JP5896832B2 - Sample information processing apparatus and sample information processing method - Google Patents

Description

  The present invention relates to a sample information processing apparatus and a sample information processing method for detecting sample information and processing the sample information.

Sensors that detect pulsating signals of arms with relatively thick blood vessels in them or fingertips with capillaries stretched like a net have a structure with a closed space. The heart is transmitted through the blood vessel by applying pressure to the skin of the arm or fingertip at a very weak level that does not obstruct the flow of blood vessels, and placing a pressure sensor such as a condenser microphone on the other side. 2. Description of the Related Art There is known a pressure sensor device that detects a pulse wave caused by a pulsation of a current with a good S / N ratio as a pressure change in a closed space.
Conventionally, various methods have been proposed in order to improve the detection sensitivity of a blood vessel pulsation signal by a pressure sensor device.

  In Patent Document 1 (Japanese Patent Laid-Open No. 63-0154153), a finite volume cavity having an opening formed by the detection body at a contact portion with the detection body, an omnidirectional microphone installed in the cavity, and There is disclosed a sensor for detecting an expansion change or a contraction change of an object to be detected as a pressure change in the cavity with the omnidirectional microphone.

  In Patent Document 2 (Japanese Patent Laid-Open No. 2010-115431), a housing having a cavity is mounted on the skin surface by a mounting member, an opening in a part of the mounting surface is sealed by the skin, and vibration of the skin surface due to body sound is generated. A body sound acquisition device is disclosed that is directly transmitted to air in a cavity and can be acquired by a microphone.

  Patent Document 3 (Japanese Patent Laid-Open No. 11-56799) includes a pressure surface that is pressed against the neck of a living body, and includes a plurality of pressure sensors that detect pressure on the pressure surface. A carotid pressure wave detection device that detects the pressure wave in the carotid artery of the head is described, and the carotid pressure wave is easily detected by correcting the pressure signal output from the pressure sensor using a plurality of pressure sensors. It is disclosed that it can be done.

  In Patent Document 4 (Japanese Patent Application Laid-Open No. 2004-321254), a pressure surface is provided with a plurality of pressure detection elements, the pressure surfaces are pressed toward a predetermined artery from the skin of the living body, and the arteries are detected by the pressure detection element. A pressure pulse wave detection device having a pressure pulse wave detection probe for detecting a pressure pulse wave from the pressure pulse wave is described, and by removing the pressure pulse wave mixed with artifacts, of the remaining pressure pulse waves not removed It is described that a pressure pulse wave having an accurate shape with little influence of artifact is obtained by selecting any one of the above or averaging the remaining pressure pulse waves.

JP 63-0154153 A JP 2010-115431 A Japanese Patent Laid-Open No. 11-56799 JP 2004-321254 A

In the case of Patent Document 1, the opening of the pressure sensor is large enough to insert a finger, and there is a problem that it is difficult to detect vibration of a blood vessel at a specific part of a specimen with high directivity.
In the case of the above-mentioned Patent Document 2, the in-vivo sound acquisition device has a hole diameter of 1 mm or 3 mm, and is not devised to measure the vibration of a thin blood vessel without a microphone directly above it.

  An ECM (electret condenser microphone, hereinafter also referred to as ECM) used for a pressure sensor is designed so that the sensitivity of a signal in a low frequency region is low for reasons such as windbreaking. This property is not mentioned.

  Moreover, in order to improve the detection sensitivity of the pulsation signal of the blood vessel by the pressure sensor device, it is important to estimate the position information of the blood vessel, in particular, the depth information of the blood vessel. There is no description about estimating blood vessel depth information.

  The present invention has been made in view of such problems, and does not require the accuracy of the positional relationship between the sensor and the blood vessel, has directivity for sensing, and detects a pulsation signal of the blood vessel. It is another object of the present invention to provide a sample information processing apparatus and a sample information processing method capable of obtaining blood vessel depth information from this pulsating signal.

  In order to achieve the above object, a sample information processing apparatus of the present invention receives pressure information resulting from a blood vessel pulsation signal in a sample, detects a blood vessel pulsation signal in the sample, and the sensor A state of having a cavity communicating with the pressure information capturing portion and having an opening having a diameter of 3 mm to 10 mm at a portion facing the sample, and mounted on the sample with the opening facing the sample A plurality of pulsating signal detection units having a sensor mounting portion having a spatial structure in which the cavity is closed, and these pulsating signal detection units are arranged in parallel to form a pulsating signal detection unit array, A blood vessel information detection unit for obtaining depth information of the blood vessel is obtained by performing a required calculation on the pulsation signal output from each sensor of the pulsation signal detection unit array. It is characterized in that it is configured Te.

Here, the sample information processing apparatus of the present invention includes a level detection unit that detects an output level from at least one of the plurality of sensors that changes as the pulsation signal detection unit array moves. Also good.
The sample information processing apparatus of the present invention further includes a level display unit that displays output level change information based on a detection result of the level detection unit, and the level display unit is provided in the pulsation signal detection unit array. May be.

Further, the sample information processing apparatus of the present invention performs at least a pulsating volume signal, a pulsating velocity signal, and a pulsating property by performing a frequency correction process on the pulsating signal output from the sensor of the pulsating signal detection unit array. A signal correction unit that extracts one of the acceleration signals may be provided.
In the sample information processing apparatus of the present invention, the signal correction unit performs at least one of an amplification operation, an integration operation, and a differentiation operation at a frequency of the pulsation signal, so that at least the pulsation property described above is obtained. It may be configured to retrieve one of the volume signal, the pulsating velocity signal, and the pulsating acceleration signal.

  The sample information processing apparatus of the present invention extracts a respiratory signal included in the pulsation signal output by performing frequency demodulation processing on the pulsation signal output from the sensor of the pulsation signal detection unit array. A frequency demodulation unit may be provided.

In the sample information processing apparatus of the present invention, the sensor may be configured as a condenser microphone that detects sound pressure information caused by a pulsating signal of an arterial blood vessel in the sample.
In the sample information processing apparatus of the present invention, the condenser microphone may be configured by a MEMS type ECM.
In the sample information processing apparatus of the present invention, the diameter of the opening may be not more than 5 times the diameter of the arterial blood vessel.

  Another gist of the present invention is a sensor that receives pressure information resulting from a pulsation signal of a blood vessel in a specimen and detects a pulsation signal of a blood vessel in the specimen, and a portion that takes in the pressure information of the sensor. The cavity is closed in a state of having an opening having a diameter of 3 mm to 10 mm at a portion facing the specimen and having the opening facing the specimen, with the opening facing the specimen. A pulsating signal detection unit array having a sensor mounting portion having a spatial structure and configured by arranging a plurality of pulsating signal detection units in parallel is prepared, and the pulsating signal detection unit array is crossed with the blood vessel. The pulsation signal detection unit is installed in a direction so that one pulsation signal detection unit of the pulsation signal detection unit array faces the blood vessel. A sample information processing method characterized in that the blood vessel depth information is obtained by receiving an output from each sensor of the pulsation signal detection unit array and performing a required calculation. Exist.

  Here, the specimen information processing method of the present invention includes the pulsation signal output intensity from the sensor of the pulsation signal detection unit at a position facing the blood vessel of the pulsation signal detection unit array, and the pulsation signal detection. The intensity of the pulsating signal output from the sensor of the other pulsating signal detection unit of the unit array, and the pulsating signal detection unit and the other pulsating signal detection at a position facing the blood vessel of the pulsating signal detection unit array The blood vessel depth information may be obtained from the distance to the unit.

  Further, the specimen information processing method of the present invention detects an output level from at least one of the plurality of sensors that changes with the movement of the pulsation signal detection unit array, and changes the output level. Based on this, position information of the blood vessel may be obtained.

  Further, the sample information processing method of the present invention performs at least a pulsating volume signal, a pulsating velocity signal, and a pulsating property by performing frequency correction processing on the pulsating signal output from the sensor of the pulsating signal detection unit array. One of the acceleration signals may be extracted.

  The sample information processing method of the present invention extracts a respiratory signal included in the pulsation signal output by performing frequency demodulation processing on the pulsation signal output from the sensor of the pulsation signal detection unit array. May be.

  According to the present invention, blood vessel depth information can be obtained from blood vessel pulsation signal output. In addition, according to the present invention, it is possible to provide a sample information processing apparatus and a sample information processing method that have a mechanism that does not require the accuracy of the positional relationship between a sensor and a blood vessel and that detect a pulsating signal of the blood vessel. Further, the pulsation signal detection unit of the present invention has a narrow sensing range as a pressure sensor and can have high directivity (or spatial resolution). In the present invention, the S / N ratio and sensitivity of the pulsation signal can be improved by detecting the pulsation signal at a position close to the blood vessel using the directivity of the pulsation signal detection unit.

It is a figure which represents typically the structure of the sample information processing apparatus concerning one Embodiment of this invention. It is a block diagram for demonstrating the function structure of the sample information processing apparatus concerning one Embodiment of this invention. It is a block diagram for demonstrating the function structure of the sample information processing apparatus concerning one Embodiment of this invention. It is a flowchart for demonstrating an example of the sample information processing in a sample information processing apparatus. It is a flowchart for demonstrating an example of the sample information processing in a sample information processing apparatus. It is a schematic diagram which shows an example which followed the artery of the palm of the left hand. It is a figure which shows an example of the relationship between the aperture diameter of a sample information processing apparatus, and the strength of a signal. It is a block diagram for demonstrating an example of a function structure of a frequency demodulation part. It is a figure showing an example of the frequency response at the time of making it the open state of a microphone. It is a figure showing an example of the frequency response at the time of making it the closed state of a microphone. It is a figure which represents typically an example of a structure of ECM. It is a figure which represents typically an example of the structure which looked at the inside of MEMS-ECM from the upper part. It is a figure which represents typically an example of a structure of the diaphragm of a MEMS-ECM, and a backplate part. It is a figure showing an example of the circuit structure of MEMS-ECM. It is the figure which represented typically the structure of the apparatus for demonstrating an example of the measuring method of the frequency characteristic of MEMS-ECM. It is a figure showing an example of the frequency characteristic in the low frequency area at the time of closed cavity formation of MEMS-ECM. It is a figure for demonstrating an example of the method of the frequency correction process of the output from MEMS-ECM. It is a figure which shows an example of the analog circuit for implement | achieving a frequency correction process. It is a figure which shows an example of the frequency characteristic of the pulse wave after the frequency correction measured by MEMS-ECM. It is a figure which shows the waveform measured using MEMS-ECM, Comprising: (a) is a figure showing an example of the volume pulse wave waveform in the wrist rib measured using MEMS-ECM, (b) is MEMS-ECM. The figure showing an example of the velocity pulse wave waveform in the wrist rib measured using, (c) is a figure showing an example of the acceleration pulse wave waveform in the wrist rib measured using MEMS-ECM. It is a figure which shows the waveform measured using the piezoelectric element, Comprising: (a) is a figure showing the volume pulse wave of the carotid artery measured using the piezoelectric element, (b) is the velocity pulse of the carotid artery measured using the piezoelectric element. FIG. 6C is a diagram showing an acceleration pulse wave of the carotid artery measured using a piezoelectric element. It is a figure showing an example of the change of the pulse wave in the sample information processing apparatus using MEMS-ECM. It is a block diagram showing an example of the function structure in the signal processing accompanying the change of a pulse wave. It is a figure which represents typically the positional relationship of the pulsation signal detection unit array and blood vessel in the sample information processing apparatus concerning one Embodiment of this invention. It is a figure which represents typically the positional relationship of the pulsation signal detection unit array and blood vessel in the sample information processing apparatus concerning one Embodiment of this invention. It is a figure showing typically an example of the point which tracked the artery of the sample, and the arrangement position of a pulsation signal detection unit. It is a figure showing an example of the pulse wave waveform from each sensor of the pulsation signal detection unit array in the sample information processor concerning one embodiment of the present invention, and (a) The pulse wave waveform of the pulsation signal detection unit of one end The figure showing an example, (b) is a figure showing an example of the pulse wave waveform of a center pulsation signal detection unit, (c) is a figure showing an example of the pulse wave waveform of the pulsation signal detection unit of the other end. . It is a figure for demonstrating calculation of the positional relationship and blood vessel depth information of the pulsation signal detection unit and blood vessel in the sample information processing apparatus concerning one Embodiment of this invention.

