UA125070C2 - Method of computed tomography - Google Patents

Abstract

A method of computed tomography includes the X-ray scanning of a lumen in a given angular range of a body part of an examined subject, conversion of X-rays passing at different angles through a selected part of a body into visible light; discrete perception of light flux by optoelectronic converters with the operating frequency specific to them and conversion of light beams into fragmentary analog video signals; their analog-to-digital conversion into fragmentary digital video signals; correction of brightness and geometric distortions of these video signals and their stitching into integral digital video signals which correspond to X-ray pictures of oblique projections of a body of an examined subject and serve as initial data for computer synthesis of tomograms. The optoelectronic transducers with an operating frequency of at least 250 frames per second are used to avoid blurring of X-ray images of moving organs and high-speed physiological processes; the fragmentary digital video signals are sequentially recorded in the buffer video memory, and their correction and stitching into integral digital video signals and computer synthesis of tomograms are performed after scanning.

Description

correction of brightness and geometric distortions of these video signals and their stitching into integral digital video signals, which correspond to radiological images of oblique projections of the subject's body and serve as input data for computer synthesis of tomograms. To avoid smearing of x-ray images of moving organs and high-speed physiological processes, optoelectronic converters with an operating frequency of at least 250 frames per second are used; fragmented digital video signals are sequentially recorded in the buffer video memory, and their correction and stitching into integral digital video signals and computer synthesis of tomograms are carried out after scanning. 1 X-ray emitter with a rectangular collimator Mm and" part | type still an spin

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Fig. 1

The invention relates to a computer tomography method based on recordings of a series of x-ray pictures, which are formed in short (usually from 2 to 16 s) time intervals by tomographs having flat multi-sensor digital receivers of x-ray radiation based on optoelectronic converters with partially overlapping fields of view.

This method is mainly intended for the diagnosis of moving organs (especially the heart against the background of tachycardia, aperiodic arrhythmia and tachyarrhythmia), rapid physiological processes (for example, local blood circulation in the brain and parts of the limbs) and for the examination of patients with involuntary convulsive activity.

Technical level

Computed tomography as a method of differential diagnosis of diseases and injuries of internal organs of humans and animals is well known (see, for example, Ziyeep5 R. Eipdatepia!5 oi teaisa! itadipa. -Satgidde Opimeg5yu Rgezv, 279 v., 2011). It includes: placement of at least part of the body of the examined subject (human or animal) between the X-ray nodes, that is, the X-ray emitter and the digital X-ray receiver; x-ray scanning into the lumen of the selected body part of the examined subject as at least the x-ray emitter is moved along a predetermined trajectory relative to the selected body part of the examined subject, receiving the x-ray radiation that has passed through each predetermined layer of the selected body part of the examined subject, and converting it into visible light, conversion of visible light into electrical signals, analog-difference conversion of these signals into digital video data and formation of each successive digital X-ray picture of an oblique projection of the subject's body and computer synthesis of tomograms based on a series of X-ray pictures.

Typical computer tomography software is generally available on the market (see, for example, 5 2008/0219567 A1). Programming the control mechanisms and electrical units used in tomographs is also not difficult. Therefore, many x-ray computer rooms of different purpose and design have already been created and put into operation

From tomographs.

However, the task of X-ray scanning for the lumen of the pulsating heart, arbitrary areas of the circulatory system with rapid blood circulation, and patients with involuntary convulsive activity has not yet been solved.

For example, the so-called cone-beam computer tomographs are known, each of which has a kinematic ring support connected to the rotation drive, where a controllable X-ray emitter and an X-ray receiver are fixed oppositely | see, for example: 1. YuOe bosk u., Meptyuz K., Sbotsybratsy 9., Map Reiedet 5., Noshyoii V., SazzeItap UM. Soper-rbreat sotryiva yutodgarnu: a pem/ Iom/ dose, podp gezoishiop itadipa iespppidne oi Te mlivi, rzhezepiaiop oi

Ingee sazez m/y Tesppidtse // 5Keiiia! VNadioiod. 2012. Mo. 41. M.1. years 93-96; 2. Vatanpiap-M/ipIt V.,

She is Mipog y. M., bsptinrinyi M., Uvapigoikh u., Mas Mapyop R., Meyop E., bozsy .).-S, Oieietapp ..-I,

Vietto a. Sope-reat sotryivea otoadgarpu aipgodgarpu: ap ippomaime todaiyu yoog yie emaIchaiiop oi mgivii Idatepi apa sapiade ipishiyev // ZKeieita! Vadioyudu 2012. M. 41. pp. 936-969; 3. A.Yu.

