Estimation device and estimation method

Abstract

An estimation device and an estimation method are provided that enable estimation of the state of a living body's urinary function in a minimally invasive manner with excellent reproducibility. [Solution] The estimation device 100 of the present invention comprises an imaging means 101 that images the flow of urine U excreted from a living body L, a first measuring means 102 that measures at least one of the velocity of the urine U, the first distance of the urine U, and the second distance of the urine U from the imaged flow of the urine U, and a second measuring means 104 that measures the flow rate of the urine U after imaging, wherein the first distance of the urine U is the distance from the position where the excretion of the urine U begins to the position where the urine U begins to form a coil, and the second distance of the urine U is the distance from the position where the excretion of the urine U begins to the position where the urine U begins to scatter.

Description

[Technical Field]

[0001] The present invention relates to an estimation device and an estimation method for estimating the state of a living body's urinary function. [Background technology]

[0002] Urinary disorders are a common illness affecting many people. Urinary disorders, such as overactive bladder and nocturia, can reduce sleep quality and affect quality of life and social activity. Urinary disorders have diverse causes, including aging, benign prostatic hyperplasia, and neurological disorders. Furthermore, the pathophysiology (mechanisms) of urinary disorders are also diverse, including obstruction, bladder contraction disorders, and sensory impairment. However, current major urination tests are limited to uroflowmetry (UFM) and urodynamic study (UDS), which are insufficient for identifying diverse causes and pathophysiology. This makes it difficult to select appropriate treatments, often resulting in inefficient diagnosis.

[0003] Although uroflow measurement is simple, the measurement results are not reproducible, making it difficult to apply to understanding pathological conditions. Urodynamic testing measures bladder contraction force and is a highly invasive test because it requires the insertion of a pressure transducer (catheter) into the urethra and rectum. In order to realize a minimally invasive and highly reproducible testing method, various studies have been conducted on the relationship between urinary stream morphology and urethral morphology (Non-Patent Documents 1 and 2). [Prior art documents] [Non-patent literature]

[0004] [Non-Patent Document 1] Vorticity in lower urinary tract can be assessed and associates with urinary tract morphology in men, 29 September 2019, Neurourology and Urodynamics. 2020;39:286-294 [Non-patent document 2] Initial clinical results of fluid dynamical approach for lower urinary tract function using a high-speed video camera, International Journal of Urology (2022), 1-2 Summary of the Invention [Problem to be solved by the invention]

[0005] The present invention has been made in consideration of the above circumstances, and aims to provide an estimation device and an estimation method that enable minimally invasive and highly reproducible estimation of the state of a living body's urinary function. [Means for solving the problem]

[0006] In order to solve the above problems, the present invention employs the following means.

[0007] (1) An estimation device according to one aspect of the present invention comprises an imaging means for imaging the flow of urine excreted from a living body, a first measuring means for measuring at least one of the velocity of the urine, the first distance of the urine, and the second distance of the urine from the imaged flow of the urine, and a second measuring means for measuring the flow rate of the urine after imaging, wherein the first distance of the urine is the distance from the position where the urine starts to be excreted to the position where the urine starts to form a coil, and the second distance of the urine is the distance from the position where the urine starts to be excreted to the position where the urine starts to scatter.

[0008] (2) In the estimation device described in (1), the imaging means may be provided at one or more positions on the side opposite the external urethral orifice of the living body, opposite a plane containing a urine stream formed by the flow of urine.

[0009] (3) In the estimation device described in either (1) or (2), the imaging means may be provided at one or more positions on a plane including a urine stream formed by the flow of urine on the side opposite the external urethral orifice of the living body.

[0010] (4) The estimation device according to any one of (1) to (3) above may further include a light irradiating means for irradiating light onto the urine during the photographing.

[0011] (5) In the estimation device described in (4) above, the light irradiation means may include a scale on a light irradiation surface.

[0012] (6) The estimation device according to any one of (1) to (5) above may further include a windbreak means provided at a position surrounding the trajectory of the urine to provide wind protection.