Embodiments of the present invention will be described below with reference to the drawings.
[1. Sample Information Processing Apparatus and Sample Information Processing Method]
[1-1. Sample configuration of sample information processing apparatus]
<Configuration of specimen information processing apparatus>
The sample information processing apparatus 1 (hereinafter also referred to as the present sample information processing apparatus) of the present invention includes a plurality of pulsating signal detection units 11a, 11b, and 11c and a signal processing unit 41 as shown in FIG. Has been. In the case where the plurality of pulsation signal detection units 11a, 11b, and 11c are not particularly distinguished, the same reference numerals are given as “pulsation detection units 11”, and portions common to the pulsation detection units are also described. In some cases, the same reference numerals are used for explanation.

  The pulsation signal detection units 11a, 11b, and 11c detect the pulsation signal and output the pulsation signal to the signal processing unit 41. The pulsation signal detection units 11a, 11b, and 11c include the sensors 31a, 31b, and 31c and the sensor attachment unit 21. . The pulsation signal detection unit 11 is arranged in parallel on the skin 92 of the specimen 91 to constitute a pulsation signal detection unit array 12. In the case where the sensors 31a, 31b, and 31c are not particularly distinguished, the description may be given with the same reference numerals as the “sensor 31”.

  In the present embodiment, a case where three pulsation signal detection units 11 are arranged to constitute a pulsation signal detection unit array 12 will be described. In FIG. 1, a gap is formed between the pulsation signal detection units 11, but these pulsation signal detection units 11 are connected to each other and configured integrally.

  The sensor 31 receives pressure information resulting from the pulsation signal of the arterial blood vessel 93 in the sample 91, and detects the pulsation signal of the arterial blood vessel 93 in the sample 91. The housing 35 of the sensor 31 has a pressure information capturing unit 32, and a sensor element 33 is provided in an air chamber 34 that is a space inside the housing 35.

  In FIG. 1, the arterial blood vessel 93 is shown as viewed from the cross-sectional direction, and the pulsating signal detection unit array 12 in which the pulsating signal detection units 11 are arranged in parallel intersects with the flow direction of the arterial blood vessel 93. Thus, they are preferably arranged so as to be orthogonal. Hereinafter, arterial blood vessels may be simply referred to as blood vessels.

  The sensor attachment portion 21 is a portion that comes into contact with the skin 92 of the sample 91 when the sample information processing apparatus 1 is attached to the sample 91, and is provided on the surface of the sensor 31 having the pressure information capturing portion 32. And a cavity (cavity) 23 formed by a rubber O-ring 24 and communicating with a pressure information capturing part 32 of the sensor 31, and an opening 22 at a portion facing the specimen 91. The cavity 23 is closed in a state where the opening 22 is attached to the skin 92 of the specimen 91. The closed spatial structure formed by the cavity 23 in this way is sometimes referred to as “Closed Cavity”.

  The signal processing unit 41 performs signal processing on the pulsation signal output from each sensor 31 of the pulsation signal detection unit array 12, and includes a signal correction unit 51, a frequency demodulation unit 61, and a blood vessel information detection unit 71. Have.

  The signal correction unit 51 performs a frequency correction process on the pulsation signal output from each sensor 31 of the pulsation signal detection unit array 12, thereby at least among the pulsation volume signal, the pulsation velocity signal, and the pulsation acceleration signal. One signal is taken out.

  The frequency demodulating unit 61 performs a frequency demodulating process on the pulsating signal output from each sensor 31 of the pulsating signal detection unit array 12 or the signal subjected to the frequency correcting process by the signal correcting unit 51, thereby generating a pulsating signal. A respiratory signal included in the signal subjected to frequency correction processing by the output or signal correction unit 51 is extracted.

The blood vessel information detection unit 71 receives the pulsation signal output from each sensor 31 of the pulsation signal detection unit array 12, and obtains the depth information of the blood vessel by performing necessary calculations described later.
Here, the depth information of the blood vessel is a depth (distance) from the surface of the skin 92 of the specimen 91 to the blood vessel 93.

  The sample information processing apparatus 1 is connected to an external computer 81 and a waveform display 82 via a wired or wireless line.

  The computer 81 receives the signal processed by the signal processing unit 41 and processes or stores the signal. The computer 81 can diagnose the health state of the specimen 91 from the waveform of each signal using the pulsating volume signal, the pulsating velocity signal, or the pulsating acceleration signal extracted by the signal correction unit 51. The computer 81 can also use the respiratory signal extracted by the frequency demodulator 61 to examine the respiratory state of the sample 91 and determine the sleep or wakefulness state of the sample 91. Further, the computer 81 can use the blood vessel depth information obtained by the blood vessel information detection unit 71 and position information described later as information for confirming the distribution state of the blood vessels 93 and information at the time of blood vessel puncture. .

  The waveform display unit 82 receives the signal output from the signal processing unit 41 and displays the signal waveform. When the pulsating volume signal, the pulsating velocity signal, or the pulsating acceleration signal is output from the signal correction unit 51 of the signal processing unit 41 to the waveform display unit 82, the waveform display unit 82 displays the pulsating volume signal and the pulsating velocity unit. The waveform of the signal or pulsation acceleration signal is displayed. When the respiratory signal is output from the frequency demodulation unit 61 of the signal processing unit 41 to the waveform display unit 82, the waveform display unit 82 displays the waveform of the respiratory signal. In addition, the waveform of the pulsation signal that has been amplified by the signal correction unit 51 of the signal processing unit 41 for the pulsation signal from the sensor 31 is displayed. As the waveform display 82, for example, a liquid crystal display, a CRT, a printer, or a pen recorder can be used.

  The sample information processing apparatus (hereinafter also referred to as the present apparatus) 1 is configured as described above, and each pulsation property is obtained by bringing the opening portion 22 of each pulsation signal detection unit 11 into close contact with the sample 91. A space structure (closed cavity) in which the cavity 23 is closed for each signal detection unit 11 is formed, and pressure information resulting from a pulsation signal of the blood vessel 93 existing in the vicinity of the mounting site of the sample information processing apparatus 1 in the sample 91 is obtained. In response, the sensor 31 of each pulsation signal detection unit 11 constituting the pulsation signal detection unit array 12 detects the pulsation signal of the blood vessel 93 in the specimen 91, and from this pulsation signal output, the blood vessel depth information is detected. Is what you want. It is also possible to extract at least one signal from a pulsating volume signal, a pulsating velocity signal, and a pulsating acceleration signal from the pulsating signal output. It is also possible to extract a respiration signal included in the pulsation signal output.

<Sample>
The sample 91 to which the present sample information processing apparatus 1 is applied is not particularly limited as long as it can measure the pulsation of the arterial blood vessel 93 in the sample 91, and can be used for humans or animals other than humans. In order for the cavity 23 to form a closed cavity by causing the opening 22 of the sensor attachment portion 21 to face and closely contact the sample 91, the sample information processing apparatus 1 is preferably attached to the skin 92 of the sample 91.

  As the wearing position of the sample information processing apparatus 1, in the case of a person, the forearm is preferable because it is easy to wear, easy to measure, and has arterial blood vessels near the body surface and can be measured with high sensitivity. . For animals other than human beings, the mounting location is preferably a site considering the ease of mounting and the ease of measurement.

  In the case of detecting a human pulsation signal using the sample information processing apparatus 1, examples of the blood vessel 93 to be measured include a radial artery or an ulnar artery present in the forearm.

<Aperture diameter>
FIG. 7 is a diagram showing the signal strength when the sensor mounting portion 21 measures the pulsation signal of the capillary blood vessel of the fingertip while changing the diameter of the opening 22.

  As is clear from FIG. 7, a signal can be measured when the diameter of the opening 22 is 1 to 3 mm, but a sufficient gain is not obtained. It can be seen that the gain increases when the diameter of the opening 22 is 3 mm or more, and the pulsation signal can be measured with a high gain when the diameter of the opening 22 is 5 mm to 6 mm. This is thought to be due to the fact that when the aperture 22 is smaller than 2 mm, the area for capturing the signal from the blood vessel 93 is narrowed, so that the detected signal is weakened. .

  If the diameter of the opening 22 is too large (for example, the diameter is larger than 10 mm), when the sample information processing apparatus 1 is attached to the sample 91, the tissue (skin, hair, etc.) on the surface of the sample 91 rises and the cavity 23 rises. By entering, there is a possibility that the pressure information take-in portion 32 is blocked by the tissue, or the tissue interferes with the sensor element 33. In addition, if the aperture 22 is too large, it is difficult for the cavity 23 to form a closed cavity when the sample information processing apparatus 1 is attached so as to be in close contact with the three-dimensional shape of the sample 91. There is a case. In addition, even when the sample information processing apparatus 1 is mounted in a location where the area of the sample 91 is small, it may be difficult to form the closed cavity of the cavity 23 when the sample information processing apparatus 1 is mounted. In addition, when the height of the cavity 23 is constant, the volume of the cavity 23 increases as the diameter of the opening 22 of the cavity 23 increases. When the strength of the pulsation signal is constant, the volume of the cavity 23 is increased. Since the vibration due to the pulsation signal of the blood vessel 93 is attenuated by the increase, the intensity of the signal detected by the sensor 31 may be reduced. If the diameter of the opening 22 is too wide, the pulsation signal of the blood vessel 93 can be detected even when the sample information processing apparatus 1 does not exist directly above the blood vessel 93. Therefore, the directivity of the sensor 31 is increased. May decrease.

  For this reason, the aperture 22 has a diameter of usually 3 mm or more, preferably 6 mm or more, and usually 10 mm or less, preferably 8 mm or less. When the lower limit of the diameter of the opening 22 is larger than the value in the above range, the detected pulsation signal becomes strong, and the opening 22 is brought into close contact with a position where vibration from the blood vessel 93 can be detected when the sample is attached to the specimen 91. It is preferable because it becomes easy. It is preferable that the upper limit of the diameter of the opening 22 is smaller than the above range because the influence of the specimen 91 entering the opening 22 can be suppressed, sensitivity can be maintained, and the directivity of the sensor 31 can be provided.

  In addition, since the diameter of arterial blood vessels (radial artery and ulnar artery) at the wrist of a human adult is about 2 mm, when the opening 22 of the sample information processing apparatus 1 is attached to the wrist of a person, the artery From the viewpoint of detecting the pulsation signal from the blood vessel 93 with high sensitivity by the sensor 31, the diameter of the opening 22 is preferably not less than 2 times and not more than 4 to 5 times the diameter of the arterial blood vessel 93. When the lower limit of the diameter of the opening 22 is larger than the value in the above range, the detected pulsation signal becomes strong, and the opening 22 is brought into close contact with a position where vibration from the blood vessel 93 can be detected when attached to the specimen 91. This is preferable because it becomes easier. Since the upper limit of the diameter of the opening 22 is smaller than the value in the above range, the influence of the sample 91 entering the opening 22 is suppressed, the decrease in sensitivity due to the increase in the volume of the cavity 23 is prevented, and the directivity of the sensor 31 is maintained. This is preferable.

<Material for forming the closed cavity>
Here, the O-ring 24 made of rubber is used as a material for forming the closed cavity. However, any material that can form the cavity 23 for confining the pulsation signal in the specimen 91 is made of a resin or metal material. Even a thing can be used. In order to form the closed cavity of the cavity 23, a material having high rigidity is desirable. However, in consideration of the characteristics (flexibility) of the skin of the human body, the affinity with the skin 92 made of rubber, silicon, etc. Is preferably used.

