• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    A positron emission tomography camera having a plurality of detector planes positioned side-by-side around a patient area to detect radiation. Each plane includes a plurality of photomultiplier tubes (60c, 62c, 64c) and at least two rows of scintillation crystals on each photomultiplier tube extend across to adjacent photomultiplier tubes for detecting radiation from the patient area. Each row of crystals on each photomultiplier tube is offset from the other rows of crystals, and the area of each crystal on each tube in each row is different than the area of the crystals on the tube in other rows for detecting which crystal is actuated and allowing the detector to detect more interplane slices. The crystals are offset by an amount equal to the length of the crystal divided by the number of rows. The rows of crystals on opposite sides of the patient may be rotated 90 degrees relative to each other.
    公开号:SU1716947A3
    申请号:SU864028209
    申请日:1986-08-22
    公开日:1992-02-28
    发明作者:Абдул-Муллани Низар
    申请人:Клэйтон Фаундейшн Фор Рисерч (Фирма)；
    IPC主号:
    专利说明:

    A known positron tomography chamber with a plurality of detector planes, for example, in the form of rings or plates, located one next to the other around the patient area and intended to detect radiation emanating from this zone. Each plane contains a multitude of scintillation detectors directed to a specific area of the patient’s body, and each plane detects a straight layer that intersects areas of the patient’s body and coincides with the plane of the detectors. Each two adjacent detector planes define a layer in the area of the patient's body, located between the planes of the detectors. Each detector plane contains a multitude of photomultipliers and at least two rows of scintillation crystals on each photomultiplier.
    Rows of crystals are located across the photomultipliers to detect radiation of a specific area of the patient's body, which is converted by these photomultipliers into electrical pulses, and the photomultipliers perceive the light of all the rows of crystals located on each photomultiplier. Each row of crystals on each photomultiplier is shifted relative to other rows of crystals, and the zone of each crystal on each photomultiplier in each row is different from the zones
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    photomultiplier crystals in other rows, which makes it possible to detect exactly which crystal is excited, and makes it possible to study with the help of detectors of a larger number of layers.
    The purpose of the invention is to increase the information content.
    The invention consists in that the rows of crystals located on opposite sides of the patient's body area are rotated 90 ° one relative to the other, which provides improved sampling for the combined detectors.
    The magnitude of the crystal displacement is equal to the length of the crystals divided by the number of rows.
    Each row of crystals is shifted relative to neighboring rows of crystals by an equal amount.
    Alternating rows of crystals are shifted relative to adjacent rows of crystals in opposite directions.
    FIG. 1 shows one of the variants of the proposed camera for positron tomography, a general view; in fig. 2 - display of direct and interplanar layers in a known positron chamber, section; in fig. 3 is a section A-A in FIG. 2; in fig. 4 — camera with a large number of mappings of direct and interplanar layers, section; in fig. 5 is a section BB in FIG. four; in fig. 6 shows direct and interplanar layers; in fig. 7 is a sectional view BB in FIG. 6; in fig. 8 - the first version of the detecting device, section. Increased scale; in fig. 9 - the second variant of the detecting device, section, increased scale; in fig. 10 - device, one of the options, an increased scale; in fig. 11 - the third variant of the detecting device, section, increased scale; in fig. 12 - the fourth version of the detecting device, section, increased scale; in fig. 13 is a variant of the arrangement of detectors for creating a planar combined image of an object, a section.
    FIG. 1 reference number 10 denotes a positron tomography camera with a bed or portal 12, the set of detector planes 14 of which in this case are shown in the form of three rings. However, other variants, such as opposing plates located on opposite sides of the patient’s body area 16, can be used to detect radiation from this area. Zone 16 may also include a bed 18 for the patient, mounted with the possibility of tilting and / or turning to scan the body from several different positions,
    To increase scanning capabilities, the portal can create vibrations. The detectors detect the radiation injected into the body, for example, rubidi -82.
    FIG. 2 and 3 shows a typical section
    positron camera with a window for entering the patient to be scanned and a plurality of detectors 22 for each detector plane 14 installed
    0 around the circumference of zone 16 of the patient’s body to detect radiation emanating from this zone 16.
    Typical detector 22 contains a photomultiplier 38, a scintillation crystal
    5 40 and partitions 32. The crystal 40 converts the detected radiation into light, transmitted to the photomultiplier 38 to convert the detected radiation into electrical pulses. Usually to one
    0 the photomultiplier 38 holds one crystal 40.
    A typical known camera has three planes with detectors 22, of which each detector contains a photomultiplier 38 with one crystal. Such a device makes it possible to obtain a total of five layers or images of sections of the patient’s body. So. the opposing detectors 22 create straight layers 42, 44 and 46. Located
    0 between the planes, the layers, e.g. 48 and 50, are summed to form one intermediate layer 52. Similarly, the transverse layers 54 and 56 create an intermediate layer 58 when added together.
    5 Consequently, the known chambers make it possible to obtain a number of layers that is twice the number of rows of detectors, minus one. For higher resolution in positron
    In chambers, detector sizes are reduced, however, the number and size of detectors remain limiting factors.