[0013] (7) An estimation method according to one aspect of the present invention is an estimation method using an estimation device described in any one of (1) to (6), and includes an imaging step of imaging the flow of urine excreted from a living body, a first measurement step of measuring at least one of the velocity of the urine, the first distance of the urine, and the second distance of the urine from the imaged flow of the urine, a storage step of receiving and storing the urine after imaging, a second measurement step of measuring the flow rate of the stored urine, and an analysis step of analyzing the state of the urinary function of the living body based on the measurement results obtained in the first measurement step and the second measurement step.

[0014] (8) The estimation method according to (7) above may further include a correction step of correcting a time lag between the first measurement step and the second measurement step.

[0015] (9) In the estimation method described in either (7) or (8), it is preferable that the measurement result of the first measurement step used in the analysis is a measurement result obtained within 30 seconds from the time when the time change of the urine momentum in the second measurement step changes from increasing to decreasing, and that the urine momentum is the flow rate of urine stored in the storage means per unit time. [Effects of the Invention]

[0016] According to the present invention, it is possible to provide an estimation device and an estimation method that enable estimation of the state of a living body's urinary function in a minimally invasive manner with excellent reproducibility. [Brief explanation of the drawings]

[0017] [Figure 1] 1 is a diagram schematically illustrating a configuration of an estimation device according to an embodiment of the present invention. [Figure 2] (a) and (b) are images explaining the rate at which urine is excreted from a living body. [Figure 3] FIG. 2 is a diagram illustrating a first distance and a second distance of urine excreted from a living body. [Figure 4] 10A and 10B are diagrams illustrating correction of a time lag between urine velocity measurement and flow rate measurement by the estimation device of the same embodiment. [Figure 5] 10A to 10C are diagrams illustrating a method for estimating a urethral cross-sectional area using the estimation device of the embodiment. [Figure 6] FIG. 10 is a diagram illustrating the change in urine flow rate over time. [Figure 7] 10(a) to 10(c) are diagrams illustrating changes in the position of urine coil formation depending on the urine flow rate. [Figure 8] 1(a) to 1(c) are diagrams showing schematic diagrams of the urethra in a normal state, a narrowed state, and a deformed state. [Figure 9] 10(a) to 10(g) are diagrams showing the shapes of parts attached to the estimation device of FIG. 9 in order to reproduce each state of the urethra. [Figure 10] 10 is a graph showing measurements of velocity, first distance, and second distance of a liquid exiting a tubular component at various heights. [Figure 11] 10 is a graph showing differences in urine velocity with changes in urethral condition. [Figure 12] 10 is a graph showing the difference in the first distance of urine with changes in the urethral condition. [Figure 13]10 is a graph showing the difference in the second distance of urine with changes in urethral condition. DETAILED DESCRIPTION OF THE INVENTION

[0018] Hereinafter, an estimation device and an estimation method according to an embodiment of the present invention will be described in detail with reference to the drawings. Note that the drawings used in the following description may show characteristic portions enlarged for convenience in order to make the characteristics easier to understand, and the dimensional ratios of the components may not be the same as those in reality. Furthermore, the materials, dimensions, etc. exemplified in the following description are merely examples, and the present invention is not limited thereto. Appropriate changes can be made within the scope of the present invention.

[0019] <Estimation device> FIG. 1 is a diagram schematically illustrating the configuration of an estimation device 100 according to one embodiment of the present invention. The estimation device 100 is a means for estimating the state of the urinary function of a living organism L, and mainly comprises an imaging means 101, a first measuring means 102, a containing means 103, and a second measuring means 104. In this embodiment, the living organism L refers to the body of a living organism, and is assumed to be alive. The type of living organism here refers to an animal that urinates, such as a mammal, including a human. The sex of the living organism is not important.

[0020] The imaging means 101 is a means (imaging device) for imaging the flow (urinary stream) of urine U excreted from the living body L, and is, for example, a high-speed video camera having a function for capturing instantaneous high-speed phenomena in slow motion video. The frame rate of the imaging means 101 is preferably about 500 to 1000 fps.

