JPH04292145A - X-ray ct device - Google Patents
X-ray ct deviceInfo
- Publication number
- JPH04292145A JPH04292145A JP3057066A JP5706691A JPH04292145A JP H04292145 A JPH04292145 A JP H04292145A JP 3057066 A JP3057066 A JP 3057066A JP 5706691 A JP5706691 A JP 5706691A JP H04292145 A JPH04292145 A JP H04292145A
- Authority
- JP
- Japan
- Prior art keywords
- output
- integrator
- switch
- ray detector
- ray
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 239000003990 capacitor Substances 0.000 claims abstract description 37
- 230000003321 amplification Effects 0.000 claims abstract description 12
- 238000003199 nucleic acid amplification method Methods 0.000 claims abstract description 12
- 238000005259 measurement Methods 0.000 abstract description 8
- 230000010354 integration Effects 0.000 abstract 1
- 238000010586 diagram Methods 0.000 description 4
- 238000013139 quantization Methods 0.000 description 3
- YBIDYTOJOXKBLO-USLOAXSXSA-N (4-nitrophenyl)methyl (5r,6s)-6-[(1r)-1-hydroxyethyl]-3,7-dioxo-1-azabicyclo[3.2.0]heptane-2-carboxylate Chemical compound C([C@@H]1[C@H](C(N11)=O)[C@H](O)C)C(=O)C1C(=O)OCC1=CC=C([N+]([O-])=O)C=C1 YBIDYTOJOXKBLO-USLOAXSXSA-N 0.000 description 1
- 210000001015 abdomen Anatomy 0.000 description 1
- 238000010521 absorption reaction Methods 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 238000003384 imaging method Methods 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- 238000009738 saturating Methods 0.000 description 1
Landscapes
- Apparatus For Radiation Diagnosis (AREA)
Abstract
Description
【0001】0001
【産業上の利用分野】本発明は、特に測定精度の改善を
図ったX線CT装置に関するものである。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an X-ray CT apparatus with particularly improved measurement accuracy.
【0002】0002
【従来の技術】図2はX線CT装置の概略構成を示す回
路図である。図2において、1はX線源、2は被検体、
3は被検体2を挟んでX線源1に対向配置され、X線源
1と一体に回転する多チャンネル構成のX線検出器であ
る。2. Description of the Related Art FIG. 2 is a circuit diagram showing a schematic configuration of an X-ray CT apparatus. In FIG. 2, 1 is an X-ray source, 2 is a subject,
Reference numeral 3 denotes an X-ray detector having a multi-channel configuration, which is disposed opposite to the X-ray source 1 with the subject 2 in between, and rotates together with the X-ray source 1.
【0003】図示構成において、X線管1から照射され
たX線は、被検体2を透過し、その透過X線が検出器3
に入射する。検出器3は、入射X線量に応じた電荷を発
生させ、その電荷はコンデンサ4に蓄えられる。このコ
ンデンサ4に蓄えられた電荷はスイッチ5をONするこ
とによって次段に与えられる。In the illustrated configuration, X-rays emitted from an X-ray tube 1 are transmitted through a subject 2, and the transmitted X-rays are transmitted to a detector 3.
incident on . The detector 3 generates an electric charge according to the amount of incident X-rays, and the electric charge is stored in the capacitor 4. The charge stored in the capacitor 4 is given to the next stage by turning on the switch 5.
【0004】このようなコンデンサ4及びスイッチ5は
、検出器3のチャンネル数だけ用意されており、各コン
デンサ4に蓄えられた電荷は、スイッチ5を1つずつO
Nして行くことによって、オペアンプ6と積分コンデン
サ7で構成される積分器8に与えられる。The number of such capacitors 4 and switches 5 is equal to the number of channels of the detector 3.
N, the signal is applied to an integrator 8 composed of an operational amplifier 6 and an integrating capacitor 7.
