US3869602A - Apparatus for automatic computation of cardiothoracic ratio - Google Patents

Apparatus for automatic computation of cardiothoracic ratio Download PDF

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Publication number
US3869602A
US3869602A US284558A US28455872A US3869602A US 3869602 A US3869602 A US 3869602A US 284558 A US284558 A US 284558A US 28455872 A US28455872 A US 28455872A US 3869602 A US3869602 A US 3869602A
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Prior art keywords
cardiothoracic
data
heart
data processing
automatically measuring
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US284558A
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Nobuhiko Sezaki
Kohji Ukena
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Panasonic Holdings Corp
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Matsushita Electric Industrial Co Ltd
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/59—Transmissivity
    • G01N21/5907—Densitometers
    • G01N21/5911—Densitometers of the scanning type
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Measuring devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/107—Measuring physical dimensions, e.g. size of the entire body or parts thereof
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/503—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for diagnosis of the heart
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/60—Analysis of geometric attributes
    • G06T7/62—Analysis of geometric attributes of area, perimeter, diameter or volume
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/10—Image acquisition modality
    • G06T2207/10116—X-ray image
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/30—Subject of image; Context of image processing
    • G06T2207/30004—Biomedical image processing
    • G06T2207/30048—Heart; Cardiac

Definitions

  • G06f /42 and heart are first inferred by processing information [58] Field of Search 235/1513; 444/1; on brightness from an X-ray image and h n n rr r 128/205 R, 2.06 R, 2.06 B, 2.6 G, 2.1 R, in the inference of the profiles is corrected by contex- 419 R, DIG, 3; 178/DIG, 5, DIG, 22; tual data. processing, so that the cardiothoracic ratio 250/320, 321, 322, 323, 401 may be computed on the basis of the corrected data.
  • the present invention relates to an apparatus for automatically computing the cardiothoracic ratio especially on the basis of an X-ray photograph.
  • a heart disease is accompanied by an abnormal enlargement of the heart
  • the universally adopted method of measurement thereof is by the cardiothoracic ratio advocated by C. S. Danzer, which is defined as a ratio in percentage of the transverse diameter of the heart to the maximal transverse internal diameter of the thorax.
  • C. S. Danzer which is defined as a ratio in percentage of the transverse diameter of the heart to the maximal transverse internal diameter of the thorax.
  • the CTR is usually determined with a rule or similar means applied to an X-ray or equivalent image of the chest. Even though various devices have been devised in an effort to facilitate the measurement, no substantial progress has been made in the direction of greatly saving the labor for the measurement.
  • the principal operations or operating principle of the apparatus according to the present invention consist of the first step of processing brightness information included in an X-ray image by an improved method to infer the profiles of the thorax and heart, the second step of correcting an error, if any, in the inference by contextual data processing and the third step of computing the cardiothoracic ratio on the basis of the corrected data.
  • Another object of the present invention is to provide an automatic cardiothoracic ratio measuring apparatus with a high performance at a reasonable cost.
  • FIG. 1 is a diagram for explaining what is the cardiothoracic ratio
  • FIG. 2 is a diagram showing an electrical signal generated by photo-electric conversion of an X-ray chest image along a straight line at right angles to the median line;
  • Flg. 3 is a diagram showing a typical electrical signal obtained from an actual X-ray chest image
  • FIG. 4 is a diagram for explaning the manner in which the peripheral points are determined in a typical electrical signal
  • FIG. 5 is a diagram similar to FIG. 4 for explaining the manner in which the peripheral points are determined in a distorted electrical signal
  • FIG. 6 is a diagram for explaining the manner in which the transverse diameter of the heart and the maximal transverse internal diameter of the thorax are determined; 1