[0021] 1 shows the photographing means 101 in one location, it may be provided in multiple locations. The location where the photographing means 101 is provided may be one or more positions on the side facing the external urethral meatus of the living body L, facing the plane containing the urine line formed by the flow of urine U, i.e., positions spaced apart to the left or right of the urine line as seen from the living body L. The location where the photographing means 101 is provided may also be one or more positions on the side facing the external urethral meatus of the living body L, on the plane containing the urine line formed by the flow of urine U (within the plane), i.e., positions spaced apart in front of or above the urine line as seen from the living body, or diagonally therebetween.

[0022] The first measuring means 102 is a means (measuring device) that measures at least one of the velocity V of the urine U, the first distance D1 of the urine U, and the second distance D2 of the urine U from the photographed flow of the urine U. The first measuring means 102 is electrically connected to the photographing means 101, and is configured to capture image data of the photographed flow of the urine U from the photographing means 101, and measure the velocity V, the first distance D1, and the second distance D2 from the image data.

[0023] Figure 2 is an image explaining the velocity V of urine U excreted from a living body L. Figure 2(a) is an image of a urine line at a certain time t seconds, and Figure 2(b) is an image of the urine line at a time (t + Δt) seconds Δt seconds after that. In the thickness direction (width direction) T of the urine line drawn by urine U, the outer surface becomes wavy, and over time, waves are formed that move along the direction F of urine U's movement.

[0024] The velocity V of urine U corresponds to the distance ΔX that the wave peak U1 moves per unit time. Therefore, the velocity V of urine U can be determined by measuring this distance ΔX using two images showing the time change of the urine stream as shown in Figure 2. The velocity V of urine U varies depending on the state of the urination function of the living body L.

[0025] 3 is an enlarged view of region R in FIG. 1 to explain the first distance D1 and second distance D2 of urine U excreted from a living body L. The urine U excreted from the living body L becomes thinner as it moves away from the excretion start position (urethral opening) P0, and begins to form a coil (twist) at position P1 where it is thinnest. Thereafter, the urine U continues to move forward while forming a coil, and begins to scatter at position P2 where it can no longer maintain the shape of the urine stream.

[0026] The first distance D1 of urine U means the distance (LFT (Length to the first twist)) from the excretion start position P0 of urine U to the position P1 where urine U begins to form a coil. The second distance D2 of urine U means the distance (LSU (Length to the scattered urine)) from the excretion start position P0 of urine U to the position P2 where urine U begins to scatter. Both the first distance D1 of urine U and the second distance D2 of urine U can be measured from an image of the urine stream. The first distance D1 of urine U and the second distance D2 of urine U each differ depending on the state of the urination function of the living body L.

[0027] The storage means 103 is a means (container) for receiving and storing the urine U after imaging. In order to reliably store the falling urine U without leakage, a funnel 105 may be provided directly above the storage means 103, as shown in FIG.

[0028] The second measurement means 104 is a means (device) for measuring the flow rate of the stored urine U. The second measurement means 104 is mainly composed of a urine volume detection unit 104A that comes into contact with the storage means 103 and detects the amount (volume) Q of the stored urine U, and a urine volume measurement unit 104B that measures the detected urine volume Q every hour.

[0029] If there is a third measurement means capable of performing both the first and second measurements, the first measurement means 102 and the second measurement means 104 may be replaced with this third measurement means. In this case, the third measurement means will be connected to both the imaging means 101 and the storage means 103.

[0030] The estimation device 100 may further include a light irradiation means 106 that irradiates light onto the urine U being photographed. By photographing with light irradiated, the obtained image can be made clearer. The light irradiation means 106 is not particularly limited, but a flat light LED can be used, for example. The light irradiation means 106 is preferably disposed so as to face the photographing means 101 with the urine U sandwiched therebetween.