Vasiliev, N.N. Blynov (junior), E.A. Yegorova. Cone-beam computer tomography - a new research technology in traumatology // MEDICAL IMAGING Mo 4, 2012, p. 65-68.

Mem Tesppoiodu oi Nezeagsi ip Tgtashtaiiodu // MEPISAG IMASIMA. Me4, 2012, pp. 65-68) and many others

The openings in the ring supports of such tomographs are narrow and sometimes only slightly exceed the size of an adult's head. Therefore, they are intended for tomography of the cartilages and bones of the hands and feet, the joints of the hands and feet, and the skull, but in principle they are unsuitable for positioning the human body for the purpose of scanning the chest organs.

Placement of the torso (and even the examined subject as a whole for X-ray scanning of arbitrary parts of the body) is possible when using tomographs equipped with horizontal X-ray transparent tables.

Currently, two types of such tomographs are known.

Large specialized clinics usually have computed tomography scanners with ring-supported X-ray units, namely a controlled X-ray emitter with a slit collimator for forming a fan X-ray beam and a multisensor digital X-ray receiver (see, for example, 05 6,574,296). Each such support has a drive for continuous rotation around the x-ray transparent table, which in turn has a drive for reciprocating movement along the geometric axis of the ring support.

The rotation of the ring support with a frequency of 2-4 rpm around the table and the simultaneous linear movement of the table along the geometric axis of this support provide a spiral movement of the fan X-ray beam relative to the body of the examined subject.

Currently, spiral tomographs are known, which have a diameter of the lumen in the ring support of 78 cm, a length of a spiral line of X-ray sensors of 100 cm, which gives a tomography zone with a diameter of up to 60 cm, and up to 64 or more such lines (see, for example, VAYU VOK 2015. TnNe

Vadioiodu Scide yu Thesppoiodu apa Iptoptaiop ip Eigore, zesip "Sotriieg Totoagarnu", years 9-12, ezresiainu year 12). This makes it possible to synthesize the appropriate number of tomograms in one session lasting, as a rule, tens of seconds.

Unfortunately, these tomographs are quite complex in design and bulky, and therefore inconvenient in production and operation. Indeed, the ring support together with the X-ray nodes is massive and cannot work in the start-stop mode. Therefore, the X-ray emitter must work continuously in each diagnostic session.

Municipal hospitals are often equipped with significantly cheaper and easier-to-maintain computer tomographs, in which the X-ray units are oppositely fixed on parallel horizontal protrusions of C-shaped supports | see, for example, the educational manual "Computer Tomography" on the website "Ner/Lymly.gadioiiapa. pei.pa/sopiepia-11 2-radei.piti", figure 1.1 (ip EEpaiivy "Sotrshiei Totodgarpu", Gen. 1.13). Such supports have drives for oscillating motion relative to stationary tables in a given angular range. They have little inertia compared to ring supports and can work in start-stop mode.

The slit X-ray emitter can be pulsed, which reduces the dose load on the examined subjects. However, even the continuous operation of this emitter during the diagnostic session does not lead to over-irradiation, because the pyramidal X-ray beam moves in a narrow sector (usually 207), its angular velocity is insignificant, and the duration of the sessions, as a rule, does not exceed 6 s.

Such computer tomographs can be equipped with multi-sensor digital X-ray receivers based on optoelectronic converters with partially overlapping fields of view. The principle of operation of such receivers was disclosed in patents OA 22127 and VO 2127961 based on PCT/OA 96/00016 (MO 98/11722). It includes:

From (1) conversion of the X-ray flux, which passed through a given layer of the body of the examined subject, into a visible light flux, (2) discrete perception of the light flux by a set of optoelectronic converters, the fields of view of which partially overlap, and the conversion of light beams into fragmentary analog video signals, (3) conversion of fragmented analog video signals into fragmented digital video signals, which are received for further processing.

This processing traditionally includes: (4) correction of brightness and such geometric distortions of fragmentary digital video signals, which are due to errors in the size and installation of optoelectronic converters and partial overlap of their fields of view, and (5) stitching of each consecutive set of corrected fragmentary digital video signals into a complete output digital video signal , which is either a single radiograph that can be recorded for subsequent reproduction and analysis, or part of a series of radiological images for computed tomography.