  • FIGS. 7A and 7B are diagrams for explaining the manner in which data obtained are corrected
  • FIG. 8 is a block diagram showing an embodiment of the present invention.
  • FIGS. 9 and 10 are diagrams showing in detail a part of the embodiment of FIG. 8;
  • FIG. 11 shows a scanning locus
  • FIG. 13 is a plan showing a film driving system
  • FIG. 14 is a plan showing a frame detecting system
  • FIG. 15 an enlarged plan showing a part of the frame detecting system of FIG. 14.
  • the reference numeral shows a reference called the median line, numeral 11 the heart and numerals 12 and 12' lungs.
  • the numerals 13 and 14 show lines drawn perpendicular to the median line on the left and right sides thereof respectively at such points where the heart is projected most to the left and right I f the lengths of t l 1e tw g lines are expressed as T3 and 14 respectively, 13 14 represents the maximal transverse diameter-of the heart.
  • the numeral 15 shows the maximal transverse internal diameter of the thorax the length of which is expressed as l 5 Therefore, the
  • FIG. 2 an electrical signal 23 obtained by photoelectric conversion of an X-ray image ofthe chest along a given straight line at right angles to the median line 10 is shown in a simplified form, the numerals 21 and 22 respectively showing the white and black levels.
  • FIG. 2 is concerned with an ordinary image with a dark lung field, its brightness may be reversed.
  • the conventional straightward method of determin-' ing the peripheral points of the heart and thorax consisted in differentiating the electrical signal 23 to obtain points 24-1, 24-2, 24-3 and 24-4 with great gradients or finding the points including 25-1, 25-2, 25-3 and 25-4 on the signal curve where it crosses a predetermined lgyel if line.
  • the data thus obtained was used to obtain l3, l4 and 1 5 and then to compute the car'diothoracic ratio.
  • the electrical signal 23 of FIG. 2 usually takes a more complex form as shown in FIG. 3.
  • the curve of FIG. 3 shows an example ofa typical electrical signal on which numerals 31, 32, 33 and 34 indicate the peripheral points corresponding to those on the straight line 20 as determined by the observation of a person with a wealth of medical knowledge and experience.
  • the points 31, 32, 33 and 34 are considered to be true peripheral points. If the first one of the conventional methods explained with reference to FIG. 2 in which an electrical signal is differentiated to find points with the greatest gradients is applied to curve of FIG. 3 it is possible to detect the points on the curve of FIG.
  • peripheral points detected by the conventional methods do not agree with the correct peripheral points in many cases, sometimes even with an error for beyond the practically allowable limit. This is the very reason why, in spite of the simple engineering processes involved, the conventional methods have not been successfully commercialized.
  • Points 40 and 40' show the ends of the curve 30.
  • Numeral 46 shows the maximum point on the gentle part of the curve almost at the center thereof. This maximum point 46 of the curve 30 which is corresponding to the straight line 20 is found in every ordinary vX-ray image of the chest.
  • FIGS. 5(A), 5(8) and 5(C) show how the peripheral points 41, 42, 43 and 44 determined according to the invention are almost free from influences of any distortions of an electrical signal. According to the conventional methods, by contrast, even if satisfactory results. may be obtained from the signal of the waveform shown in FIG. 5(A), distortions of the signal as shown in FIGS.
  • a set of peripheral points thus determined will as-- merals 60-1, 60-2, 60-3, 60-n show equidistant straight lines at right angles to the median line which are equivalent to the straight line 20 moved up and down.
  • the distance between the straight lines which is determined taking into consideration the required accuracy and economy may be much longer than in the television raster.
  • the peripheral points 61-1, 62-1, 63-1 and 64-1; 61-2, 62-2, 63-2 and 64-2; 61-3, 62-3, 61-n, 62-n, 63-n and 64-n determined by the abovementioned method are the series of data providing the profiles of the thorax and the heart.
  • the line 62-n on the straight line 60-n is known to be a peripheral point of the diaphragm 69 but not the peripheral point between the lungs and the heart, the line 62-n will be disregarded, as mentioned in detail later with reference to th e second step of operation, in gle term in ing th e length 62-1.