    The proposed photomultiplier works with more than one scintillation
    5 crystal, and the crystals are arranged in such a way as to facilitate their identification, this increases the number of image planes, reduces the effective size of the detector, with a concomitant increase in resolution by half or more and cheaper cameras due to the fact that in comparison with the known devices approximately half or less than the total number of photomultipliers.
    FIG. 6 and 7, photomultipliers 60, 62 and 64 located in the chamber 10 and various parallel planes 14 are shown. As planes 14, rings may be used that are located in planes extending across the longitudinal axis of the patient’s body 16 zone (see Fig. 1 ), or located one opposite the other from opposite sides of the zone 16 of the plate 15 and 17.
    In addition, around the inner circumference of photomultipliers 60, 62 and 64, for detecting radiation from zone 16, there is a multitude of scintillation crystals of any appropriate type for converting this radiation into light, which is converted by photomultipliers into electrical pulses. The crystals are located in a certain position relative to the photomultipliers 60, 62 and 64, as a result of which each photomultiplier perceives the light of more than one crystal.
    Crystals 1, 2 and 3 are in the area of view of only photomultipliers 60, 62 and 64, respectively. Crystals 1, 2 and 3 cover 1/2, i.e. The top half of each photomultiplier in each of the planes 14. However, crystal 4, adjacent to photomultipliers 60 and 62, is in their field of view, and crystal 5 is in the field of view of photomultipliers 62 and 64.
    Such a device makes it easy to identify a specific crystal. For example, the photomultiplier 60 reacts to the excitation of the crystal 1. Similarly, only the photomultiplier 62 reacts to the excitation of the crystal 2 and only the photomultiplier 64 reacts to the excitation of the crystal 3. However, the reaction of both photomultipliers 60 and 62 identifies the crystal 4. Similarly, the crystal 5 causes the response of both photomultipliers 62 and 64. This design also provides an increase in resolution as a result of reducing the size of crystals 1-5 compared to a normal size by half, since a normal crystal must cover the entire photomultiplier surface. Such a design and method requires the use of almost half the number of photomultipliers for both detectors and for identifying crystals. The cost reduction is due to the lower cost of smaller crystals compared to larger ones. In addition, improved data sampling in the layer direction is provided.
    Another significant sign due to a certain position of the crystals relative to the photomultiplier is an increased number of image planes as a result of improved data sampling due to the displacement of the first row of crystals 1, 2 and 3
    with respect to the second row of crystals 4 and 5. The chamber (Tables 2 and 3} with three rows of detectors makes it possible to obtain three direct layers and two effective intermediate layers. However, the proposed chamber (Fig. 4-7), where crystals 4 and 5 are displaced relative to crystals 1, 2 and 3, nine effective layers are obtained, of which five are direct and four are effective intermediate layers. The direct layers are indicated by reference numbers 70, and the effective intermediate layers - numbers 72. FIG. 8 shows a device with four planes 14 or rings. With photocummers 5, the knife sets 60c, 62c, 64c and 65c, respectively, reacting to the light of three rows of crystals. The crystals 1c, 2c, 3c, 4c, 5c, 6c, 7c, 8c, 9c and 10c form horizontal rows passing across planes 14 c. If desired, the crystals can be located around the circumference of each ring, i.e. not horizontally, as shown in Fig. 8, but vertically.
    5 photomultiplier 60c. The chip 5c is identified by the signal of the photomultiplier 62c, which is larger than the signal emitted by the photomultiplier 60c. Similarly, an 8c crystal is identified
    0 by the signal from the photomultiplier 60c, which is larger than the signal emitted by the photomultiplier 62c. The procedure for identifying other crystals does not differ from that indicated. Shown in FIG. The 8th option provides enhanced resolution, more efficient sampling in image planes and is cheaper as a result of using common photomultipliers.
    0 In these embodiments, multiple scintillation crystals are used, located in each plane next to the photomultipliers to detect radiation, and the crystals are set
    5 on the photomultiplier in such a way that each photomultiplier perceives the light of more than one crystal. Each row of crystals on each photomultiplier is located with a certain shift relative to the other rows of crystals, and the zone of each crystal in each row on the photomultiplier differs from that of the other rows of this photomultiplier, which allows us to determine which particular crystal
    5 is excited, and a greater number of planar layers are detected using detectors. In a preferred embodiment, the magnitude of the crystal shift is equal to the length of the crystal divided by the number of rows. According to FIG. 4-7 rows of crystals 1, 2 and 3
    shifted relative to the row of crystals 4 and 5 by a distance equal to 1/2 the length of a single crystal. FIG. 8 shows three rows of crystals, spaced a distance equal to 1/3 of the crystal length. Although FIG. 8 shows crystals whose width is such that the total width of several rows is equal to the width of the photomultiplier tube; photomultipliers of larger or smaller sizes can be used, located between the rows of crystals and photomultiplier tubes of the light guide. In this case, the total width of the crystal row can be either more or less than the width of the photomultiplier tube,
    You can use other device variants with more than four rows of crystals arranged with a relative shift. FIG. Figure 9 shows a device with square or round tubes of photo multipliers, with square or round fibers, in which the relative shift of rows 80, 82, 84 and 8 is equal to 1/4 of the length of a single crystal. In this case, the magnitude of the shift of each of the p - ds 80, 82, 84 and 86 relative to the corresponding adjacent row is equal to 1/4 the length of one of the crystals.