[0031] The light irradiation means 106 may be provided with a scale (an implement (device, part) with a scale printed on it) 107 on its light irradiation surface (the surface from which light is emitted) 106a. In this case, by taking an image from a position facing the light irradiation means 106 across the urine line, the graduations of the scale 107 appear near the urine line in the resulting image, making it possible to easily and accurately know the dimensions of each point on the urine line.

[0032] The estimation device 100 may further include a position adjustment means 108 that adjusts the position of the storage means 103. The force and angle of urination vary depending on the living body L. Therefore, if the position of the storage means 103 is fixed, it is necessary to adjust the posture of the living body L, and tension, strain, etc., of the living body L that accompanies this adjustment may affect the flow state of the urine U. When the position adjustment means 108 is used, adjusting the position of the storage means 103 eliminates the need to adjust the posture of the living body L, allowing urination in a natural, relaxed position, and various measurements can be performed with the urine U in its original flow state.

[0033] The estimation device 100 may further include a windbreak means for reducing the influence of wind. By reducing the influence of wind, various measurements can be performed in the original flow state of the urine U. An example of the windbreak means is a wall-like object provided in a position surrounding the trajectory of the urine U.

[0034] <Estimation method> The estimation method of this embodiment using the estimation device 100 mainly includes an imaging step, a first measurement step, a storage step, a second measurement step, and an analysis step, and can be performed in the following procedure.

[0035] (Photography process, first measurement process) The flow of urine U excreted from a living body L is photographed by an imaging means 101, and from the photographed flow of urine U, at least one of the velocity V of urine U, the first distance D1 of urine U, and the second distance D2 of urine U is measured by a first measuring means 102.

[0036] (Storage step, second measurement step) The urine U after the photograph (urine that has fallen further from the photographed position) is received and stored in a storage means 103 (a specified container), and the flow rate of the stored urine U is measured by a second measurement means 104.

[0037] (correction process) FIG. 4 is a diagram illustrating the correction of the time lag Δt between the first measurement step (measuring the urine velocity, first distance, and second distance) and the second measurement step (measuring the urine flow rate) by the estimation device 100. The estimation device 100 is configured to perform the second measurement several seconds after the first measurement. Therefore, as shown in FIG. 4, there is a time lag Δt between the velocity value obtained in the first measurement (upper curve) and the urine flow rate value obtained in the second measurement (lower curve). It is preferable to correct this time lag Δt between the first measurement step and the second measurement step before the next analysis step.

[0038] (Analysis process) The state of the urinary function of the living body L is analyzed based on the measurement results obtained in the first measurement step and the second measurement step. Specifically, it is examined how the measurement results of the velocity V, the first distance D1, the second distance D2 obtained in the first measurement step, and the measurement result of the urine flow rate Q obtained in the second measurement step change relative to their respective values ​​in a normal state, and the state of the urinary function corresponding to the changes is estimated. This estimation may be performed using a database that records the correspondence between past measurement results and the state of the urinary function.

[0039] It is preferable that the first measurement result used for analysis is measured when the urine flow rate in the second measurement step is stable over time. The time when the urine flow rate is stable over time is, for example, when the time change in the urine flow rate in the second measurement step changes from increasing to decreasing (when the peak is passed). The number of time change peaks is one in a healthy organism, but may be multiple in a diseased organism. In a healthy organism, the time when the urine flow rate is stable over time is within approximately 30 seconds from the time when the time change in the urine flow rate in the second measurement step changes from increasing to decreasing.

[0040] FIG. 5 is a diagram illustrating a method for estimating the cross-sectional area A1 of the urethra L1 using the estimation device 100. It shows urine U being discharged from the opening of the urethra L1. The amount of urine discharged per unit time Q, the urine velocity V, and the urethral opening area A satisfy the relational expression Q = V × A. In this embodiment, the urine flow rate Q and velocity V can be measured using the first measurement means 102 and the second measurement means 104, and the urethral opening area A can be calculated by substituting the measurement results into this relational expression. This opening area A may not coincide with the internal cross-sectional area A1 of the urethra, but it can be used as a reference value to determine the approximate size of the cross-sectional area A1.

