monitor according to the embodiment of the present invention. It is a schematic diagram explaining the bright spot imaged on the image receiving surface in the case of FIG. It is a flowchart which shows the outline of the process process by the respiration monitor which concerns on embodiment of this invention.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Respiration monitor 2 Person 3 Bed 10 FG sensor 11 Projector 11a Pattern 11b Bright spot 12 Imaging device 14 Measuring unit 20 Calculation unit 24 First state determination unit 25 Second state determination unit 26 Spectrum calculation unit 27 Spectrum comparison unit 28 Body motion detector 29 Threshold acid calculator 36 Alarm device 141 Movement amount calculator 142 Movement amount waveform generator T1 Observation period T2 Reference data acquisition period T3 Data accumulation time T4 Discriminant evaluation period T5 Spectral averaging period T6 Respiration cycle calculation period T7 Body movement reference value calculation period T8 Body movement determination value calculation period

Claims (12)

Based on measurement data indicating the state of an object with periodic movement, a probability distribution of data relating to the magnitude of periodic movement in a second predetermined period before and after the first predetermined period before and after the determination target time point; And a first state determination means for determining whether or not the state of the object at the determination target time point is abnormal according to the magnitude of the periodic movement in the first predetermined period;
State analysis device. The first state determination unit is configured to store data related to the periodic motion magnitude in the first predetermined period based on a probability distribution of data related to the periodic motion magnitude in the second predetermined period. Estimating a first probability of occurrence of a predetermined range of distribution states determined from the distribution, and determining abnormality of the object using the first probability;
The state analysis apparatus according to claim 1. The first state discriminating means is based on the probability distribution of the data relating to the magnitude of the periodic movement in the second predetermined period, and the distribution of the magnitude of the periodic movement in the first predetermined period. The predetermined range in which the occurrence probability of the distribution state in the predetermined range obtained from the above is less than or equal to the second probability, and the distribution state of the data relating to the magnitude of the periodic motion in the first predetermined period falls within the predetermined range Determining abnormality of the object based on whether it is included,
The state analysis apparatus according to claim 1. The first state determination means calculates a threshold based on a probability distribution of data related to the magnitude of periodic movement in the second predetermined period and the second probability, When the maximum value of the magnitude of periodic movement falls below the threshold, it is determined that the object is abnormal.
The state analysis apparatus according to claim 3. Second state determining means for determining whether or not the state of the object at the determination target time point is abnormal according to a comparison result of a value based on the measurement data in a third predetermined period with a reference value;
The state analysis apparatus of any one of Claim 1 thru | or 4. Spectrum calculating means for calculating a spectrum of the third predetermined period based on the measurement data;
Spectrum comparison means for comparing a low frequency component and a high frequency component of the spectrum based on the spectrum;
The second state determining means determines an abnormality of the object based on a comparison result of the spectrum comparing means;
The state analysis apparatus according to claim 5. The first state determination means further determines that the object is abnormal when the period of the periodic movement at the determination target time point fluctuates.
The state analysis apparatus of any one of Claim 1 thru | or 6. Aperiodic motion detection means for determining and detecting aperiodic motion that occurs with the periodic motion based on the measurement data;
The first state determination unit sets the first predetermined period or the second predetermined period as a period excluding a period in which a non-periodic motion is detected by the non-periodic motion detection unit.
The state analysis apparatus of any one of Claim 1 thru | or 7. The magnitude of the periodic movement uses a value obtained by integrating the measurement data from zero cross to zero cross.
The state analysis apparatus according to any one of claims 1 to 8. A measuring device for acquiring the measurement data;
The measurement apparatus includes: a projection apparatus that projects a plurality of bright spots on a target area; an imaging apparatus that captures a target area on which the plurality of bright spots are projected; and two frames acquired at different times by the imaging apparatus. A movement amount calculating means for calculating a movement amount between the two frames of the plurality of bright spots from an image; and a movement amount waveform generating means for generating movement amount waveform data in which the movement amounts are arranged in time series.
The state analysis apparatus according to any one of claims 1 to 9. A software program installed on a computer and operating the computer as a state analysis device;
Based on measurement data indicating the state of an object with periodic movement, a probability distribution of data relating to the magnitude of periodic movement in a second predetermined period before and after the first predetermined period before and after the determination target time point; Controlling the computer to execute a process of determining whether or not the state of the object at the determination target time point is abnormal according to the magnitude of the periodic movement in the first predetermined period;
Software program. Based on measurement data indicating the state of an object with periodic movement, based on a comparison between a maximum value and a maximum threshold value of data regarding the magnitude of periodic movement in a first predetermined period before and after the determination target time point And a first state determining means for determining whether or not the state of the object at the determination target time point is abnormal;
State analysis device.