  Further, when the plurality of pulsation signal detection units 11 are arranged in parallel and the opening 22 of each pulsation signal detection unit 11 is in contact with the skin 92 of the sample 91, even if there are undulations or irregularities on the sample 91, In view of enabling all the cavities 23 of the plurality of pulsating signal detection units 11 to form closed cavities, the material forming the closed cavities is rich in flexibility or elasticity such as rubber or silicon. A material is preferred.

<Sensor>
The sensor 31 is not particularly limited as long as it detects a pulsation signal of the blood vessel 93, but the vibration (sound pressure information) of the air generated by the vibration of the skin 92 of the specimen caused by the pulsation of the blood vessel 93 is electrically detected. It is possible to suitably use a microphone for detection. Among the microphones, a condenser microphone is preferable from the viewpoint of directivity, S / N ratio, and sensitivity, and an ECM (electret condenser microphone; hereinafter, also simply referred to as “ECM”) can be suitably used. In addition, a MEMS type ECM (hereinafter also referred to as “MEMS-ECM”), which is an ECM manufactured using a MEMS (microelectromechanical system) technique, can be suitably used.

  Here, the configuration in which one sensor 31 is provided in each pulsation signal detection unit 11 is described, but from the viewpoint of improving the strength of the detected pulsation signal and increasing the S / N ratio, A pulsation signal in each pulsation signal detection unit 11 is preferably obtained by providing two or more sensors 31 in one pulsation signal detection unit 11 and adding the signals of the sensors 31. When the plurality of sensors 31 are provided in the pulsation signal detection unit 11, the MEMS-ECM is preferable because it is easy to mount because the size is small, and the diameter of the opening 22 can be prevented from becoming too large. In addition, since the quality of the MEMS-ECM is stable, it is preferable because a stable signal can be obtained even when many sensors are connected in parallel and the signals of the sensors 31 are added.

<Arrangement of pulsation signal detection unit>
In FIG. 1, the configuration in which the pulsation signal detection unit array 12 is configured by arranging three pulsation signal detection units 11 is described. However, the number of pulsation signal detection units 11 is two or more (a plurality of pulsation signal detection units 11). ) As long as it is not limited. In order to improve the accuracy of obtaining blood vessel depth information, it is preferable to arrange at least three pulsating signal detection units 11. If the number of the pulsating signal detection units 11 is too large, the handling of the pulsating signal detection unit array 12 becomes poor, and the cost for providing the pulsating signal detection units 11 may become a problem. In addition, all the cavities 23 of the plurality of pulsating signal detection units 11 may not be able to form a closed cavity.

  The pulsation signal detection unit 11 receives a pulsation signal detected by the sensor 31 of each pulsation signal detection unit 11 and performs a calculation to obtain blood vessel depth information. The detection units 11 are preferably arranged in parallel. In other words, it is preferable that the central axis of the pulsation signal detection unit 11 passing through the center of the opening 22 of the pulsation signal detection unit 11 vertically is parallel between the plurality of pulsation signal detection units 11. It is preferable that the openings 22 of the plurality of pulsation signal detection units 11 face the same direction, and the heights of the openings 22 of the plurality of pulsation signal detection units 11 are substantially the same.

  The plurality of pulsating signal detection units 11 are preferably arranged so as to be positioned on a substantially straight line. Further, the plurality of pulsation signal detection units 11 are preferably arranged close to each other, and more preferably, the pulsation signal detection units 11 are connected and brought into close contact with each other.

  When three or more pulsation signal detection units 11 are arranged, one pulsation signal detection unit 11 is a central pulsation signal detection unit, and two or more pulsation signal units are central pulsation signal units. It is preferable that they are arranged equidistant from each other.

  The plurality of pulsating signal detection units 11 are preferably arranged so that the openings 22 have substantially the same height, but when the opening 22 of each pulsating signal detection unit 11 is in contact with the skin 92 of the specimen 91. The relative height relationship between the individual pulsation signal detection units 11 is such that the cavities 23 of each pulsation signal detection unit 11 can form a closed cavity even if there are undulations or irregularities on the sample 91. It may be configured to vary depending on the undulations and irregularities.

[1-2. Functional configuration of sample information processing apparatus]
<Functional configuration of sample information processing apparatus>
When the sample information processing apparatus 1 is functionally represented, the sample information processing apparatus 1 includes a pulsation signal detection unit array 12 and a signal processing unit 41 as shown in FIGS. Here, the sample information processing apparatus 1 includes three pulsation signal detection units 11a, 11b, and 11c, and the pulsation signal detection unit array 12 is configured by the three pulsation signal detection units 11a, 11b, and 11c. Yes. The signal processing unit 41 includes a signal correction unit 51, a frequency demodulation unit 61, and a blood vessel information detection unit 71.

  As described above, the pulsation signal detection units 11a, 11b, and 11c receive pressure information resulting from the pulsation signal of the blood vessel 93 in the sample 91 by the sensor 31, and detect the pulsation signal of the blood vessel 93 in the sample 91. This pulsation signal is output.

  As described above, the signal correction unit 51 performs frequency correction processing on the pulsation signal output from each of the sensors 31a, 31b, and 31c of the pulsation signal detection unit array 12, thereby causing the pulsation volume signal, the pulsation velocity signal, And one of the pulsating acceleration signals is extracted. The process of extracting one of the pulsating volume signal, the pulsating speed signal, and the pulsating acceleration signal by the signal correction unit 51 is also referred to as a correction process.

  The signal correction unit 51 performs at least one of an amplification operation, an integration operation, and a differentiation operation at a frequency of the pulsation signal, so that at least the pulsation volume signal, the pulsation velocity signal, and the pulsation property are obtained. One of the acceleration signals is taken out.

  The signal correction unit 51 may correct the pulsation signal from each sensor 31 of the pulsation signal detection unit array 12 with respect to the pulsation signal from the sensor 31 of one pulsation signal detection unit 11. Correction processing may be performed on the pulsation signal from the sensor 31 of the pulsation signal detection unit 11.

  When correction processing is performed on the pulsation signal from the sensor 31 of one pulsation signal detection unit 11, the intensity of the pulsation signal from the sensor 31 of each pulsation signal detection unit 11 is compared, and the signal is the most. It is preferable to use a strong pulsation signal for the correction process. The closer the pulsation signal detection unit 11 is to the blood vessel 93, the stronger the pulsation signal, and the stronger the signal, the better the S / N ratio of the pulsation signal. The accuracy of one of the pulsating volume signal, the pulsating velocity signal, and the pulsating acceleration signal obtained by the correction process can be improved.

  When correction processing is performed on the pulsation signals from the sensors 31 of the plurality of pulsation signal detection units 11, the strength of the pulsation signals from the pulsation signal detection units 11 is added, and the added pulsation signals are obtained. It is preferable to use for correction processing. By adding the pulsation signals from the plurality of pulsation signal detection units 11, the S / N ratio of the pulsation signal can be increased, and the pulsation volume signal, the pulsation velocity signal, and the pulsation obtained by the correction processing The accuracy of one of the sexual acceleration signals can be improved.

  The frequency demodulator 61 extracts a respiratory signal included as a modulation component in the pulsating signal by frequency demodulation processing using, for example, a phase-locked loop (hereinafter also referred to as “PLL”). The process of extracting the respiratory signal by the frequency demodulator 61 is also referred to as an extraction process.

  The frequency demodulator 61 may perform extraction processing on the pulsation signals from the sensors 31 of one pulsation signal detection unit 11 for the pulsation signals from the plurality of pulsation signal detection units 11. You may perform an extraction process about the pulsation signal from the sensor 31 of the signal detection unit 11. FIG.

  When extracting the pulsation signal from the sensor 31 of one pulsation signal detection unit 11, the strength of the pulsation signal from the sensor 31 of each pulsation signal detection unit 11 is compared, and the signal is the most. It is preferable to use a strong pulsating signal for the extraction process. The closer the pulsation signal detection unit 11 is to the blood vessel 93, the stronger the pulsation signal, and the stronger the signal, the better the S / N ratio of the pulsation signal. For this reason, the accuracy of the respiration signal obtained by the extraction process can be improved by using the pulsation signal having a strong signal for the extraction process.

  When performing extraction processing on the pulsation signals from the sensors 31 of the plurality of pulsation signal detection units 11, the strengths of the pulsation signals from the sensors 31 of the pulsation signal detection units 11 are added, and the added pulsation The sex signal is preferably subjected to an extraction process. By adding the pulsation signals from the sensors 31 of the plurality of pulsation signal detection units 11, the S / N ratio of the pulsation signal can be increased, and the accuracy of the respiratory signal obtained by the extraction process can be improved. it can.

  As shown in FIG. 2, the extraction of the respiratory signal in the sample information processing apparatus 1 is performed by directly demodulating the pulsation signal output from each sensor 31 of the pulsation signal detection unit array 12 without using the signal correction unit 51. The unit 61 may perform frequency demodulation processing.

  Alternatively, in the extraction of the respiratory signal in the sample information processing apparatus 1, as shown in FIG. 3, the pulsation signal output from each sensor 31 of the pulsation signal detection unit array 12 is subjected to frequency correction processing in the signal correction unit 51. After that, the frequency demodulation unit 61 may be configured to perform frequency demodulation processing on any one of the pulsating volume signal, the pulsating velocity signal, and the pulsating acceleration signal after the correction processing.

  As described above, the blood vessel information detection unit 71 receives the pulsation signal output from each sensor 31 of the pulsation signal detection unit array 12 and performs a required calculation to obtain the depth information of the blood vessel. .

<Functional configuration of frequency demodulator>
When the frequency demodulator 61 is functionally represented, the frequency demodulator 61 includes a phase comparator 151, a low-pass filter 152, a VCO (Voltage Controlled Oscillator) 153, and a frequency divider 154 as shown in FIG. I have.

The frequency demodulation process is a process of extracting a respiratory signal included in the pulsation signal by comparing two signals whose phases are synchronized by a PLL. As an example, as shown in FIG. 8, in the frequency demodulator 61, a pulsation signal is input to the phase comparator 151, the output from the phase comparator 151 is input to the low-pass filter 152, and the oscillation frequency of the VCO 153 is output as the output. Is divided by the frequency divider 154 and returned to the phase comparator 151 to synchronize these two signals, whereby the output waveform of the low-pass filter 152 can be obtained as a respiratory component.
That is, the respiratory component can be extracted from the pulsating signal by performing demodulation processing on the pulsating signal in which the respiratory component of the specimen is modulated.

[1-3. Operation of specimen information processing apparatus]
<Extraction of respiratory signal>
The operation of the sample information processing apparatus 1 will be described with reference to the flowcharts shown in FIGS.

  In the sample information processing apparatus 1 having the functional configuration shown in FIG. 2, first, as shown in FIG. 4, a pulsation signal is detected by each sensor 31 of the pulsation signal detection unit array 12 (step S11).

  Next, the frequency demodulator 61 performs frequency demodulation processing on the pulsation signal output detected by each sensor 31 of the pulsation signal detection unit array 12 (step S12), and the respiratory signal included in the pulsation signal output is output. Extract (step S13).

  At this time, there is a step of comparing the strength of the pulsating signal output obtained from each sensor 31 of the plurality of pulsating signal signal detection units 11 between step S11 and step S12, and the pulsation with the strongest signal. For the output of the sex signal, the frequency demodulation processing may be performed in step S12.

  Moreover, it has the step which adds the pulsation signal output obtained from each sensor 31 of the several pulsation signal signal detection unit 11 between step S11 and step S12, and is a step about the added pulsation signal output. You may make it perform a frequency demodulation process by S12.