All these operations are performed in real time.

Video cameras initially served as optoelectronic converters, and later photodiode matrices with an operating frequency of no more than 30 frames per second.

The same optoelectronic converters were used in multisensor digital X-ray receivers in the form of two or three flat sections joined at obtuse angles (see M/O0/2017/200507 and OA 117599 based on PCT/OA 2016/000065).

In the same documents, a linear pyramid-beam X-ray tomograph with a C-shaped support of X-ray nodes and a movable X-ray transparent table was disclosed.

This provides x-ray scanning for the lumen in an angular range of 45", when the table is perpendicular to the geometric axis of the horizontal shaft of the C-shaped support, and even up to 110", when the table is located along this geometric axis.

The functional analysis of the design and the description of the work of the specified tomograph allow us to reveal the method of computer tomography, which is closest to the method proposed below in terms of technical essence. This known method includes:

(1) placing a part of the subject's body in front of a multi-sensor digital x-ray receiver based on a plurality of optoelectronic transducers with partially overlapping fields of view; (2) X-ray scanning for the lumen in a given angular range of the selected part of the subject's body using an X-ray emitter with a rectangular collimator; (3) conversion of X-ray radiation passing at different angles through the selected part of the subject's body into a visible light stream; (4) discrete perception of the light flow by optoelectronic converters such as video cameras or photodiode matrices with a typical operating frequency of about 30 frames per second and conversion of light beams into fragmentary analog video signals; (53 conversion of fragmentary analog video signals into fragmentary digital video signals; (6) correction of brightness and such geometric distortions of fragmentary digital video signals, which are caused by errors in the dimensions and installation of optoelectronic converters and partial overlap of their fields of view; (7) stitching of corrected fragmentary digital video signals into integral digital video signals corresponding to X-ray images of oblique projections of the subject's body, and (8) computer synthesis of tomograms based on a series of X-ray images.

This method, all operations of which are performed in real time, is sufficient for obtaining high-quality tomograms in most diagnostic studies of immobile or immobile organs.

However, when examining a pulsating heart (especially against the background of tachycardia, aperiodic arrhythmia and tachyarrhythmia), rapid physiological processes such as local blood circulation and patients with involuntary convulsive activity, X-ray pictures based on fragmentary analog video signals, each of which has a duration of about 30 milliseconds, are blurred. This worsens the distinction of details and significantly complicates (and sometimes excludes) correct diagnosis.

It can be shown that this drawback can be easily eliminated by using modern ones

From optoelectronic converters with an operating frequency of 250 and more frames per second with a duration of each individual video signal less than 4 ms (m/mlu.5opu.pei/siv-ipaivigu).

Unfortunately, other restrictions apply in this case.

Thus, there are well-known optoelectronic converters based on KMON structures (that is, complex metal-oxide-semiconductor structures, in English SMO5). They are able to generate streams of video information at the outputs with an average intensity of at least 130 megapixels per second.

It is known that the formation of a complete output digital video signal usually requires the simultaneous operation of approximately 100 identical optoelectronic converters. Therefore, the intensity of the output stream of video data in the case of using KMON-structures will be approximately 13 giga-pixels per second. This many times exceeds the bandwidth of personal computer interfaces, which at a clock frequency of up to 10 GHz is no more than 300 megapixels per second.

Brief summary of the essence of the invention

The invention is based on the task of improving the mode and order of performing operations to create a computer tomography method that avoids smearing of X-ray images during examination of moving organs and high-speed physiological processes.

The task is solved by the computer tomography method, which includes: (1) placing a part of the subject's body in front of a multi-sensor digital X-ray receiver based on a set of optoelectronic transducers with partially overlapping fields of view; (2) X-ray scanning for the lumen in a given angular range of the selected part of the subject's body using an X-ray emitter with a rectangular collimator; (3) conversion of X-ray radiation passing at different angles through the selected part of the subject's body into a visible light stream; (4) discrete perception of light flow by optoelectronic converters with their characteristic operating frequency and conversion of light beams into fragmentary analog video signals; (53 conversion of fragmented analog video signals into fragmented digital video signals;