  • 63-1, 63-2, 63-3, 65 show the length of lines perpendicular to the median line and passing through the points 6i 1 ,63-2, 63-n respectively
  • the maximum length 63-J corresponding to 14 in FIG. 1 is determined without regard to 637.
  • the distange between the points 61-1 and 64-1 is expressed as 65-]
  • the distance between points 61-2 a r i d 64-2 as 5 and so on, the maxim n distance 65-K is determined which corresponds to 15 in FIG. 1.
  • t h e ca rd i othorzgc ratiol computed from the length 62-1, 63-J and 65 -K as 62-I +63 J/65- R X 100 percent.
  • the cardiothoracic ratio is obtained only after the correction of the profile at the second step of the operation which will be explained below.
  • peripheral points 41, 42, 43 and 44 determined in FIGS. 4 and 5 according to the first step of operation agree well with the true peripheral points and that the results obtained are very stable. Even in this case, however, an error sometimes occurs which exceeds an allowable limit. This is mainly attributable to the fact that as mentioned above the shades of the ribs and blood vessels are indistinguishable from that of the lung field or the heart. The result is an electrical signal representing false information indicating an erroneous peripheral point. As far as the observation.
  • the straight lines -1, 70-2, 70-6 in FIG. 7A correspond to the straight line 20.
  • the peripheral points 72-1, 72-2, 72-6 were determined by following the first step of operation, the point 724 being a false peripheral point determined as mentioned above.
  • the co-ordinates representing the points 72-1, 72-2, 72-6 are D D D respectively.
  • FIG. 7B shows the case in which D does not actually exist within the range of P i A estimated on the basis of D and P
  • D is again employed for a further procedure disregarding P
  • Such a case occurs in the neighborhood of the diaphragms 69 and 69' in FIG. 6.
  • the data series tend to depart from the median line sharply in the neighborhood of the diaphragm, and it is known that points 72-4, 72-5, 72-6, correspond to the diaphragm, so that these data may be eliminated in the process of determining the maximal transverse diameter of the heart.
  • FIGS. 7A and 7B are primarily concerned with the determination of the profile of the heart, but a similar correcting process is applied to the determination of the profile of the thorax.
  • the method of correction explained with reference to FIGS. 7A and 7B is onlyan example of many possible methods, and does not preclude the use of a combination of more complex techniques of prediction. The important thing is to verify the co-relation with points in the neighborhood.
  • the present invention may be also effectively applied to the automatic measurements of not only the size of various internal organs but the area occupied thereby as its image is projected in a certain direction, as well as the volume of the internal organ through the combination of the above data and the ratio between them on the basis of radiographs.
  • the reference numeral 800 shows a light source including a lamp 801, a light diffusion plate 802 and a box 803 serving simultaneously as a reflector.
  • the light source 800 which is so designed that almost uniform brightness is obtained over the whole area ofthe light diffusion plate 802 is identical with the one used by a doctor for the observation of an X.-ray film.
  • the X-ray film-810 is disposed near the light diffusion plate 802.
  • Numeral 820 shows a photo-electric conversion system including a lens 821, vidicon tube 822, deflection circuit 823, video signal amplifier 824, sample and hold circuit 825, A-D converter 826 and control circuit 827.
  • the lens 821, vidicon tube 822, deflection circuit 823 and video signal amplifier 824 or a part thereof are equivalent to and may be replaced by a standard type of television camera with 525 scanning lines.
  • the lens 821 should preferably be provided with an automatic iris control regulated by, say, a CdS sensor in the neighborhood of the lens. Theiris of thelens is automatically adjusted to maintain the good operating conditions of the vidicon tube and the video signal amplifier even if the average shade of the film image varies with the photographing and developing conditions or an object.
  • the output of the video signal amplifier 824 is applied through the sample and hold circuit 825 to the A-D converter 826 where parallel digital outputs are produced.