  Further, in the sample information processing apparatus 1 having the functional configuration shown in FIG. 3, first, as shown in FIG. 5, a pulsation signal is detected by each sensor 31 of the pulsation signal detection unit array 12 (step S21). Next, the signal correction unit 51 of the signal processing unit 41 performs frequency correction processing on the pulsation signal output detected by each sensor 31 of the pulsation signal detection unit array 12 (step S22), and the pulsation volume signal, One of the pulsating velocity signal and the pulsating acceleration signal is extracted (step S23). The frequency demodulation unit 61 of the signal processing unit 41 performs frequency demodulation processing on one of these pulsating volume signal, pulsating velocity signal, and pulsating acceleration signal (step S24), and is included in the pulsating signal. A respiration signal is extracted (step S25).

  At this time, there is a step of comparing the strength of the pulsating signal output obtained from each sensor 31 of the plurality of pulsating signal signal detection units 11 between step S21 and step S22, and the pulsation with the strongest signal. For the sex signal output, a frequency correction process may be performed in step S32.

  Moreover, it has the step which adds the pulsation signal output obtained from each sensor 31 of the some pulsation signal signal detection unit 11 between step S21 and step S22, and about the added pulsation signal output, step You may make it perform a frequency correction process by S22.

<Acquisition of blood vessel position information>
Acquisition of blood vessel position information using the sample information processing apparatus 1 of the present invention will be described with reference to the drawings.
Here, the blood vessel position information is information indicating the position of the blood vessel 93 on the skin 92 of the specimen 91 (see FIG. 26). In other words, the information represents the position of the blood vessel existing in the skin 92 of the specimen 91 at a position corresponding to the outer surface of the specimen 91 in the skin 92.

  The pulsation signal detection unit array 12 is installed facing the sample 91, and the pulsation signal is detected on the surface of the skin 92 while changing the position on the sample 91 of the sample information processing apparatus 1. At this time, by checking the waveform of the pulsating signal displayed on the waveform display 82, the output level from the sensor 31 of the pulsating signal detection unit array 12 accompanying the change in the position of the pulsating signal detection unit array 12 can be determined. Can be detected. Furthermore, plotting a position where a heartbeat (pulsation signal) from the sensor 31 of at least one pulsation signal detection unit 11 is strongly detected (a position where the amplitude of the pulse wave waveform as an output level is detected to be large) is plotted. By repeating, the position of the blood vessel 93 can be tracked. In FIG. 6, the pulsation signal detection unit array 12 of the sample information processing apparatus 1 is applied to the palm of the left hand to search for a position where even the velocity component of the pulse wave can be detected, and the pulsation signal detection unit array 12 is located in the vicinity thereof. The graph shows a plot where the amplitude of the velocity pulse wave (the output level of the pulsating signal) is maximized by gradually shifting.

  It is known that an artery exists in the palm of the left hand, and knowledge about the distribution of the artery is obtained. Comparing the distribution of this artery with the distribution of the plot of FIG. 6, it can be seen that the plot of FIG. 6 matches the distribution of the artery, and that the arterial blood vessel can be traced by the plot of FIG. In the plot shown in FIG. 6, although the plot is intermittently obtained and the arterial blood vessel is not completely traced, the sample information processing apparatus 1 can create a two-dimensional map such as a blood vessel distribution. it can.

  That is, as described above, by detecting the output level from at least one of the plurality of sensors 31 that changes as the pulsation signal detection unit array 12 moves, the output level changes. Based on this, it is possible to obtain the position of the blood vessel 93 on the skin 92 (position information of the blood vessel). The higher the output level from the sensor 31, the better the S / N ratio of the signal and the easier it is to acquire the position information of the blood vessel. Therefore, the sensor having the highest output level among the plurality of sensors 31 of the plurality of sensors 31. It is preferable to obtain the position information of the blood vessel based on the change in the output level from.

  As the output level from the sensor 31, the amplitude of the pulse wave waveform of the pulsating signal displayed by the waveform display 82 can be used as described above. As the pulsation signal, any of a volume pulse wave, a velocity pulse wave, or an acceleration pulse wave may be used. Alternatively, in the computer 81, the pulsation signal input from the signal processing unit 41 is processed, and the strength of the pulsation signal is digitized as a value over time accompanying a change in the position of the sample information processing apparatus 1. You may make it compare as an output level of a pulsation signal.

<Calculation of blood vessel depth information>
Calculation of blood vessel depth information using the sample information processing apparatus 1 of the present invention will be described with reference to the drawings.

(Positional relationship between pulsation signal detection unit array and blood vessels)
24 and 25 are diagrams showing the positional relationship between the pulsation signal detection unit array 12 and the blood vessel 93 for obtaining blood vessel depth information. Here, a case where the pulsation signal detection unit array 12 is configured by three pulsation signal detection units 11a, 11b, and 11c will be described. In FIG. 24, a blood vessel 93 is present in the vertical direction of the drawing on the front side of the drawing, and the pulsation signal detection unit array 12 is shown on the back side of the drawing with the sensor mounting portion 21 and the opening 22 facing the front side of the drawing. . That is, FIG. 24 shows the positional relationship between the blood vessel 93 and the pulsating signal detection unit array 12 when viewed in parallel with the skin 92 from the inside of the specimen 91 to the outside. FIG. 25 shows the positional relationship between the blood vessel 93 and the pulsation signal detection unit array 12 when viewed from the cross-sectional direction of the blood vessel 93 extension direction.

  As shown in FIG. 24, in order to obtain blood vessel depth information, a plurality of pulsation signal detection units 11a, 11b, and 11c are arranged so as to be positioned on a straight line, thereby forming a pulsation signal detection unit array 12. It is preferable. The pulsation signal detection unit array 12 is preferably installed so that the pulsation signal detection unit array 12 intersects the blood vessel 93, and the pulsation signal detection unit array 12 is orthogonal to the blood vessel 93. More preferably, the unit array 12 is installed (set).

  As shown in FIG. 25, it is preferable that the heights of the openings 22 of the plurality of pulsating signal detection units 11a, 11b, and 11c are substantially the same. Further, the pulsation signal detection unit array 12 may be installed in the sample 91 at a position where one of the pulsation signal detection units 11 a, 11 b, 11 c of the pulsation signal detection unit array 12 is opposed to the blood vessel 93. preferable. In other words, the pulsation signal detection unit array 12 may be installed on the specimen 91 such that one of the pulsation signal detection units 11 a, 11 b, 11 c of the pulsation signal detection unit array 12 is positioned immediately above the blood vessel 93. preferable. Of the three pulsation signal detection units 11a, 11b, and 11c, the central pulsation signal detection unit 11b is located at a position facing the blood vessel 93, in other words, the three pulsation signal detection units 11a, 11b, and 11c. Among them, it is preferable to install the pulsation signal detection unit array 12 on the specimen 91 so that the central pulsation signal detection unit 11 b is located immediately above the blood vessel 93. Further, the pulsatility is such that the distance from the left and right pulsation signal detection units 11a, 11c to the central pulsation signal detection unit 11b is equal, and the distance from the left and right pulsation signal detection units 11a, 11c to the blood vessel 93 is equal. It is preferable to install the signal detection unit array 12 on the specimen 91. Further, the pulsation signal detection units 11a and 11b are set so that the angle formed by the blood vessel 93, the central pulsation signal detection unit 11b, and either the left or right pulsation signal detection unit 11a or 11c is approximately 90 degrees. 11c and the pulsation signal detection unit array 12 are preferably installed, and the line connecting the blood vessel 93 and the left and right pulsation signal detection units 11a and 11c is set to two sides having the same length. It is preferable to install the pulsation signal detection units 11a, 11b, 11c and the pulsation signal detection unit array 12 so as to have an equilateral triangular positional relationship.

  In the case of the distance from the left and right pulsation signal detection units 11a and 11c to the central pulsation signal detection unit 11b, the central pulsation signal is transmitted from the center of each opening 22 of the left and right pulsation signal detection units 11a and 11c. It can be regarded as the distance to the center of the opening 22 of the detection unit 11b.

  The vibration caused by the pulsation signal of the blood vessel 93 propagates through the skin 92 of the specimen 91 to reach the surface of the skin 92, and vibrates the epidermis of the skin 92. The vibration generated on the surface of the epidermis of the skin 92 causes the air in the vicinity of the opening 22 of the pulsating signal detection units 11a, 11b, and 11c to vibrate and propagates to the air inside the cavity 23. The vibration of the air inside the cavity 23 causes the air chamber 34 inside the sensor 31 to vibrate through the pressure information take-in portion 32, and the sensor element 33 detects the vibration of the air chamber 34. Pressure information resulting from the signal can be detected. Here, the vibration caused by the pulsation signal of the blood vessel 93 attenuates according to the distance from the blood vessel 93 when propagating through the skin 92 of the specimen 91, whereas the vibration generated on the surface of the epidermis of the skin 92 is Since the cavity 23 forms a closed cavity, the attenuation in the cavity 23 and the air chamber 34 is considered to be small. Therefore, the sensor 31 can detect vibration equivalent to vibration generated on the surface of the skin 92 of the skin 92. Therefore, in the case of the distance from the blood vessel 93 to the pulsation signal detection units 13 to 15, the distance from the blood vessel 93 to the center of the opening 22 or the distance from the blood vessel 93 to the surface of the epidermis of the skin 92 inside the cavity 23. Can be considered.

(Determination of installation position of pulsation signal detection unit array)
As described in the above-described acquisition of the blood vessel position information, the output level from at least one of the plurality of sensors 31 that changes with the movement of the pulsation signal detection unit array 12 is detected. The position of blood vessel 93 on skin 92 (blood vessel position information) can be obtained based on the change in the output level. Points 2 to 5 shown in FIG. 26 represent points indicating the position information of the blood vessel obtained by determining the position information of the blood vessel and tracking the blood vessel 93 as described above. From the position information of blood vessels arranged like points 2 to 5, it can be seen that the blood vessels 93 exist on the line connecting the points.

  Here, as shown in FIG. 26, in the pulsating signal detection unit array 12 having the three pulsating signal detection units 11a, 11b, and 11c, the central pulsation signal detection unit 11b connects points 2 to 4. The pulsation signal detection unit array 12 is installed so as to be located at a point M on the line, and the left and right pulsation signal detection units 11a and 11c are connected to the left and right pulsation signal detection units 11a and 11c, respectively. To the pulsating signal detection unit array 12 so as to be located at the points L and N where the distances to the lines connecting .about.4 are equal, the blood vessel 93 and the pulsating signal detection as shown in FIGS. The pulsation signal detection unit array 12 can be installed so as to be in a positional relationship between the unit array 12 and the pulsation signal detection units 11a, 11b, and 11c. That.

  In order to confirm whether or not the central pulsation signal detection unit 11b of the pulsation signal detection unit array 12 is in a position facing the blood vessel 93, the waveform of the pulsation signal displayed by the waveform display 82 is confirmed. Thus, it is only necessary to detect the output level of each sensor 31 of the pulsation signal detection unit array 12 that accompanies a change in the position of the pulsation signal detection unit array 12.

  One method for confirming whether or not the central pulsation signal detection unit 11b is at a position facing the blood vessel 93 is to check the pulsation waveform of the pulsation signal from the sensor 31b of the central pulsation signal detection unit 11b. However, the pulsation signal detection unit array 12 is moved so as to cross the line connecting points 2 to 5 in FIG. 26, and the output level (amplitude) of the pulsation signal that changes as the pulsation signal detection unit array 12 moves. ) Is detected as shown in FIG. 27B, and it can be determined that the central pulsation signal detection unit 11b is at a position facing the blood vessel 93 at the point where the amplitude of the pulsation signal is maximized. .