(6) correction of brightness and such geometric distortions of fragmentary digital video signals, which are caused by errors in the dimensions and installation of optoelectronic converters and partial overlapping of their fields of view; (7) splicing of corrected fragmentary digital video signals into integral digital video signals corresponding to X-ray images of oblique projections of the subject's body; and (8) computer synthesis of tomograms based on a series of radiological pictures. according to the inventive idea, optoelectronic converters with an operating frequency of at least 250 frames per second provide discrete perception of light flux and conversion of light beams into fragmentary analog video signals; fragmentary digital video signals are sequentially recorded in the buffer video memory and delayed in it until the completion of X-ray scanning, and only then correction of brightness and geometric distortions of fragmentary digital video signals, stitching of corrected fragmentary digital video signals into complete digital video signals and computer synthesis of tomograms are carried out.

As can be seen from what has been said, the proposed method involves separating the processes of video data formation from the processes of their transformation into tomograms. Under such conditions, the formation of fragmented digital video signals and their buffering at a speed of at least 250 frames per second before transmission to the synthesis of tomograms make it possible: first, to receive in a few seconds clear, unsmeared frames of X-ray images of oblique projections of the pulsating heart even in states of tachycardia, aperiodic arrhythmias or tachyarrhythmias and patterns of pulse waves in local areas of the circulatory system (with a corresponding increase in the quality of tomograms and the accuracy of diagnosis of diseases of the cardiovascular system) and, secondly, to receive such a bonus as minimizing the dose load on patients.

The first additional difference is that the specified x-ray scan of the selected body part of the examined subject in a given angular range is performed by linear movement of the rotary x-ray emitter along the frontal plane of the fixed x-ray receiver. This makes it possible to economically implement the method on slightly modernized basic ones that are easy to manufacture and maintain

From X-ray systems that are common in medical institutions, including stationary and mobile outpatient clinics.

The second additional difference is that the body of the examined subject is scanned with X-rays in the angular range of 5 207 This is usually enough for an accurate examination of the pulsating heart.

The third additional difference to the second is that the specified x-ray scan of the selected body part of the examined subject in the given angular range is performed by the synchronous angular movement of the oppositely fixed specified x-ray receiver and the specified x-ray emitter with a rectangular collimator. This makes it possible to implement the method on pyramidal X-ray tomographs available in many clinics, equipped with C-shaped supports of X-ray units and drives for their oscillating movement.

The fourth additional difference is that the examined subject is scanned with X-rays in the angular range - 1107 This allows for the examination of large farm animals (for example: breeding bulls, breeding and sports horses, etc.).

Brief description of the drawings

Next, the essence of the invention is explained by a detailed description of the computer tomography method using examples of its hardware implementation with references to the attached drawings, which are shown in: fig. 1 - a structural diagram of the computer tomography video tract, which is minimally necessary for the implementation of the method; Fig. 2 - a modernized single-stand basic X-ray system of a computer tomography (with a horizontal arrangement of the C-shaped support of X-ray nodes); fig. C is the same as in fig. 2 (with a vertical arrangement of the C-shaped support). The best options for implementing the invention

For the implementation of the proposed method, any computer tomograph is suitable, the video path of which, at a minimum, has (see Fig. 1): an X-ray emitter 1 with a rectangular collimator, a flat multi-sensor digital receiver 2 of X-ray radiation, which includes sequentially located along the beam : an unmarked particularly radiolucent front wall, because the X-ray optical converter 3,

a set of optoelectronic converters 4 with partially overlapping fields of view, which are fixed in the slots of the board 5, which is opaque to residual X-ray radiation, and which, in particular, are used by KMON structures of the IMX287 IA model of the 5OMU company, corresponding to the 1/3 inch standard and capable of forming fragmentary analog video signals of size 728(H) x 544(M) with an operating frequency of 330 frames per second with a duration of each individual video signal of about 3 ms) (m/mluy.vopu.pe/siv-ipdvigu), analog-to-digital converters (ADC) 6, mounted on the rear side of the board 5 along the path of light and connected to the outputs of the optoelectronic converters 4; programmable microprocessors 7, which are also mounted on the back side of the board 5, are connected to the information outputs of the ADC 6 and are designed for the rapid transfer of fragmentary digital video signals for temporary storage during the X-ray scan and their transfer after scanning for the correction of brightness and geometric distortions and stitching into integral digital video signals ; cells of 8 buffer video memory (in particular, UNO type), which are connected to programmable microprocessors by 7 lines capable of working in direct and feedback modes; block 9 of connecting programmable microprocessors 7 to a personal computer (PC) 10, which has software necessary for correction and stitching of corrected fragmentary video signals into integral digital video signals corresponding to radiological pictures of individual oblique projections, and for the synthesis of tomograms.