  • the number of levels into which the shade is quantized in the digital data processing of an image depends upon the object of the data processing, but 7 bits that is 128 levels or 8 bits that is 256 levels meet the requirements of the present invention. In other words, one datum is containedin one byte.
  • FIG. 9. the output of the video signal amplifier 824 is applied to the lead wire 9-1.
  • the reference numeral 92 shows an operational amplifier, numerals 93 and 94 MOS FETs, numeral 95 a drive circuit for supplying a sampling signal to the gateof the MOS FET. 93.
  • a timing signal for the sampling operation is introduced from the control circuit 827 and applied to the lead wire 96.
  • a high input imedpance of the gate of the MOS FET 94 and capacitor 97 constitute a hold circuit, a signal held by which is taken out of the source of the MOS FET and applied through the lead wire 98 to the A-D converter 826. No explanation will be made of the A-D converter 826 which is well known.
  • the control circuit 827 acts to control not only the sample and-hold circuit 825 and A-D converter 826 but the deflection circuit 823 and is shown in detail in FIG. 10.
  • the numeral 101 shows a clock pulse generator, numeral 102 a countdown circuit, numeral 103 a lead wire for supplying horizontal and vertical synchronizing pulses to the deflection circuit 823 of the vidicon tube 822, and numeral 104 a dynamic shift register for a circulating storage with a circulation time equal to a horizontal scanning period, which is provided with output terminals for designating the positions of the parallel straight lines 60-1, 60-2, 60-3, 60-n in FIG. 6.
  • Numeral 105 shows a shift register for determining the number of the 1 parallel straight lines 60-1, 60-2, 60-3, 60-n in FIG.
  • numeral 106 a timing circuit
  • numeral 107 a lead wire for introducing a data read start instruction signal of image pick-up within which the vidicon tube operates
  • numeral 112 a locus of the electron beam scanning.
  • the locus'in FIG. 11 is shown rotated by even though actually its aspect ratio is 3 to 4 and agrees with a standard television system as already explained.
  • The-interlaced scanning ratio of 2 to l in the standard television system is not employed in this embodiment as will be clear from FIG. 10, partly because a resolution of about 128 lines is sufficient for the purpose of the present invention, and partly because it isdesired that the control circuit'827 should not unnecessarily be complicated.
  • the clock pulse generator 101 produces an output at the frequency of 1 MHz, while the horizontal and vertical synchronizing I signals produced from the count-down circuit 102 have the period of 64p sec or the frequency of [5625 KHZ and 16.384 in sec or 61.035 Hz respectively. Strictly speakingQtherefore, they are different from the standard system but it is needless to say that this small difference in frequency does not affect the normal operation of the standard type of camera or monitor. This merit, however, is not an important element of the present invention.
  • the above-mentioned method of obtaining the virtual scanning lines-by the standardtype of scanning and the controlling of timing of the sampling operation is only one of the possible methods.
  • Another method of achieving the object of the present invention is to deflect the electron beam along the above-mentioned vertical scanning lines. In other words, what is important is to convert the brightness of an image into an electrical signal along such loci.
  • the digital signal thus obtained is processed on the aforementioned principle by the data processing means 830 which comprises an interface 831, random access memory 832, processor unit 833 and read only memory 834.
  • the data processing means 830 should preferably be provided with an interrupt function, whereby the processing time can be shortened.
  • This data processing means may be replaced by a small digital computer which is generally called a minicomputer, in which case the program may be written not in the read only memory 834 but in the random access memory 832 with a capacity of approximately 4,000 bytes or words.
  • the numeral 840 in FIG. 8 shows an output means for producing the computation results of the cardiothoracic ratio.
  • Such an output means is typically represented by an input-output typewriter such as Teletype ASR33 of Teletype corporation or a CRT display terminal.
  • the profile of the heart and therefore the silhouette thereof as shown in FIG. 12 which is an interim result of the data processing operation is easily printed or otherwise displayed as'desired by a doctor involved.