  As another method for confirming whether or not the central pulsation signal detection unit 11b is at a position opposite to the blood vessel 93, the distance from the central pulsation signal detection unit 11 to the left and right pulsation signal detection units 11a and 11c. Are equal, the pulsation is made so as to cross the line connecting points 2 to 5 in FIG. 26 while checking the pulsation waveform of the pulsation signal from the sensors 31a and 31c of the left and right pulsation signal detection units 11a and 11c. 27A to 27C, the output level (amplitude) of the pulsation signal that changes with the movement of the pulsation signal detection unit array 12 is detected, and the results are shown in FIGS. As described above, the amplitude of the pulsating waveform of the pulsating signal from the sensors 31a and 31c of the left and right pulsating signal detection units 11a and 11c, that is, the strength of the pulsating signal. In that the output level) is comparable, it can be determined to be in a position where the center of the pulsating signal detection unit 11b faces the vessel 93.

  As the output level from the sensor 31, the amplitude of the pulse wave waveform of the pulsating signal displayed by the waveform display 82 can be used as described above. As the pulsation signal, any of a volume pulse wave, a velocity pulse wave, or an acceleration pulse wave may be used. Alternatively, in the computer 81, the pulsation signal input from the signal processing unit 41 is processed, and the strength of the pulsation signal is digitized as a value over time accompanying a change in the position of the sample information processing apparatus 1. You may make it compare as an output level of a pulsation signal.

(Calculation of blood vessel depth information)
24 and 25, a plurality of pulsation signal detection units 11a, 11b, and 11c are installed so as to be positioned on a substantially straight line, and the central pulsation signal detection unit 11b faces the blood vessel 93. The angle between the blood vessel 93, the central pulsation signal detection unit 11b, and the left or right pulsation signal detection unit 11a or 11c is at a position of approximately 90 degrees, and the central pulsation blood vessel 93 And the right and left pulsation signal detection units 11a and 11c are positioned at an isosceles triangle with two sides having the same length. From the central mobility signal detection unit 11b, When the distance to the sex signal detection units 11a and 11c is equal, the relationship between the blood vessel 93 and each of the pulsation signal detection units 11a, 11b, and 11c is schematically illustrated. It can be represented as 28. In FIG. 28, a represents the distance from the central pulsation signal detection unit 11b to the left and right pulsation signal detection units 11a and 11c, and x represents the distance from the central pulsation signal detection unit 11b to the blood vessel 93 (ie, , The depth from the surface of the skin 92 to the blood vessel 93), and y represents the distance from the left and right pulsating signal detection units 11a, 11c to the blood vessel 93.

When the angle formed by the blood vessel 93, the central pulsation signal detection unit 11b, and either the left or right pulsation signal detection unit 11a or 11c is at a position of approximately 90 degrees, the left and right pulsation properties are determined from the Pythagorean theorem. The distance y from the signal detection units 11a and 11c to the blood vessel 93 can be expressed by the following equation (1).
y = SQRT (a ² + x ² ) (1)
Here, the pulsation V in the blood vessel 93 can be expressed by the following formula (2) with the time t as a variable.
V = Asin (ωt) (2)
(In the above formula (2), A represents the amplitude A of the pulsation of the blood vessel 93, and ω represents the angular frequency of the pulsation of the blood vessel 93.)

At this time, the pulsation M detected by the central pulsation signal detection unit 11b is expressed by the following equation (3), and the pulsation S detected by the left and right pulsation signal detection units 11a and 11c is expressed by the following equation (4). Let's say.
M = Bsin (ωt + p) (3)
S = Csin (ωt + q) (4)
(In the above equation (3), B represents the amplitude of the pulsation detected in the central pulsation signal detection unit 11b, ω represents the angular frequency of the pulsation detected in the central pulsation signal detection unit 11b, p represents a time delay from the pulsation of the blood vessel 93 detected by the central pulsation signal detection unit 11b, where C is detected by the left and right pulsation signal detection units 11a and 11c. The pulsation amplitude is represented, ω represents the angular frequency of the pulsation detected in the left and right pulsation signal detection units 11a and 11c, and q represents the pulsation blood vessel 93 detected in the left and right pulsation signal detection units 11a and 11c. Represents the time delay from the pulsation of

It is considered that the amplitude of pulsation is inversely proportional to the distance from the blood vessel 93. Further, by setting C / B = β, the following equation (5) is derived from the equations (1) to (4).
x = a × β / SQRT (1-β ² ) (5)

  From the equation (5) derived by the above procedure, the distance x from the central pulsation signal detection unit 11b to the blood vessel 93 is determined from the central pulsation signal detection unit 11b to the left and right pulsation signal detection units 11a and 11c. , The pulsation amplitude B detected by the sensor 31b of the central pulsation signal detection unit 11b, and the pulsation amplitude C detected by the sensors 31a, 31c of the left and right pulsation signal detection units 11a, 11c. It can be seen that it can be calculated from For this reason, in the blood vessel information detection unit 71, blood vessel depth information can be obtained by performing calculation using Expression (5).

  Here, the distance a from the central pulsation signal detection unit 11b to the left and right pulsation signal detection units 11a and 11c is the distance between the pulsation signal detection unit 11a and the pulsation signal detection unit 11b and the pulsation signal. By configuring the pulsation signal detection unit array 12 with a constant distance between the detection unit 11a and the pulsation signal detection unit 11b, it can be regarded as a constant. For this reason, the distance (blood vessel depth information) x from the central pulsation signal detection unit 11b to the blood vessel 93 is equal to the amplitude B of the pulsation detected by the sensor 31b of the central pulsation signal detection unit 11b and the left and right The pulsation amplitude C detected by the sensors 31a and 31c of the pulsation signal detection units 11a and 11c can be calculated by substituting into the equation (5).

[1-4. Specimen information processing method]
The sample information processing method of the present invention (hereinafter also referred to as the present sample information processing method) receives pressure information resulting from the pulsation signal of the blood vessel 93 in the sample 91, and the pulsation of the blood vessel 93 in the sample 91 described above. A sensor 21 that detects a signal, a cavity 23 that communicates with a pressure information capturing unit of the sensor 21, and an opening 22 that has a diameter of 3 mm to 10 mm at a portion that faces the sample 91. A pulsating signal constituted by arranging a plurality of pulsating signal detection units 11 in parallel with a sensor mounting part 31 having a spatial structure in which the cavity 23 is closed in a state of being mounted on the specimen 91 so as to face the surface. The detection unit array 12 is prepared, the pulsation signal detection unit array 12 is installed in a direction crossing the blood vessel 93, and the pulsation signal detection unit described above is provided. The pulsation signal detection unit array 12 is installed so that one pulsation signal detection unit 11 of the rays 12 faces the blood vessel 93, and thereafter, from each sensor 31 of the pulsation signal detection unit array 12. The depth information of the blood vessel 93 is obtained by performing the required calculation in response to the above output.

  Further, in this specimen information processing method, for example, when the pulsation signal detection unit array 12 includes three pulsation signal detection units 11a, 11b, and 11c, as shown in FIGS. The intensity of the pulsation signal output from the sensor 31b of the pulsation signal detection unit 11b at a position facing the blood vessel 93 of the detection unit array 12 and the other pulsation signal detection units 11a and 11c of the pulsation signal detection unit array 11 are detected. From the strength of the pulsating signal output from the sensors 31a and 31c and the distance between the pulsating signal detection unit 11b at the position facing the blood vessel 93 of the pulsating signal detection unit array 12 and the other pulsating signal detection units 11a and 11c. The depth information of the blood vessel 93 is obtained.

  In addition, the sample information processing method of the present invention detects an output level from at least one of the plurality of sensors 31 that changes as the pulsation signal detection unit array 12 moves, and changes the output level. The position information of the blood vessel 93 is obtained based on the above.

[1-5. effect]
According to the sample information processing apparatus 1 of the present invention and the sample information processing method of the present invention, by performing a required calculation on the pulsation signal output from each sensor 31 of the pulsation signal detection unit array 12, Depth information can be determined.

  Further, according to the sample information processing apparatus 1 and the sample information processing method, at least one of the plurality of sensors 31 of the pulsation signal detection unit array 12 that changes as the pulsation signal detection unit array 12 moves. The position information of the blood vessel can be obtained based on the change in the output level from the two sensors 31.

  Further, according to the sample information processing apparatus 1 and the sample information processing method, the pressure information of the sensor 31 is captured by mounting the opening 22 of the sample information processing apparatus 1 on the blood vessel 93. Even if the part 32 is not directly above the blood vessel 93, the pulsation signal of the blood vessel 93 can be detected. That is, the sample information processing apparatus 1 and the sample information processing method having a mechanism that does not require the accuracy of the positional relationship between the sensor 31 and the blood vessel 93 can be provided, and the acquisition of the blood vessel position information and the calculation of the blood vessel depth information are provided. Can be carried out simply and quickly.

  Further, in the sample information processing apparatus 1 and the sample information processing method, the cavity 23 is formed between the sensor 31 and the skin 92 of the sample 91 by causing the opening 22 to face the sample 91 when detecting the pulsation signal. A closed cavity is formed. In the pulsation signal detection unit 11 of the present invention, the diameter of the opening 22 is limited to a predetermined size. Therefore, the range of pressure information received by the opening 22 is limited, and the sensing of the sensor 31 as a pressure sensor is limited. The range is narrow and limited. Thus, it is possible to provide the sample information processing apparatus 1 and the sample information processing method having higher directivity (or spatial resolution) than when sensing in an open system using another sensor such as a piezoelectric element or a microphone. It is possible to improve the accuracy of obtaining blood vessel position information and calculating blood vessel depth information.

  In the sample information processing apparatus 1 and the sample information processing method, the pulsatility signal is detected at a position close to the blood vessel 93 by using the directivity of the pulsation signal detection unit 11 of the present invention. The S / N ratio and sensitivity of the signal can be improved, the S / N ratio and sensitivity of the respiratory signal extracted from the pulsation signal are also improved, the acquisition of the blood vessel position information, and the blood vessel depth information The calculation accuracy can be improved.

Further, according to the sample information processing apparatus 1 and the sample information processing method, by performing frequency correction processing on the pulsating signal, at least one of the pulsating volume signal, the pulsating velocity signal, and the pulsating acceleration signal is obtained. The signal can be extracted.
Moreover, according to the sample information processing apparatus 1 and the present sample information processing method, the respiratory signal included in the pulsation signal output can be extracted by performing frequency demodulation processing.

[2. About ECM and MEMS-ECM]
Regarding the sensor used in the sensor 31 of the sample information processing apparatus 1, first, the relationship between the closed cavity of the microphone and the frequency response will be described, and then ECM and MEMS-ECM, and detection of pulsating signals using them will be described. The frequency characteristics and frequency correction processing will be described.

[2-1. Closed cavity and frequency response]
The sample information processing apparatus 1 does not measure the vibration of the pulsating signal of the blood vessel 93 in the open state (open system) by the sensor 31, but in the relationship between the sensor 31 and the vibration source, the air chamber 34 of the sensor 31. Measured in such a manner that the cavity 23 communicating with the sensor forms a closed space structure (closed cavity), that is, the sensor 31 and the vibration source are closed.
In order to explain this, the difference in frequency response between the open state and the closed state of the sensor (microphone) will be described.

In detecting the pulsation signal of the blood vessel 93 in the specimen 91, vibration originating from the movement of the heart can be captured from anywhere in the specimen 91. However, the amplitude of the movement is extremely small, and it is difficult to detect vibration originating from the movement of the heart even if a microphone or the like that can sense pressure is placed near the human body. In the case it was the sensor in an open state, once vibrations emitted into the space on the principle of sound radiation, as shown in FIG. 9, the response is peaked at the natural frequency f ₀ of the element, than the natural frequency f ₀ However, it is a constant output in the high frequency region, but follows a so-called -40 dB / dec curve toward the low frequency region, and shows a frequency response that is a very small signal at the fundamental frequency of the heart motion. is there. In a small acoustic device, the natural frequency is supposed to be several kHz, and in the vicinity of 1 Hz such as heart motion, the signal attenuates to −120 dB or less with respect to the amplitude with respect to the high frequency, and the response is low and the sensitivity is sufficient. It is difficult to measure with In FIG. 9, the number of traces is a so-called damping factor difference, and the position of f _{o on} the horizontal axis means the natural frequency.