Programmable microprocessors 7 can be 32-bit gate matrices Mioz EII with operational programming (ERSA) and calculations with a reduced set of instructions (VZS) of the IPega company (pOIRz/lLiumum.anega.sot/rgodisiv/rgosev55og5/5irroi.piti). These matrices have built-in timers that can be set to an arbitrary operating frequency, memory controllers and interfaces.

The memory controllers of the microprocessors 7 are programmed to generate commands for recording frames (that is, fragmentary digital video signals) in the cells 8 of the video buffer memory, taking into account the actual operating frequency of the optoelectronic converters 4, and the interfaces of these microprocessors 7 are set: only to record these frames in the cells 8 during every regular x-ray session

From scanning and only for reading the previously recorded frames from these cells 8 and their transfer through the unit 9 of the connection to the PC 10 after the X-ray scanning session is completed.

A computer tomograph for implementing the method can be built, for example, on the basis of a single-stand digital X-ray diagnostic complex MIMAT Ogai of the Swiss company Khgau Zmivv (PYr://Lymly.khgau-5miv5.sp).

The mechanical part of such a modernized tomograph has (see Figures 2 and 3): a standard vertical rack 11 with not particularly marked longitudinal guides; the first carriage 12, which is installed in the mentioned guides of the rack 11 with the possibility of controlled vertical reciprocating movement and locking at a given level;

A C-shaped support, which can be turned left-right relative to the horizontal axis, is installed on the carriage 12 and has a crossbar 13 with not particularly marked radially oriented longitudinal guides and opposite horizontal protrusions 14, installed in these longitudinal guides with the possibility of synchronous adjustment closer or farther apart.

On one of the protrusions 14 with the possibility of controlled reciprocating movement, a second carriage 15 is installed, which carries a rotary X-ray emitter 1 with a rectangular collimator, and on the other protrusion 14, a multi-sensor digital receiver 2 of X-ray radiation is rigidly fixed.

In addition, a gurney with a radiolucent table, not particularly shown, may be included in the tomograph kit.

The proposed method is carried out in three stages.

The first, preparatory, stage includes the following operations: (1) installation of the first carriage 12 (and, accordingly, the C-shaped support of the X-ray nodes) at the required level and its locking relatively stable 11; (2) bringing the C-shaped support of the X-ray nodes 1 and 2 into one of the two initial configurations by turning 90", namely: (2.1) or into the configuration according to Fig. 2, when both horizontal protrusions 14 are located at the same height, the receiver 2 of X-ray radiation is fixed vertically in the middle of one projection 14, and the second carriage 15 together with the rotary X-ray emitter 1 is brought to one of the extreme positions on the other projection 14 (this is convenient for examining patients in a standing position);

(2.2) or in the configuration according to fig. 3, when both horizontal protrusions 14 are located in the same vertical plane, and the receiver 2 of X-ray radiation and the second carriage 15, together with the X-ray emitter 1, are fixed in the middle of the corresponding protrusions 14 (this is necessary for examining patients in a lying position on an X-ray transparent table, not shown here, which can be inserted into the gap between the emitter 1 and the receiver d); (3) if necessary - adjustment of the gap between the emitter 1 and the receiver 2 by synchronously moving the protrusions 14 in the mentioned guides of the crossbar 13; (4) the location of the examined subject in the gap between the emitter 1 and the receiver 2 (while the standing subject must lean against the radiolucent wall of the receiver 2, and the lying subject must be fixed on the mentioned radiolucent table from accidental displacement during the X-ray scan of the selected body parts); The second stage, performed in real time, includes: (5) turning on the power of the X-ray emitter 1 with a rectangular collimator and continuous X-ray scanning on the lumen of the selected part of the body of the examined subject in a given angular range, namely (5.1) or preferably in the interval x 207 by linearly moving the emitter 1 from one edge of the protrusion 14 to the other edge and turning the pyramidal X-ray beam as it moves (see Fig. 2), (5.2) or preferably in the interval 51107 by synchronously turning to the left or right the crossbar 13 and the oppositely fixed on it emitter 1 and receiver 2 of X-ray radiation (see Fig. 3); (b) formation of a continuous visible light stream by the x-ray optical converter C as the pyramidal x-ray beam passes at different angles through the selected part of the subject's body; (7) discrete perception of light flux by optoelectronic converters 4 with their characteristic operating frequency (in particular, with a frequency of at least 250 frames per second) and conversion of light beams into fragmentary analog video signals; (8) conversion of fragmentary analog video signals of ADC 6 into fragmentary digital video signals; (9) sequential recording of fragmentary digital video signals using programmable microprocessors 7 in the buffer video memory 8 and delay in it until completion of the X-ray scan of the selected part of the subject's body.