[0041] Figure 6 is a graph showing the change over time in the force of urine U (the amount of urine flowing per unit time). The force of urine U generally increases sharply from the start of urination, remains almost constant at its maximum, and then gradually decreases.

[0042] 7(a) to (c) are images of a urine stream taken at three different times T1, T2, and T3. Time T1 is the time when the urine flow reaches its maximum. Times T2 and T3 are times when the urine flow decreases. In this embodiment, the urine flow is defined as the flow rate of urine stored in the storage means per unit time.

[0043] 7(a) to 7(c), the measurement results of the first distance D1 and the second distance D2 may vary depending on the measurement time. The first distance D1 and the second distance D2 tend to become shorter as time passes. Since all measurement results used for comparison must be performed under the same conditions, it is preferable to measure the first distance D1 and the second distance D2 when the urine flow is stable.

[0044] 8(a) to 8(c) are schematic diagrams showing the urethra L1 in a normal state, a narrowed state, and a deformed state, respectively. The urethra L1 in a normal state extends almost straight (linear), and its inner diameter (thickness) is almost constant regardless of position. In contrast, the urethra L1 in a narrowed state extends straight, but the inner diameter is smaller in some parts along the way. Furthermore, the urethra L1 in a deformed state has a curved (curved) shape. Because the flow state of excreted urine differs depending on the state of the urethra L1, the state of the urethra L1 can be estimated by analyzing the flow state of urine.

[0045] As described above, the estimation device and estimation method of this embodiment estimate the state of a living organism's urinary function using the urine velocity, first distance, and second distance obtained by imaging urine excreted from the living organism and the urine flow rate obtained by conventional uroflowmetry (UFM) as criteria for determination. The inventors have confirmed that the urine velocity, first distance, and second distance are associated with abnormalities such as urethral stricture and deformation that cause impaired urinary function. Therefore, the estimation device and estimation method of this embodiment can estimate the state of a living organism's urinary function in a minimally invasive manner with excellent reproducibility.

[0046] Uroflowmetry measures only the amount of urine flow per unit time, and attempts to understand the degree and pathology of urinary disorders based on the pattern of increase and decrease. However, because uroflowmetry is affected by the amount of urine collected, it cannot be evaluated with small amounts of urination. Furthermore, the results of "thick, weak (slow) urination" and "thin, forceful (fast) urination" appear similar and cannot be distinguished. Furthermore, it is impossible to distinguish between benign prostatic hyperplasia, non-hypertrophic bladder outlet obstruction, and bladder contraction disorder.

[0047] In contrast, with the estimation of this embodiment, by calculating the urine velocity V, it is possible to calculate the cross-sectional area A of the urethra by dividing the synchronously measured urine volume Q by the velocity V. Therefore, by distinguishing between thin urine (narrow A) and thick urine (wide A), it is possible to understand the pathology better than with urinary flow measurement. Furthermore, since A is constant regardless of the force, it is possible to calculate A without being affected by the urination volume.

[0048] Urodynamic testing (UDS) requires the insertion of a catheter-type pressure transducer into the bladder and rectum, which inevitably causes physical and mental pain. In contrast, the estimation method of this embodiment relies on UFM and urinary stream observation, which are performed without contact with the living body, and can be performed less invasively than UDS.

[0049] Furthermore, UDS requires many consumable items (catheters, transducers, contrast agents, etc.), and further requires expensive measuring equipment in specialized facilities and the presence of at least three people: a doctor, a technician, and a nurse. The estimation device and estimation method of this embodiment, which do not require these, have significant advantages over UDS in terms of economy, human workload, and simplicity. [Example]

[0050] The effects of the present invention will be made clearer by the following examples. Note that the present invention is not limited to the following examples and can be practiced with appropriate modifications within the scope of the present invention.