On the other hand, by creating a closed space at the tip of an element (sensor) that senses this vibration and bringing it into a closed state, the frequency characteristics are changed completely as shown in FIG. The presence of a plurality of traces in FIG. 10 is a difference in so-called damping factor as described above. From FIG. 10, it can be seen that the signal in the low frequency region can be measured with high sensitivity when the closed cavity is formed. This means that even the vibration of the heart near 1 Hz can be detected with the same amplitude and the same amplitude as the vibration near the natural frequency f _{0 as} compared with the frequency response in the open state of FIG. This is considered to be because vibration is not emitted into the air as acoustic energy but is converted into a pressure change in a closed space.

  As described above, the frequency response in the low frequency region can be improved by measuring the sensor (ECM) in a closed state so as to form a closed cavity.

  That is, in this apparatus, pressure information resulting from the pulsation signal of the blood vessel 93 in the sample 91 near 1 Hz, which has been difficult to measure in the past, is received and the pulsation signal of the blood vessel 93 in the sample 91 is detected with high sensitivity. Furthermore, the respiratory signal of the specimen 91 can be extracted from the pulsation signal around 1 Hz.

[2-2. About ECM]
As a pressure change in a closed space (cavity) as described above, a microphone is the most familiar when detecting minute vibrations. Among them, ECM (electret condenser microphone) is particularly suitable for this application. ECM is increasingly applied to mobile phones and the like, not to mention miniaturization and stabilization, but is easy to obtain by mass production.
The ECM is a small microphone that realizes high sensitivity and low voltage drive by fusing an electret film to the diaphragm or fixed electrode of a condenser microphone.

  As shown in FIG. 11, the housing 208 of the ECM 201 has an air hole 202 that communicates with the outside and has a shape like a window. In the air chamber 205 that is an internal space inside the housing 208, A diaphragm 203 and a back plate 204 facing the air hole 202 are provided to face each other. Here, an electret film is used as the diaphragm 203. Electrodes 206 are attached to the diaphragm 203 and the back plate 204 as shown in the figure, and the back plate 204 serves as a fixed electrode, from which a signal can be detected as a change in voltage, and between the diaphragm 203 and the back plate 204. The capacitance (capacitance) can be measured. Further, in order to take out a signal with low impedance, a field effect transistor or a CMOS IC is used as the impedance conversion element. The diameter of the air hole 202 is used for adjusting the pneumatic frequency characteristics, but is generally about 1/3 of the diameter of the housing 208 on the side having the air hole. For example, in the case of a general ECM having a diameter of 6 mm, the diameter of the air hole is about 2 mm. In addition, this air hole is not a single hole, and those having a plurality of smaller air holes are also commercially available.

  When vibration is generated from the vibration source, the vibration of the air in the air chamber 205 transmitted through the air hole 202 acts as a force pushing the diaphragm 203, and the distance between the diaphragm 203 and the back plate 204 changes to change the capacitance (electrostatic capacity). (Capacity) changes.

The ECM 201 always operates by adding a constant charge (Q) between the diaphragm 203 and the back plate 204 during operation. Further, when the distance between the diaphragm 203 and the back plate 204 is (d), and these areas are the same (S), the capacitance (C) of the ECM 201 can be defined by the following equation (6).
C∝S / d (6)
(In the above equation (6), ∝ means proportionality.)

  Meanwhile, from electromagnetism

Q = C × V (7)
Since the relationship of the above equation (7) holds, the voltage (V) detected from the ECM 201 is expressed by the following equation (8) from these equations.
V ∝ Q x d / S (8)

  As is clear from the equation (8), since the charge (Q) and the area (S) are constants that do not change with air pressure, the voltage (V) is proportional to the distance (d) between the diaphragm 203 and the back plate 204. In other words, the air vibration that enters from the air hole 202 in FIG. 11 can be detected in the form of the voltage V.

  In this way, vibration can be measured by converting the capacitance change into voltage. The pressure information resulting from the pulsation signal of the blood vessel 93 in the sample 91 is also transmitted to the skin 92 of the sample 91, and the vibration of the skin 92 causes the air in the cavity 23 to vibrate. Can be detected as

  In FIG. 11, the configuration in which the diaphragm 203 is opposed to the air hole 202 is described. However, the diaphragm 203 and the back plate 204 may be provided in the opposite direction to the air hole 202. That is, the back plate 204 facing the air hole 202 and the diaphragm 203 may be provided to face each other.

  Here, the configuration in which the electret film is used as the diaphragm has been described. However, an ECM in which a DC voltage is applied to the diaphragm from the outside can also be used in the present invention.

[2-3. About MEMS-ECM]
In recent years, ECM is increasingly using a silicon-based diaphragm produced by a semiconductor process as a diaphragm due to a demand for miniaturization. Such an ECM is referred to as a MEMS (microelectromechanical system) -ECM.

  The MEMS-ECM is an ultra-compact ECM that is three-dimensionally finely processed by sub-μm order processing / film formation technology by a semiconductor process, and is generally called a “silicon microphone”. MEMS-ECM is in principle the same as ECM, but is smaller than ECM and adjusts frequency characteristics using space, so the size of air holes (also called sound holes) is less than 1 mm in diameter. Is normal. It is known that MEMS-ECM is not inferior to ordinary ECM and has less variation in quality in terms of sensitivity, S / N, and frequency characteristics.

  As shown in FIG. 12, the MEMS-ECM 211 includes a MEMS chip 212 having a diaphragm and a back plate, and a CMOS (Complementary Metal Oxide Semiconductor) chip 213, which are connected by wire bonding 214. It has become.

  As shown in FIG. 13, the MEMS-ECM 211 is provided with a diaphragm 221 facing the air chamber 223 that is a space inside the MEMS-ECM and a back plate 222, and a capacitance between the diaphragm 221 and the back plate 222 ( (Capacitance) can be measured. Similar to ECM, when vibration is generated from a vibration source, vibration of air in the air chamber 223 transmitted through an air hole (sound hole) (not shown) communicating with the outside vibrates the diaphragm 221, and the diaphragm 221 and the back plate 222 A change in capacitance occurs due to a change in distance. By converting this capacitance change into a voltage, vibration can be measured. The diaphragm 221 and the back plate 222 may be provided so as to face each other with respect to the air hole (sound hole). That is, the back plate 222 may be provided to face the diaphragm 221 facing the air hole (sound hole), or the diaphragm 221 may be provided to face the back plate 222 facing the air hole (sound hole).

  As shown in FIG. 14, the MEMS-ECM includes a MEMS chip portion 231 and a CMOS chip portion 234. Since the CMOS structure amplifier is included for impedance conversion and amplification as in the equivalent circuit of FIG. 14, a change in voltage generated in the diaphragm 232 and the back plate 233 of the MEMS chip portion 231 is caused by the CMOS chip portion 234. The signal is further amplified by the amplifier 235 and output through the buffer 236.

[2-4. Closed cavity formation and pulsation signal detection]
When these ECMs or MEMS-ECMs (sometimes referred to as silicon microphones) are used to capture vibrations of the blood vessels 93 (pulsating signals) caused by the heart, these microphones have frequency characteristics as shown in FIG. Thus, it is desirable to detect the pressure change in a closed space (closed cavity) formed by the cavity. For this purpose, for example, they may be pressed directly against the skin of the human body. In this case, since the space is closed between the air hole and the diaphragm, it is considered that the signal can be detected with the frequency characteristics as shown in FIG.

  However, actually, even if ECM or MEMS-ECM is directly pressed against the specimen 91, it is difficult to obtain a desired signal. The biggest cause seems to be that the diameter of the air hole is too small. For example, in an ECM with an air hole diameter of 2 mm, a signal could be detected only when the air hole came directly above the blood vessel 93. On the other hand, in MEMS-ECM, the signal could hardly be detected because the diameter of the air hole (sound hole) was smaller than that of the blood vessel 93. This is because, when the sensor mounting portion 21 having the opening 22 and the cavity 23 is not provided between the specimen 91 and the sensor 31, a pressure information capturing portion (air hole, sound hole) of the ECM or MEMS-ECM is provided. It is considered that the characteristic that the pulsation signal of the blood vessel 93 immediately below 32 can be detected has an influence. Further, it is considered that the skin tissue or the like enters from the pressure information capturing unit 32 due to the softness of the skin tissue of the specimen 91 and the pressure information capturing unit 32 is blocked.

  Therefore, in the sample information processing apparatus 1, the sensor mounting portion 21 having the opening 22 and the cavity 23 is provided using the O-ring 24 to form a closed cavity, and the pressure information of the cavity 23 and the sensor 31 is captured. By communicating the part 32 and the air chamber 34, it is possible to detect a pulsating signal of the low-frequency blood vessel 93 within the range of the opening 22.

[2-5. Frequency characteristics of ECM and MEMS-ECM]
A common characteristic of current ordinary ECM, MEMS-ECM, and the like is that measures against windbreaks are taken. Microphones such as mobile phones have small holes (several tens of μm) in the diaphragm so that they do not react to wind noise when the wind is strong or sudden pressure changes such as when the user coughs (blows). Is opened. As a result, attenuation in the low frequency is caused in terms of frequency characteristics. Slow air flow is easy to understand given that it passes through the hole in this small diaphragm.

  In addition, in MEMS-ECM in which diaphragm holes are formed by a semiconductor process, holes can be stably formed with the same quality, and the frequency response is more stable between individuals for each MEMS-ECM compared to ECM. It is known that

The sensitivity reduction in the low frequency region is effective in preventing wind noise and blowing in the normal use of the microphone for the audible sound region (20 Hz to). However, since the center frequency of the pulse wave to be detected in the present sample information processing apparatus 1 is about 1 Hz and the frequency of the respiratory signal also appears remarkably in the region of the order of several Hz, this sensitivity reduction in the low frequency region affects detection. It is possible.
Therefore, verification of frequency characteristics using MEMS-ECM will be described.

  As described above, in this sample information processing apparatus 1, it is necessary to verify frequency characteristics in a low frequency region including 1 Hz in order to detect a pulsation signal and extract a respiratory signal. The verification of the frequency characteristics was performed using an apparatus having the configuration shown in FIG.

  As the speaker 403, a dynamic speaker is used, the diaphragm is removed, the cone paper is removed while leaving the voice coil of the speaker in a moving state (also referred to as “Exciter”), and a rubber sheet is attached to that portion. An air chamber coupling 404 was formed on the rubber sheet of the speaker 403 by press-fitting the MEMS-ECM 405 whose frequency characteristics with an enlarged cavity diameter were inspected (to be tested) so as to face each other.

  In this state, an FFT analyzer 401 (CF-7200, Ono Sokki Co., Ltd.) is used as a low frequency signal generator to output signals of each frequency by sine wave sweep in the range of 0.125 to 100 Hz. The signal was input to the DC power amplifier 402 and amplified. This amplified signal is input to the FFT analyzer as input 1.

  Furthermore, by driving the voice coil of the speaker 403 with the low-frequency signal generated from the low-frequency signal generator 401, the signal from the speaker 403 moves up and down the rubber sheet according to the signal. A signal 407 (volume pulse wave signal, velocity pulse wave signal, acceleration pulse wave signal) obtained by correcting the frequency generated by the MEMS-ECM 405 in the frequency compensation circuit 406 as necessary is input to the FFT analyzer as input 2. . Note that the frequency compensation circuit 406 performs processing similar to frequency correction described later. That is, a signal obtained by integrating the signal generated by the test MEMS-ECM 405 is a volume pulse wave signal, a signal obtained by amplifying the signal generated by the test MEMS-ECM 405 is a velocity pulse wave signal, and a signal generated by the test MEMS-ECM 405 The differentiated one is obtained as an acceleration pulse wave signal.