【0005】積分器8は、その積分コンデンサ7の容量
で決まる増幅率で入力信号を増幅して出力する。この積
分器8の出力は、PGA(Programable
Gain Amplifier)11によって出力レ
ベルが調整された後、ADC(AnalogDigit
al Converter)12によってディジタル
データに変換され、断層像を再構成する画像処理装置1
3に送られる。The integrator 8 amplifies the input signal with an amplification factor determined by the capacitance of the integrating capacitor 7 and outputs the amplified signal. The output of this integrator 8 is a PGA (Programmable
After the output level is adjusted by the Gain Amplifier) 11, the ADC (Analog Digit)
an image processing device 1 which converts the data into digital data by an al Converter 12 and reconstructs a tomographic image;
Sent to 3.
【0006】なお、9は積分器8のリセットスイッチ、
10は電流制限抵抗である。リセットスイッチ9は、前
記スイッチ5がONされ、それによる出力が積分器8を
介してADC12に与えられてA/D変換される毎にO
Nされ、積分器8をリセットする。Note that 9 is a reset switch for the integrator 8;
10 is a current limiting resistor. The reset switch 9 turns on the output every time the switch 5 is turned on and the resulting output is given to the ADC 12 via the integrator 8 and A/D converted.
N and resets the integrator 8.
【0007】[0007]
【発明が解決しようとする課題】上記従来技術は、以下
のような問題点があった。すなわち上記従来技術では、
積分器8の出力Vは、コンデンサ4から送られてくる電
荷をQ、積分コンデンサ7の容量をCとすると、V=Q
/Cで表わせる値をとる。この積分器8は、出力範囲が
オペアンプ6の出力電圧で制限されるため、被検体2が
存在せずX線源1及び検出器3相互間に空気しかなく、
検出器3からの出力が最大のときに、オペアンプ6の最
大電圧以内に収まるよう、容量Cの値を定めなければな
らない。[Problems to be Solved by the Invention] The above-mentioned prior art has the following problems. That is, in the above conventional technology,
The output V of the integrator 8 is expressed as V=Q, where Q is the charge sent from the capacitor 4 and C is the capacitance of the integrating capacitor 7.
Takes a value expressed as /C. Since the output range of this integrator 8 is limited by the output voltage of the operational amplifier 6, the object 2 is not present and there is only air between the X-ray source 1 and the detector 3.
The value of the capacitance C must be determined so that the output from the detector 3 is within the maximum voltage of the operational amplifier 6 when it is at its maximum.
【0008】しかし、このように定めたコンデンサ7の
容量Cでは、実際に被検体2の腹部などを透過したとき
のX線による検出器3からの出力は格段に小さくなる。
そこで、積分器8の出力をADC12へ送る前にPGA
9で増幅し、量子化誤差を最小限に抑えるようにしてい
るが、これによると、検出器3の出力と共に、積分器8
で発生したノイズ成分まで増幅してしまい、測定精度が
低くなるという問題点があった。However, with the capacitance C of the capacitor 7 determined in this way, the output from the detector 3 due to the X-rays when actually passing through the abdomen of the subject 2 becomes much smaller. Therefore, before sending the output of the integrator 8 to the ADC 12,
9 to minimize the quantization error. According to this, along with the output of the detector 3, the integrator 8
There was a problem in that the noise components generated in the process were also amplified, resulting in lower measurement accuracy.
【0009】本発明の目的は、X線検出器出力信号が小
さいとき、積分器のノイズ成分を増加することなくX線
検出器出力信号成分のみを増幅でき、測定精度を向上す
ることのできるX線CT装置を提供することにある。An object of the present invention is to provide an X-ray detector that can amplify only the X-ray detector output signal component without increasing the noise component of the integrator when the X-ray detector output signal is small, and improve measurement accuracy. The purpose of the present invention is to provide a line CT device.