[0051] The state of a living body's urinary function was estimated in accordance with the above embodiment. As a model of the urination part, tubular parts simulating the urethra in various states and a liquid supply means for supplying (flowing into) a liquid into the tubular part were prepared and incorporated into the estimation device of the above embodiment. The liquid supply means was configured to use a pump or the like to flow liquid (water) into one end of the prepared tubular part at a predetermined pressure and to allow the liquid to flow out (discharge) from the other end.

[0052] 9(a) to 9(g) are diagrams showing the shapes of the prepared tubular parts. The tubular part in Fig. 9(a) corresponds to the urethra in a normal state, and has a shape that extends straight with a uniform thickness (width).

[0053] The tubular parts in Figures 9(b) to (d) correspond to three types of urethra strictures (half-compressed type, fully compressed type, and stricture type), and each has a normal portion and a strictured portion (thinned portion). The normal portion has the same diameter as the tubular part in Figure 9(a).

[0054] In the tubular parts of Figures 9(b) and (c), the thickness changes continuously between the normal and constricted portions. In the constricted portion of the tubular part of Figure 9(b), only one side is concave inward. In the constricted portion of the tubular part of Figure 9(c), all sides are concave inward. In the tubular part of Figure 9(d), the thickness changes intermittently between the normal and constricted portions, and all sides are concave inward in the constricted portion.

[0055] The tubular parts in Figures 9(e) to (g) correspond to urethras in three different deformation states (curved type, strong curved type, and flat type). The tubular parts in Figures 9(e) and (f) each have a partially curved shape. Compared to the tubular part in Figure 9(e), the tubular part in Figure 9(f) is more curved. The tubular part in Figure 9(g) has a partially flat shape.

[0056] [Measurement 1] Using the tubular part of Figure 9(a), the velocity, first distance, and second distance of the liquid flowing out of the tubular part installed at various heights were measured. Figure 10 is a graph showing the measurement results. The horizontal axis of the graph indicates the height (cm) of the tubular part measured from the bottom of the container (container) that contains the liquid. The vertical axis of the graph indicates the ratio (%) of each measurement value when the tubular part is set to each height. The ratio is based on each measurement value when the height of the tubular part is 50 cm.

[0057] Specifically, the circle plots show the ratio of the liquid velocity when the height is 50cm, 70cm, 90cm, and 110cm to the liquid velocity when the height is 50cm. The triangular plots show the ratio of the first distance of the liquid when the height is 50cm, 70cm, 90cm, and 110cm to the first distance of the liquid when the height is 50cm. The square plots show the ratio of the second distance of the liquid when the height is 50cm, 70cm, 90cm, and 110cm to the second distance of the liquid when the height is 50cm.

[0058] A comparison of the measurement results in FIG. 10 reveals that the higher the urine discharge position, the greater the urine velocity, first distance, and second distance.

[0059] [Measurement 2] Using the tubular parts shown in Figures 9(a) to (g), the height of the tubular parts was adjusted to set the force of the outflowing liquid to 4 mL / s, 6 mL / s, and 15 mL / s, and the velocity, first distance, and second distance of the liquid outflowing from the tubular parts were measured.

[0060] Figure 11 is a graph showing the results of measuring the liquid velocity. The vertical axis of the graph shows the ratio (%) of the liquid velocity in each state to the liquid velocity in the normal state. The velocity in the constricted state is more than 20% lower than the velocity in the normal state. The velocity reduction becomes greater as the momentum of the liquid increases. It is believed that the velocity of the outflowing liquid is largely influenced by the constriction of the tubular part. On the other hand, the velocity in the deformed state is about the same as the velocity in the normal state, and the influence of the deformation of the tubular part is not very noticeable.

[0061] These results show that the rate at which urine is excreted from a strictured urethra tends to be slower than the rate at which urine is excreted in a normal state, and that urine rate can be used as a basis for estimating the presence or absence and degree of urethral stricture.

[0062] FIG. 12 is a graph showing the measurement results of the first distance of the liquid. The vertical axis of the graph shows the ratio (%) of the first distance of the liquid in each state to the first distance of the liquid in the normal state. The first distance in both the constricted state and the deformed state is shorter than the first distance in the normal state. The effect of the momentum of the liquid on the reduction in the first distance varies.