The third stage includes operations performed in accordance with the technical capabilities and software of the PC 10, namely: (10) correction of brightness and such geometric distortions of fragmentary digital video signals, which are caused by errors in the size and installation of optoelectronic converters and partial overlapping of their fields of view; (11) splicing of the corrected fFragmentary digital video signals into integral digital video signals corresponding to X-ray images of oblique projections of the subject's body; and (12) computer synthesis of tomograms based on a series of radiological pictures.

Industrial suitability

The industrial applicability of the invention is due to the availability of hardware for implementing the proposed method.

Claims (5)

FORMULA OF THE INVENTION 1. The computer tomography method, which includes: (1) placing a part of the subject's body in front of a multi-sensor digital X-ray receiver based on a set of optoelectronic converters with partially overlapping fields of view; (2) X-ray scanning for the lumen in a given angular range of the selected part of the subject's body using an X-ray emitter with a rectangular collimator; (3) conversion of X-ray radiation passing at different angles through the selected part of the subject's body into a visible light stream; (4) discrete perception of light flow by optoelectronic converters with their characteristic operating frequency and conversion of light beams into fragmentary analog 60 video signals; (5) conversion of fragmented analog video signals into fragmented digital video signals; (6) correction of brightness and such geometric distortions of fragmentary digital video signals, which are caused by errors in the dimensions and installation of optoelectronic converters and partial overlapping of their fields of view; (7) stitching of corrected fragmentary digital video signals into integral digital video signals corresponding to radiological images of oblique projections of the subject's body; and (8) computer synthesis of tomograms based on a series of X-ray pictures, which is distinguished by the fact that discrete perception of light flux and conversion of light beams into fragmentary analog video signals are provided by optoelectronic converters with an operating frequency of at least 250 frames per second; fragmentary digital video signals are sequentially recorded in the buffer video memory and delayed in it until the completion of X-ray scanning, and only then correction of brightness and geometric distortions of fragmentary digital video signals, stitching of corrected fragmentary digital video signals into complete digital video signals and computer synthesis of tomograms are carried out. 2. The method according to claim 1, which differs in that the specified X-ray scan of the selected body part of the examined subject in the given angular range is performed by linear movement of the rotary X-ray emitter along the frontal plane of the fixed X-ray receiver. 3. The method according to claim 2, which differs in that the examined subject is scanned with X-rays in an angular range of 20". 4. The method according to claim 1, which differs in that the specified X-ray scan of the selected body part of the examined subject in the given angular range is performed by synchronous angular movement of the oppositely fixed specified X-ray receiver and specified X-ray emitter with a rectangular collimator. 5. The method according to claim 4, which is characterized by the fact that the examined subject is scanned with X-ray Zo rays in the angular range of -110". . X-ray emitter with a rectangular collimator Pi pi z 7 part | still Z 4. Y 4 in x Where ! - ; shi KO / УК, "7 r Ah M g y "Unineuezhe vyt nin nan kozhykyk y I bagatasensornyy soci non b dennnky ; ach and receiver of Renteniv SAD AI TD h/ oon SPA DDEEAT KN pen tenet rya market and myh miv - p sums KM: dreams! ! cha r | | zh» m, 00 1 to programmable microprocessors 7 in cy | ! ADC! ; and Y Y I nn 7 programmable | | 7 programmable microprocessor microprocessors and theirs, Y r h yoOnya V sa M r y y chik uncle V cells M u 8 cells buffer kch r buffer video memory Kk i vidromamyti 9 connection unit ty personal computer Fig. 1