  • the availability of this option is very important as it helps the doctor, if he so desires, diagnose a heart disease especially when the cardiothoracic ratio is abnormally high.
  • the reference numeral 850 in FIG. 8 shows a film handling system including a film handling mechanism 851 and a control circuit 852.
  • the types of film handled are roughly divided into a sheet and a roll.
  • a film handling system for a sheet is similar in construction to an OCR system called a document reader, while a roll film handling system is like an OCR system generally called a journal tape reader.
  • sheet filmsin an input hopper are fed one by one to automatically measure the cardiothoracic ratio following the above-mentioned operating steps, while this system is so arranged that on completion of a processing the processed films are housed in a stacker to make ready for the next film processing.
  • a roll of film is fed from one spool to the other -by means of a pinch roller, and it is desirable that the film is maintained stationary at least during the period of time in which a frame of film is being processed or when the film is being scanned to derive information.
  • the shaft 131 of the pinch roller is connected to the shaft of the motor 133 through the electromagnetic clutch 132 or the shaft of the electromagnetic clutch/brake 134 through the electromagnetic clutch 132.
  • the time when the film should be stopped occurs when the center of a frame of film to be processed reaches the optical axis of the lens 821, as detected by photo'electric sensors.
  • the vidicon 822, lens 821, film 810, light diffusion plate 802 and lamp 801 in FIG. 14 are identical to those shown in FIG. 8, the numerals 141 and 142 showing the photo-electric sensors.
  • the numeral 810 shows a roll film which is fed in the direction of arrow 143.
  • FIG. 15 The relationship between a series of frames of the film 810 and the photo-electric sensors 141 and 142 as seen from the lens is shown in FIG. 15.
  • the distance 151 between the two photo-electric sensors 141 and 142 is equal to the length 152 of a frame of the recorded roll film 810.
  • either the control circuit 852 is energized by a signal from the data processing means 830, or the operator in response to an alarm from the displayer indicating the completion of the processing 10 depresses a button for feed instructions, thereby to restart the feed of the" roll film 810 in the direction of arrow 143, but it is not until the next frame 8102 reaches the mid-point between the sensors 141 and 142 that the outputs of both the sensors 141 and 142 change to the white level.
  • the output of the sensors is shaped and, after an AND operation thereof, the control circuit 852 is energized, whereupon the film 810 is stopped by the electromagnetic clutch/brake 134.
  • the film handling system 850 may be replaced by a manual system in which the film is fed by hand sheet by sheet or frame by frame, as the occasion may be.
  • a system for automatically measuring the cardiothoracic ratios comprising photo-electric conversion means (820) for effectively scanning a chest X-ray image (810) along a plurality of parallel lines perpen dicular to the median line of said chest X-ray image and converting the brightness of said X-ray image into a corresponding electrical signal, data processing means (830) for processing data obtained from said photo electric conversion means, and means (840) for recording or displaying the value of the cardiothoracic.
  • a system for automatically measuring the cardiov thoracic ratios according to claim 1, in which said film handling means is manually operated.
  • a system for automatically measuring the cardiothoracic ratios according to claim 1, in which said photo-electric conversion means comprises a standard type of television image pickup device or an equivalent film camera.
  • a system for automatically measuring the cardiothoracic ratios according to claim 1, in which said data processing means is replaced by a general-purpose digital computer.
  • a system for automatically measuring the cardio-' thoracic ratios accordingto claim 1, in which data are processed in such a manner as to display or record the profiles of the heart and/or the thorax or the silhouettes thereof as well as the cardiothoracic ratios.
  • a system for automatically measuring the cardiothoracic ratios according to claim 1, further comprising film handling means for automatically feeding the film carrying said chest X-ray image.