【0010】0010
【課題を解決するための手段】上記目的は、被検体から
の透過X線を検出するX線検出器とA/D変換器との間
に積分器を備えたX線CT装置において、前記積分器は
、それに備わる積分コンデンサの全容量を外部よりスイ
ッチ操作で複数段階に選択可能に、積分コンデンサ及び
スイッチの直列回路からなる増幅率切換回路を設けるこ
とにより達成される。[Means for Solving the Problems] The above object is to provide an X-ray CT apparatus equipped with an integrator between an X-ray detector for detecting transmitted X-rays from a subject and an A/D converter. This is achieved by providing an amplification factor switching circuit consisting of a series circuit of an integrating capacitor and a switch so that the total capacity of the integrating capacitor provided therein can be externally selected in a plurality of stages by operating a switch.
【0011】[0011]
【作用】積分器に設けられた増幅率切換回路は、積分コ
ンデンサ及びスイッチの直列回路からなり、積分器に備
わる積分コンデンサの全容量を外部より上記スイッチの
操作で複数段階に選択可能である。[Operation] The amplification factor switching circuit provided in the integrator consists of a series circuit of an integrating capacitor and a switch, and the total capacity of the integrating capacitor provided in the integrator can be externally selected in a plurality of stages by operating the switch.
【0012】いま、X線検出器の最大出力時の積分器前
段のコンデンサの蓄積電荷Qの値に応じて、積分器の出
力Vが、積分器のオペアンプの最大出力電圧を越えない
よう、最大の積分コンデンサ全容量Cの値(Cmax)
を決める。そしてこれが、前記増幅率切換回路のスイッ
チを何ら操作しない状態(スイッチON状態)で得られ
るように設定しておく。Now, depending on the value of the accumulated charge Q in the capacitor in front of the integrator at the maximum output of the X-ray detector, the maximum The value of the total capacitance C of the integrating capacitor (Cmax)
decide. The setting is made so that this can be obtained without any operation of the switch of the amplification factor switching circuit (switch ON state).
【0013】次に、通常計測での検出器出力時、ADC
の量子化誤差を抑えるため、積分器出力Vの増幅が必要
な場合は、前記増幅率切換回路のスイッチをOFFして
積分コンデンサの全容量Cの値を小さくする。これによ
り、積分器出力Vが大きくなる。例えば、Cの値を1/
2にすることにより、出力Vは2倍に、Cの値を1/4
にすることにより出力Vは4倍になる。Next, when the detector outputs in normal measurement, the ADC
If the integrator output V needs to be amplified in order to suppress the quantization error, the amplification factor switching circuit is turned off to reduce the total capacitance C of the integrating capacitor. This increases the integrator output V. For example, change the value of C to 1/
2, the output V is doubled and the value of C is reduced to 1/4.
By doing so, the output V is quadrupled.
【0014】このとき、積分器に起因するノイズ成分は
このCの値によらず一定なので、ノイズ成分に着目すれ
ば、積分器の出力Vをその後段回路(前記PGAなど)
で増幅したときに比べ、ノイズ成分は、検出器出力を2
倍に増幅したとき1/2、4倍に増幅したとき1/4と
小さくなり、測定精度が向上されることになる。At this time, the noise component caused by the integrator is constant regardless of the value of C, so if we focus on the noise component, the output V of the integrator can be transferred to the subsequent circuit (such as the above-mentioned PGA).
Compared to when amplified by
When it is amplified twice, it becomes 1/2, and when it is amplified four times, it becomes 1/4, and the measurement accuracy is improved.
【0015】また、Cの値を更に小さくして行くことに
より、微小出力(積分器前段のコンデンサの蓄積電荷Q
が微少)のときでも、その計測信号をノイズに埋れさせ
ることなく積分器から抽出でき、ダイナミックレンジも
拡大されることになる。Furthermore, by further decreasing the value of C, it is possible to reduce the minute output (accumulated charge Q of the capacitor before the integrator).