    More preferable than that shown in FIG. 9. A variant of the device with four rows of crystals is shown in FIG. 10. In this embodiment, the magnitude of the relative shift of rows 90, 92, 94, and 96 is 1/4 of the length of the crystal, similar to the device in FIG. 9, to detect and measure crystal radiation and obtain a larger number of interplanetary layers. However, unlike the device shown in FIG. 9, the device shown in FIG. 10 provides improved sampling. The difference between these devices lies in the fact that alternating rows 90 and 94 are shifted relative to neighboring rows 92 and 96 in the direction opposite to the shift direction of neighboring rows 92 and 94.
    Similarly to FIG. 11 and 12 show a device with six rows of crystals extending across the tubes of photomultipliers 60f, 62f, 64f, which in the preferred embodiment have a square end, with each tube of photomultipliers 60f, 62f, 64f having six passing across to adjacent photomultipliers rows of 100, 102, 104, 106, 108, and 110, and the photomultipliers perceive the light of all rows of crystals.
    According to FIG. 11, the value of the relative shift of the rows is equal to 1/6 of the length of a single crystal. Fig. 12 shows a similar image of the device, each photomultiplier in which has six rows of crystals 108, 110, 112, 114, 116, and 118 arranged displaced from each other by a distance equal to 1/6 of the length of the crystal
    However, unlike the device shown in FIG. 11, in the device shown in FIG. 12, alternating rows of crystals are shifted in opposite directions (see 108, 112, 166 and 110, 1414 and 118), which also makes it possible to obtain an improvement compared with the device shown in FIG. 11, the sample
    Although in all of these embodiments, the rows of crystals lie in a horizontal plane, all of these rows can be rotated 90 ° and can pass vertically, which makes it possible to obtain thinner straight layers, an increased interplanar resolution and an improved sample in the plane.
    FIG. 13 shows detectors located in two plates 120 and 122 on opposite sides of a patient’s body area 16, similar to that shown in FIG. 6 plates 15 and 17, shown in FIG. 6 plates of detectors with coincident crystals arranged with a relative shift allow to improve the sample and reduce the cost of the detectors. However, according to FIG. 13 on one of the plates, for example plate 120, arranged with a relative shift of a row of crystals, passes in a vertical direction, and on plate 122, located with a relative shift of a row of crystals, passes in a horizontal direction, i.e. the detectors of the opposite plates 120 and 122 are rotated 90 ° one relative to the other. Such a device provides improved sampling for matching detectors.
    Thus, each of the plates 120 and 122 is provided with a plurality of photomultipliers 60h, 62h, 64h located in different planes 14h, 14i and 14j, respectively. The detectors 60h allow to obtain one straight layer passing through the patient body area 16, the detectors 62h - the second straight layer and the detectors 64h - the third straight layer.
    In this embodiment, each photomultiplier is equipped with two rows of crystals arranged with a relative shift, similar to those shown in FIG. 4-7. Obviously, you can use a different number of rows. Arranged with a relative shift, the rows of crystals of one plate, such as plate 120, extend in a vertical direction, Tak; rows 124 and 126 extend vertically across photomultipliers 60g. 62h and 64h. The magnitude of the relative shift of adjacent rows is 1/2 the length of a single crystal. The rows 128 and 130 of the second plate 122 extend horizontally across each horizontal row of the photomultipliers 60h, 62h and 64h. The rows 128 and 130 are also arranged with a relative shift, the size of which is equal to 1/2 the length of one of the crystals.
    权利要求:
    Claims (4)
    [1]
    1. A positron tomography chamber containing a plurality of detector arrays located adjacent to one another, with each scattering detector containing a plurality of scintillation detectors with photomultipliers, and the detectors located on opposite sides of the patient placement area and directed to this zone, each detector plane provides registration of a planar layer, and every two adjacent detector planes provide an interplanar layer registration, each photomultiplier is connected in less In a measure with two rows of scintillation crystals, each row of crystals of each photomultiplier is shifted relative to the other rows of crystals, for each photomultiplier the crystal zones associated with the photomultiplier are different for each row, differing from increasing informativity, rows of crystals on opposite sides of the patient placement area are rotated 90 ° relative to each other.
    [2]
    2. A camera according to claim 1, characterized in that the crystals are offset by an amount equal to the length of the crystals divided by the number of rows associated with each photomultiplier.
    [3]
    3. The camera according to claim 1 or 2, characterized in that in adjacent rows the crystals are shifted by the same amount,
    [4]
    4. The camera according to claim 1, from which the alternating rows of crystals are displaced from adjacent rows of crystals in the direction opposite to the displacement in adjacent rows.
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    引用文献:
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    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    US06/768,906|US4642464A|1984-05-24|1985-08-23|Positron emission tomography camera|
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