Regarding the amplitude and phase characteristics of the signal (input 1) and the input 2 of the driving low frequency signal generator, the value of (input 2 / input 1) is obtained at each frequency swept in the range of 0.125 to 100 Hz. By adding 128 times and averaging this, the low frequency characteristics of the MEMS-ECM at each frequency were measured and verified.
By taking the frequency (Hz) on the horizontal axis and the amplitude (dB) on the vertical axis by the frequency characteristic measurement method described above, the verification result of the low frequency frequency characteristic is expressed as shown in FIG.

  As shown in FIG. 16, in the frequency characteristics of the MEMS-ECM used for verification, a sensitivity decrease of 20 dB / dec was recognized toward the low frequency. If it is related to the motion of the heart, the pulse is usually about 1 Hz (when the pulse is 60 per minute), so this can be said to indicate the differential characteristic of the signal to be detected originally. It can also be said to be equivalent to a differential circuit having one pole in the vicinity of 100 Hz.

At this time, assuming that a signal such as volume change is to be detected, when measuring a pulse wave with MEMS-ECM, in a target frequency band (approximately 0.5 to 10 Hz), The measured waveform shows a velocity component that is a differential of a normal pulse wave, and can be considered as a “velocity pulse wave”.
The acceleration pulse wave that is often used to determine the state of the blood vessel is a time derivative of this velocity pulse wave.

[2-6. About frequency correction processing]
<Frequency correction processing>
Next, frequency correction processing for pulsation signal output will be described.
The frequency correction process is a correction process for extracting at least one of a pulsating volume signal, a pulsating velocity signal, and a pulsating acceleration signal with respect to the pulsating signal output from the sensor 31 of the sample information processing apparatus 1. .

Since the output (measurement data) of the MEMS-ECM showing a response as shown in FIG. 16 is obtained as a velocity pulse wave, the velocity pulse wave can be obtained when frequency correction is not performed.
In order to obtain a pulse wave and an acceleration pulse wave from the output of the MEMS-ECM, a frequency correction process for passing through an electric circuit having a frequency response as shown in FIG. 17 may be applied.

  In other words, if the MEMS-ECM output passes through a flat curve at -20 dB / dec from an extremely low frequency range to 100 Hz, a (volume) pulse wave can be obtained, and the MEMS-ECM output exceeds the output of the MEMS-ECM. If it rises at 20 dB / dec from low frequency to 100 Hz and then passes through a flat electric circuit, an acceleration pulse wave can be obtained. Further, when the correction process is not performed on the output of the MEMS-ECM, a velocity pulse wave is obtained. The total frequency characteristic after passing through such a circuit is as shown in FIG.

In FIG. 19, D indicates the frequency characteristic of the velocity pulse wave, E indicates the frequency characteristic of the volume pulse wave, and F indicates the frequency characteristic of the acceleration pulse wave.
These acceleration pulse waves, velocity pulse waves, and volume pulse waves shown in FIG. 19 increase in gain at 40 dB / dec, 20 dB / dec, and 0 dB / dec as the frequency increases. In the vicinity of the frequency of the pulse wave, the acceleration pulse wave, the velocity pulse wave, and the frequency characteristics that generate the pulse wave are obtained.

  In this frequency correction process, an acceleration pulse wave can be obtained by compensating (differentiating) 100 Hz or less for the velocity pulse wave with a differentiation circuit, and 100 Hz or less for the velocity pulse wave is compensated for by an integration circuit ( The processing equivalent to the processing capable of obtaining the volume pulse wave by performing integration) is performed. In the frequency correction process, an amplification operation may be performed as necessary.

Further, the frequency correction processing is to obtain an acceleration pulse wave by performing a differentiation operation on a frequency of 1 Hz of a pulse wave, obtain a volume pulse wave by performing an integration operation, and perform an amplification operation to obtain a speed. It can also be said that it is a process for obtaining a pulse wave.
When a circuit for performing such frequency correction is represented by an analog circuit, it can be configured as shown in FIG.
In FIG. 18, the part indicated by reference sign A is an amplification operation circuit part, the part indicated by reference sign B is an integration operation circuit part, and the part indicated by reference sign C is a differential operation circuit part.

<Frequency correction processing and pulse waveform>
FIG. 20 shows the waveform of a pulse wave observed by applying MEMS-ECM to the wrist rib so that the diameter of the opening 22 is expanded and the cavity 23 forms a closed cavity. The waveform of the velocity pulse wave (measurement data) obtained by the measurement is represented as shown in FIG. The volume pulse wave obtained by compensating the velocity pulse wave by the integration circuit described above is expressed as shown in FIG. The acceleration pulse wave obtained by compensating the velocity pulse wave by the above-described differentiation circuit is expressed as shown in FIG.

  The waveforms of volume pulse velocity, velocity pulse wave, and acceleration pulse wave are used for health care and diagnosis of diseases in various fields including Oriental medicine. As an example, the waveform of the volume pulse wave obtained by measuring the pulse wave of the carotid artery using a piezoelectric element is represented as shown in FIG. The velocity pulse wave is expressed as shown in FIG. The acceleration pulse wave is represented as shown in FIG.

  As shown in FIG. 20 (c) and FIG. 21 (c), the peaks of a to e (a wave to e wave) characterizing the acceleration pulse wave are obtained. Among these, the relative amplitudes of the b-wave and d-wave are used for estimation of the relationship with the cardiovascular disease, age and blood pressure, and the like, and are factors that are clinically important. This b-d wave is derived from the manner of synthesis of ejection waves from the heart (Percussion Wave, hereinafter also referred to as “PW”) and reflected waves from vascular barriers (Tidal Wave, hereinafter also referred to as “TW”). However, the pulse wave is greatly different depending on the shape of the constriction at the portion indicated by PW and TW in FIG.

  From the comparison of the waveforms of FIG. 20 and FIG. 21, the S / N ratio of the observed volume pulse wave (FIG. 20A) is improved by measuring the pulse wave using MEMS-ECM. It can be seen that the gap formed by PW and TW is emphasized, and that a significant peak is also formed in the acceleration pulse wave (FIG. 20C).

  According to the sample information processing apparatus 1 and the sample information processing method of the present invention, the cavity 23 forms a closed cavity, and the ECM or MEMS-ECM is used as the sensor 31, so that it is in a lower frequency region than before. The S / N ratio of the pulsation signal is greatly improved, and a clearer pulse wave can be obtained. At this time, it is possible to improve the accuracy of blood vessel depth information that can be calculated by substituting the amplitude of pulsation into equation (5).

[3. About notification of blood vessel position]
As described above, by using the sample information processing apparatus 1, an output level from at least one of the plurality of sensors 31 that changes with the movement of the pulsation signal detection unit array 12 is detected. Based on the change in the output level, the position of the arterial blood vessel 93 can be traced on the surface of the skin 92 of the specimen 91 to determine the position information of the blood vessel.
Next, using this characteristic of the sample information processing apparatus 1, the position information of the blood vessel is notified when the sample information processing apparatus 1 detects a pulsation signal, and the apparatus is mounted at an appropriate detection position. And a device that makes it possible to make measurements

  The sample information processing apparatus 1 that performs notification of the blood vessel position information includes a level detection unit and a level display unit, and the level display unit is provided in the pulsation signal detection unit array 12. be able to.

  The level detection unit detects an output level from at least one of the plurality of sensors 31 that changes as the pulsation signal detection unit array 12 moves.

  The level display unit displays output level change information based on the detection result of the level detection unit. The level display unit is preferably provided at a location that is easily visible in the sample information processing apparatus 1, for example, at a site that is the upper surface of the device when the device is mounted on a sample.

  When functionally representing the sample information processing apparatus 441 that notifies the blood vessel position, it can be configured as shown in FIG. 23, for example. The level detection unit 442 includes a PLL (Phase-locked loop) 443, a timing generation unit, and the like. 444 and sample hold 445 and 446, and the level display unit 447 includes comparators 448 and 450, and LEDs (Light Emitting Diodes) 449 and 451.

When the pulse information is measured by the sample information processing apparatus 1, the pulsation signal is detected while changing the position with the pulsation signal detection unit array 12 facing the sample, and as shown in FIG. depending on the positional relationship between the arterial blood vessel 93 of the pulsating signal detection unit 11 and the sample 91 of signal detecting unit array 12, the output level from the sensor 31 (pulse wave intensity (amplitude)) of the peak t ₁ ~t ₈ It changes in order as follows. Wherein at t ₁ ~t _4, the amplitude of the pulse wave increases as the sample processing apparatus 1 approaches the artery 93 of the specimen, represent the manner in which the peak at t _4. In addition, from t _{5 to} t ₈ , the sample information processing apparatus 1 represents a state in which the amplitude decreases as the sample information processing apparatus 1 moves away from the arterial blood vessel 93 of the sample 91.

  For the pulse wave obtained by the measurement, first, the level detection unit 442 detects the output level from the sensor 31 that changes as the pulsation signal detection unit array 12 moves. As an example, as shown in FIG. 23, a peak value output from the sample hold 445 and a delay corresponding to one peak position output from the sample hold 446 using the PLL 443, the timing generation unit 444, and the sample hold 445, 446 are used. The peak obtained is input to the comparators 448 and 450.

Next, as shown in FIG. 23, the level display unit displays the output level evaluation information in accordance with the output from the level detection unit 442. Here, the LEDs 449 and 451 are lit when the outputs of the comparators 448 and 450 are Low. Thus, comparator 450 receives the output from the sample hold 445 and sample and hold 446, (in the case of t ₁ ~t ₄ in FIG. 22) input from the sample hold 445 is higher than the input from the sample hold 446 The LED 451 is turned on. Comparator 448 receives the outputs from sample hold 445 and sample hold 446, and turns on LED 449 if the input from sample hold 445 is lower than the input from sample hold 446.

  Since the LEDs 449 and 451 are provided at locations that are easily visible in the present apparatus, it is possible to easily know that the present apparatus 1 is mounted at a site corresponding to an appropriate detection position that is close to the position of the arterial blood vessel 93. it can.

Since the present sample information processing apparatus 1 is configured as described above, for example, when a pulsation signal is detected while moving a human wrist as a sample in one direction in the circumferential direction, the sample information processing apparatus 1 is separated from the arterial blood vessel 93. As the sample information processing apparatus 1 approaches the arterial blood vessel 93 from the peak of t _1, the peak increases as shown by t ₂ to t _{3 in} FIG. 22, and reaches the maximum at t ₄ that is closest to the arterial blood vessel 93. During this time, the level detection unit 442 detects the output level from the sensor 31, and the level display unit 447 turns off the LED 449 and turns on the LED 451. Furthermore, when the detection of the pulsatile signal while moving the sample processing apparatus 1, the sample processing apparatus 1 is that away from the arterial vessel 93, the amplitude decreases at t ₅ ~t _8. During this time, the level display unit 447 turns on the LED 449 and turns off the LED 451.

  When detecting the pulsation signal while moving the sample information processing apparatus 1 by providing the LEDs 449 and 451 in the pulsation signal detection unit array 12 and emitting the LED 449 in red and the LED 451 in blue, for example. In addition, the positional relationship with the arterial blood vessel 93 can be notified to the user by a change in the lighting state (lighting color) of the LED. As a result, the user can easily attach the apparatus to an appropriate position close to the arterial blood vessel 93 by operating the sample information processing apparatus 1 and checking the LED at hand on the sample information processing apparatus 1. Can be measured. In addition, measurement at a position close to the arterial blood vessel 93 is possible, and a strong pulsation signal can be detected.

  Of course, when the LED 449 is turned on, a display board showing the output level determination result (for example, a display board displayed as “after” by turning on the LED 449) is illuminated, and when the LED 451 is turned on, it is different from the display board illuminated by the LED 449. A display board (for example, a display board displayed as “front” when the LED 451 is turned on) may be illuminated. With this configuration, a person using this apparatus can easily confirm the position of the arterial blood vessel 93 by performing an operation according to the display on the display board, and confirm the proper mounting position of this apparatus. I can do it.