[0063] These results show that the first distance of urine discharged from the urethra tends to be shorter than the first distance in a normal state, and can be used as a basis for estimating the presence and degree of abnormalities such as urethral stricture and deformation. In particular, it can be seen that the first distance can be a more effective basis for estimating the presence and degree of deformation than velocity.

[0064] FIG. 13 is a graph showing the measurement results of the second distance of the liquid. The vertical axis of the graph shows the ratio (%) of the second distance of the liquid in each state to the second distance of the liquid in the normal state. The second distance in the constricted state is shorter than the second distance in the normal state. Depending on the momentum of the liquid, the second distance in the deformed state may be higher than the second distance in the normal state. The effect of the momentum of the liquid on the change in the second distance varies.

[0065] These results show that the second distance of urine discharged from a strictured urethra tends to be shorter than the second distance in a normal state, and that the second distance of urine can be used as a basis for estimating the presence or absence and degree of urethral stricture. Furthermore, the second distance of urine discharged from a deformed urethra tends to be different from the second distance in at least a normal state, and that the second distance of urine can be used as a basis for estimating the presence or absence of a deformed urethra. [Explanation of symbols]

[0066] 100... Estimation device 101....Shooting Method 102...first measurement means 103. Storage means 104...Second measuring means 104A Urine volume detector 104B...Urine volume measuring section 105···Furth 106...Light irradiation means 106a...Light irradiation surface 107 scale 108...Position adjustment means A: Urethral opening area A1: Cross-sectional area of ​​the urethra D1...first distance D2...Second distance F: Direction of urine flow L... Living organism L1...urethra T... Direction of urine stream thickness U···Urine U1... Wave crest P0: Position at which urine begins to be excreted P1: The point where urine begins to coil P2: The position where urine begins to scatter

Claims

1. an imaging means for imaging the flow of urine excreted from a living body; a first measuring means for measuring at least one of a velocity of the urine, a first distance of the urine, and a second distance of the urine from the photographed flow of the urine; a second measuring means for measuring the urine flow rate after imaging; the first distance is a distance from a position where urine starts to be discharged to a position where the urine starts to form a coil, The estimation device is characterized in that the second distance is the distance from the position where the urine starts to be discharged to the position where the urine starts to scatter.

2. The estimation device described in claim 1, characterized in that the imaging means is provided at one or more positions on the side facing the external urethral orifice of the living body and on the side facing the plane containing the urine stream formed by the flow of urine.

3. The estimation device described in either claim 1 or 2, characterized in that the imaging means is provided at one or more positions on a plane including a urine stream formed by the flow of urine on the side opposite the external urethral orifice of the living body.

4. 3. The estimation device according to claim 1, further comprising a light irradiation unit that irradiates light onto the urine during the photographing.

5. 5. The estimation device according to claim 4, wherein the light irradiation means has a scale on the light irradiation surface.

6. 3. The estimation device according to claim 1, further comprising a windbreak means provided at a position surrounding the urine trajectory for blocking wind.

7. An estimation method using the estimation device according to claim 1 or 2, an imaging step of imaging the flow of urine excreted from a living body; a first measuring step of measuring at least one of a velocity of the urine, a first distance of the urine, and a second distance of the urine from the photographed flow of the urine; a storing step of receiving and storing the urine after the photographing; a second measuring step of measuring the flow rate of the urine contained therein; and an analysis step of analyzing the state of the urinary function of the living body based on the measurement results obtained in the first measurement step and the second measurement step.

8. 8. The estimation method according to claim 7, further comprising a correction step of correcting a time lag between the first measurement step and the second measurement step.

9. The measurement result of the first measurement step used in the analysis is a measurement result obtained within 30 seconds from the time when the time change of the urine flow in the second measurement step changes from an increase to a decrease, 8. The estimation method according to claim 7, wherein the force of urine is a flow rate of urine stored in a storage means per unit time.

Images