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US284558A 1971-09-03 1972-08-29 Apparatus for automatic computation of cardiothoracic ratio Expired - Lifetime US3869602A (en)

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Cited By (11)

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US3988602A (en) * 1975-02-03 1976-10-26 Goodyear Aerospace Corporation Method and apparatus for enhancing data
US4101961A (en) * 1977-02-16 1978-07-18 Nasa Contour detector and data acquisition system for the left ventricular outline
US4240440A (en) * 1977-11-17 1980-12-23 Siemens Gammasonics, Inc. Method and apparatus for nuclear kymography providing a motion versus time display of the outer transverse dimensions of an organ
EP0066824A3 (en) * 1981-06-08 1983-02-09 General Electric Company X-ray image digital substraction system
US4521808A (en) * 1979-03-22 1985-06-04 University Of Texas System Electrostatic imaging apparatus
US5022063A (en) * 1989-01-25 1991-06-04 Hitachi Medical Corporation Multiple-mode scanning and beam current control x-ray TV apparatus
US5065435A (en) * 1988-11-16 1991-11-12 Kabushiki Kaisha Toshiba Method and apparatus for analyzing ventricular function
ES2087824A1 (es) * 1994-09-16 1996-07-16 Duque Rafael Aparicio Dispositivo perfeccionado para la determinacion rapida del indice cardiotoracico mediante banda graduada de material elastico.
FR2790657A1 (fr) * 1999-03-12 2000-09-15 Iodp Procede de mesure de l'epaisseur d'un muscle a partir d'une image
US20090196481A1 (en) * 2008-02-05 2009-08-06 Huanzhong Li Image processing method and apparatus
CN104732520A (zh) * 2015-01-31 2015-06-24 西安华海盈泰医疗信息技术有限公司 一种胸部数字影像的心胸比测量算法及系统

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NL7611419A (nl) * 1976-10-15 1978-04-18 Optische Ind De Oude Delft Nv Inrichting voor het uitlezen en verwerken van in- formatie vervat in beeldkaders, zoals gevormd door het achtereenvolgens vanuit meerdere rich- tingen met een in hoofdzaak platte bundel van kortgolvige straling, doorstralen van een object.
JPS5530835A (en) * 1978-08-25 1980-03-04 Takashi Katoda Method of forming heterogeneous junction in semiconductor
JPS57168579A (en) * 1981-04-08 1982-10-16 Fuji Photo Film Co Ltd Method and device for reading of picture information
JPS5876712A (ja) * 1981-10-31 1983-05-09 Shimadzu Corp Ｘ線検査装置
JP6082337B2 (ja) * 2013-10-30 2017-02-15 横河電機株式会社 心胸郭比算出装置

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Patent Citations (1)

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Cited By (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3988602A (en) * 1975-02-03 1976-10-26 Goodyear Aerospace Corporation Method and apparatus for enhancing data
US4101961A (en) * 1977-02-16 1978-07-18 Nasa Contour detector and data acquisition system for the left ventricular outline
US4240440A (en) * 1977-11-17 1980-12-23 Siemens Gammasonics, Inc. Method and apparatus for nuclear kymography providing a motion versus time display of the outer transverse dimensions of an organ
US4521808A (en) * 1979-03-22 1985-06-04 University Of Texas System Electrostatic imaging apparatus
EP0066824A3 (en) * 1981-06-08 1983-02-09 General Electric Company X-ray image digital substraction system
US5065435A (en) * 1988-11-16 1991-11-12 Kabushiki Kaisha Toshiba Method and apparatus for analyzing ventricular function
US5022063A (en) * 1989-01-25 1991-06-04 Hitachi Medical Corporation Multiple-mode scanning and beam current control x-ray TV apparatus
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FR2790657A1 (fr) * 1999-03-12 2000-09-15 Iodp Procede de mesure de l'epaisseur d'un muscle a partir d'une image
US20090196481A1 (en) * 2008-02-05 2009-08-06 Huanzhong Li Image processing method and apparatus
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CN104732520A (zh) * 2015-01-31 2015-06-24 西安华海盈泰医疗信息技术有限公司 一种胸部数字影像的心胸比测量算法及系统

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FR2152055A5 (enrdf_load_stackoverflow) 1973-04-20
JPS5116091B2 (enrdf_load_stackoverflow) 1976-05-21
JPS4834452A (enrdf_load_stackoverflow) 1973-05-18
GB1400471A (en) 1975-07-16
NL7211930A (enrdf_load_stackoverflow) 1973-03-06
DE2243449B2 (de) 1975-08-14
CA979074A (en) 1975-12-02
DE2243449A1 (de) 1973-03-22

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