  As described above, the sample information processing apparatus 1 includes the level detection unit 442 and the level display unit 447, and the level display unit 447 is provided in the pulsation signal detection unit array 12. It becomes possible to acquire position information. In addition, since this apparatus can be mounted and measured at a position close to the position facing the blood vessel 93, the accuracy of calculating blood vessel depth information can be improved. Further, since this apparatus can be mounted at an appropriate position close to the blood vessel 93 and measurement can be performed, a pulsation signal having a strong signal and a high S / N ratio can be detected, and the amplitude of the pulsation is expressed by the equation (5). ), The accuracy of blood vessel depth information that can be calculated can be improved. Further, the S / N ratio and sensitivity of the respiratory signal extracted from the pulsation signal by the frequency demodulator 61 can be improved.

  Here, the level detection unit and the level display unit are applied to the output level from one sensor, and the output level from one sensor 31 that changes with the movement of the pulsation signal detection unit array is detected. However, the present invention may be applied to the output levels from all the sensors 31 of the plurality of pulsation signal detection units 11 constituting the pulsation signal detection unit array 12, and any one pulsation signal may be applied. You may apply about the output level from the sensor 31 of the detection unit 11. FIG.

  In the case of applying the output level from the sensor 31 of one pulsation signal detection unit 11 among the plurality of pulsation signal detection units 11, the sensor 31 of the pulsation signal detection unit 11 at a position facing the blood vessel 93. It is preferable to notify the blood vessel position by detecting the output level. For example, as shown in FIGS. 24 and 25, when the pulsation signal detection unit array 12 is constituted by three pulsation signal detection units 11a, 11b, and 11b, the central pulsation signal detection unit 11b is opposed to the blood vessel 93. Therefore, it is preferable to apply to the output level from the sensor 31b of the central pulsation signal detection unit 11b. In this case, the central pulsation signal detection unit 11b is connected to the blood vessel 93 in that the output levels from the sensors 31a and 31c of the pulsation signal detection units 11a and 11c at both ends of the central pulsation signal detection unit 11b are approximately the same. This is because information that can be determined to be in a position opposite to can also be used.

(Other)
(About pulsation detection unit array and pulsation detection unit)
In the above embodiment, the example in which the pulsation signal detection unit array 12 is configured by the three pulsation signal detection units 11 has been described. However, two or four or more pulsation signal detection unit arrays 12 are provided. The pulsation signal detection unit 11 may be configured.

  When the pulsation signal detection unit array 12 is constituted by two pulsation signal detection units 11, the acquisition of the blood vessel position information is obtained based on a change in the output level from at least one sensor 31, and therefore 3 This can be performed in the same manner as when the pulsation signal detection unit array 12 is constituted by the two pulsation signal detection units 11. The calculation of the depth information of the blood vessel is performed by installing the pulsation signal detection unit array 12 so that one of the pulsation signal detection units 11 faces the blood vessel 93 using the position information of the blood vessel. The pulsation amplitude detected by the sensor 31 of the pulsation signal detection unit 11 and the distance between the two pulsation signal detection units 11 can be calculated by Equation (5).

  When the pulsation signal detection unit array 12 is configured by four pulsation signal detection units 11, the acquisition of the blood vessel position information is obtained based on a change in the output level from at least one sensor 31. This can be performed in the same manner as when the pulsation signal detection unit array 12 is configured by the pulsation signal detection unit 11. The calculation of the blood vessel depth information is performed by installing the pulsation signal detection unit array 12 so that one of the pulsation signal detection units 11 faces the blood vessel 93 using the blood vessel position information. The amplitude of the pulsation detected by the sensor 31 of the pulsation signal detection unit 11 at the position opposite to that of the pulsation signal 93, the amplitude of the pulsation detected by the sensor 31 of the other pulsation signal detection unit 11, and the amplitude were measured 2 From the distance between the two pulsation signal detection units 11, it can be calculated by the equation (5). At this time, when a plurality of pulsation signal detection units 11 are installed at equal intervals, the pulsation is performed so that the sensor 31 of the pulsation signal detection unit 11 existing at both ends is opposed to the blood vessel 93. By installing the sex signal detection unit array 12, the output level of the pulsation signal detection unit 11 adjacent to the pulsation signal detection unit 11 located at the position opposite to the blood vessel 93 is used to make the pulsation signal detection unit. 11 is preferable because it can be confirmed that 11 is in a position facing the blood vessel 93.

(About notification of the position of the central pulsation detection unit)
In the above description, as shown in FIGS. 24 and 25, the pulsation signal detection unit array 12 is composed of three pulsation signal detection units 11a, 11b, and 11c, and the central pulsation property is shown. If the distance from the signal detection unit 11b to the left and right pulsation signal detection units 11a and 11c is equal, is the pulsation signal detection unit 11b at the center of the pulsation signal detection unit array 12 positioned opposite the blood vessel 93? As a method for confirming whether or not the waveform of the pulsating signal detection unit array 12 is confirmed by checking the waveforms of the pulsating signals from the sensors 31a and 31c of the left and right pulsating signal detection units 11a and 11c displayed by the waveform display unit 82. The output level of each sensor 31 of the pulsation signal detection unit array 12 with the change in position is detected, It is determined that the central pulsation signal detection unit 11b is at a position facing the blood vessel 93 in that the output levels of the pulsation signals from the sensors 31a and 31c of the pulsation signal detection units 11a and 11c are approximately the same. As described above, the level detection unit that detects the output level from the pulsation signals from the sensors 31a and 31c of the left and right pulsation signal detection units 11a and 11c that change with the movement of the pulsation signal detection unit array 12. And a level display unit for displaying output level change information based on the detection result of the level detection unit, and the level display unit is provided in the pulsation signal detection unit array 12, so that You may comprise so that it may notify that the signal detection unit 11b exists in the position facing the blood vessel 93. FIG.

  As such a configuration, for example, as shown in FIGS. 24 and 25, the pulsation signal detection unit array 12 is composed of three pulsation signal detection units 11a, 11b, and 11c. When the distance from the pulsation signal detection unit 11b to the left and right pulsation signal detection units 11a and 11c is equal, the pulsation signal detection unit array 12 is moved across the line connecting points 2 to 5 in FIG. In this case, the level display unit detects the output levels from the sensors 31a and 31c, and the level display unit is configured to light the LEDs in that the output levels from the sensors 31a and 31c are approximately the same. Thus, notification that the central pulsation signal detection unit 11b is in a position facing the blood vessel 93 by lighting the LED. It can be.

(About signal processing)
In the above description, the processing by the analog circuit included in the sample information processing apparatus 1 is described for the processing of the pulsating signal. However, the sample information processing apparatus 1 is a digital circuit, for example, a digital signal processor (hereinafter also referred to as “DSP”). It is good also as a structure which digitally processes a signal by this digital circuit. In addition, the pulsation signal detected by each sensor 31 of the pulsation signal detection unit array 12 is output to the computer 81 via the external A / D converter of the sample information processing apparatus 1, and the signal is processed by the CPU. It is also good.

DESCRIPTION OF SYMBOLS 1 Sample information processing apparatus 11, 11a, 11b, 11c Pulsating signal detection unit 12 Pulsating signal detection unit array 21 Sensor attachment part 22 Opening part 23 Cavity
24 O-ring 31, 31 a, 31 b, 31 c Sensor 32 Pressure information capturing unit 33 Sensor element 34 Air chamber 35 Housing 41 Signal processing unit 51 Signal correction unit 61 Frequency demodulation unit 71 Blood vessel information detection unit 81 Computer 91 Sample 92 Skin 93 blood vessels

Claims (14)

A sensor that receives pressure information resulting from a blood vessel pulsation signal in the specimen and detects the blood vessel pulsation signal in the specimen, and a cavity communicating with the pressure information capturing portion of the sensor, and the specimen A sensor mounting portion having a spatial structure in which an opening having a diameter of 3 mm to 10 mm is provided at an opposing portion, the opening is opposed to the sample, and the cavity is closed in a state of being attached to the sample. Provide multiple pulsation signal detection units,
These pulsation signal detection units are arranged in parallel to form a pulsation signal detection unit array,
A specimen characterized by comprising a blood vessel information detection unit that obtains the depth information of the blood vessel by performing a required calculation on the pulsation signal output from each sensor of the pulsation signal detection unit array Information processing device.   2. The sample according to claim 1, further comprising a level detection unit that detects an output level from at least one of the plurality of sensors that changes as the pulsation signal detection unit array moves. Information processing device. A level display unit that displays output level change information based on the detection result of the level detection unit;
The sample information processing apparatus according to claim 1, wherein the level display unit is provided in the pulsation signal detection unit array.   A signal for extracting at least one of a pulsating volume signal, a pulsating velocity signal, and a pulsating acceleration signal by performing frequency correction processing on the pulsating signal output from the sensor of the pulsating signal detection unit array. The sample information processing apparatus according to claim 1, further comprising a correction unit.   The signal correction unit performs at least one of an amplification operation, an integration operation, and a differentiation operation at a frequency of the pulsating signal, so that at least the pulsating volume signal, the pulsating velocity signal, and the pulsating acceleration are obtained. 5. The sample information processing apparatus according to claim 4, wherein one of the signals is extracted.   A frequency demodulator that extracts a respiratory signal included in the pulsation signal output by performing frequency demodulation processing on the pulsation signal output from the sensor of the pulsation signal detection unit array; The specimen information processing apparatus according to claim 1, wherein the specimen information processing apparatus is characterized.   7. The sensor according to claim 1, wherein the sensor is configured as a condenser microphone that detects sound pressure information caused by a pulsating signal of an arterial blood vessel in the specimen. Sample information processing device.   The sample information processing apparatus according to claim 7, wherein the condenser microphone is configured by a MEMS type ECM.   The sample information processing apparatus according to any one of claims 1 to 8, wherein a diameter of the opening is not more than five times a diameter of an arterial blood vessel. Each of the sensors receives pressure information resulting from the pulsation signal of the blood vessel in the specimen, and has a sensor that detects the pulsation signal of the blood vessel in the specimen, and a cavity that communicates with the pressure information capturing unit of the sensor. A sensor mounting portion having a spatial structure in which an opening having a diameter of 3 mm to 10 mm is provided at a portion facing the sample and the cavity is closed in a state where the opening is mounted on the sample with the opening facing the sample; A pulsation signal detection unit array configured by arranging a plurality of pulsation signal detection units in parallel is prepared,
The pulsation signal detection unit array is installed in a direction crossing the blood vessel, and the pulsation signal detection unit of the pulsation signal detection unit array is positioned so as to face the blood vessel. The sex signal detection unit array is installed,
Thereafter, the specimen information processing method is characterized in that the depth information of the blood vessel is obtained by receiving the output from each sensor of the pulsation signal detection unit array and performing a required calculation.   The strength of the pulsating signal output from the sensor of the pulsating signal detection unit at a position facing the blood vessel of the pulsating signal detection unit array, and the sensor of another pulsating signal detection unit of the pulsating signal detection unit array Depth information of the blood vessel from the strength of the pulsating signal output from the pulsating signal detection unit and the distance between the pulsating signal detection unit and the other pulsating signal detection unit at a position facing the blood vessel of the pulsation signal detection unit array. The sample information processing method according to claim 10, wherein:   Detecting an output level from at least one of the plurality of sensors that changes as the pulsation signal detection unit array moves, and obtaining position information of the blood vessel based on the change in the output level. The specimen information processing method according to claim 10 or 11, characterized in that it is characterized.   Extracting at least one of a pulsating volume signal, a pulsating velocity signal, and a pulsating acceleration signal by performing a frequency correction process on the pulsating signal output from the sensor of the pulsating signal detection unit array. The sample information processing method according to any one of claims 10 to 12, characterized by:   9. The respiratory signal included in the pulsation signal output is extracted by performing frequency demodulation processing on the pulsation signal output from the sensor of the pulsation signal detection unit array. The specimen information processing method according to any one of claims 10 to 13.

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