Even when the signal is small), the measurement signal can be extracted from the integrator without being buried in noise, and the dynamic range is also expanded.
【0016】[0016]
【実施例】以下、図面を参照して本発明の実施例を説明
する。図1は、本発明によるX線CT装置の一実施例の
要部を示す回路図である。この図1において、4〜7,
9,10,12,13は各々図2と同様である。8も図
2と同様に積分器を示すが、本発明では増幅率切換回路
21を備えてなる。Embodiments Hereinafter, embodiments of the present invention will be described with reference to the drawings. FIG. 1 is a circuit diagram showing a main part of an embodiment of an X-ray CT apparatus according to the present invention. In this Figure 1, 4 to 7,
9, 10, 12, and 13 are the same as in FIG. 2, respectively. 8 also represents an integrator as in FIG. 2, but in the present invention it is provided with an amplification factor switching circuit 21.
【0017】この増幅率切換回路21は、積分コンデン
サの全容量Cを外部よりスイッチ操作で複数段階に選択
可能に、積分コンデンサ22及びスイッチ23の直列回
路24からなる積分コンデンサ容量切換回路を構成して
なるものである。この場合、上記直列回路24は積分コ
ンデンサの全容量Cの所望切換段数に応じて1又はそれ
以上設けられる。図示例では2回路設けられ、積分コン
デンサ全容量Cを3段階に切換可能に、基本的な積分コ
ンデンサ7に並列に接続して構成されている。次に動作
について説明する。図1中、下側のスイッチ23をS1
、同上側のスイッチ23をS2、基本的な積分コンデン
サ7の容量をC1、スイッチS1に接続されたコンデン
サ22の容量をC2、スイッチS2に接続されたコンデ
ンサ22の容量をC3とする。また、C1=C2,C3
=2C1とする。This amplification factor switching circuit 21 constitutes an integrating capacitor capacity switching circuit consisting of a series circuit 24 of an integrating capacitor 22 and a switch 23, so that the total capacitance C of the integrating capacitor can be selected in a plurality of stages by operating a switch from the outside. That's what happens. In this case, one or more series circuits 24 are provided depending on the desired number of switching stages of the total capacitance C of the integrating capacitor. In the illustrated example, two circuits are provided, and are connected in parallel to the basic integrating capacitor 7 so that the total capacitance C of the integrating capacitor can be switched in three stages. Next, the operation will be explained. In FIG. 1, the lower switch 23 is set to S1.
, the upper switch 23 is S2, the capacitance of the basic integrating capacitor 7 is C1, the capacitance of the capacitor 22 connected to the switch S1 is C2, and the capacitance of the capacitor 22 connected to the switch S2 is C3. Also, C1=C2,C3
=2C1.
【0018】いま、被検体2が存在せず、X線源及びX
線検出器相互間に空気しかなく、X線検出器からの出力
が最大のときには、スイッチS1,S2を閉じておき、
積分器出力が飽和しないようにされる。[0018] Now, the subject 2 is not present, and the X-ray source and
When there is only air between the X-ray detectors and the output from the X-ray detector is at its maximum, switches S1 and S2 are closed.
The integrator output is prevented from saturating.
【0019】次に、X線源及びX線検出器相互間にX線
吸収の大きい被検体が存在した場合、積分器出力の増幅
が必要となるが、この時、スイッチS2をOFFするこ
とにより、積分コンデンサの全容量CはそれまでのC1
+C2+C3=4C1から、C1+C2=2C1となる
。したがって、V=Q/Cより、積分器8の出力Vは2
倍となり、積分器8のノイズ成分を増加させることなく
、ADC12によるA/D変換時の量子化誤差を減少で
きる。[0019] Next, when there is a subject with high X-ray absorption between the X-ray source and the X-ray detector, it is necessary to amplify the integrator output. , the total capacitance C of the integrating capacitor is C1
Since +C2+C3=4C1, C1+C2=2C1. Therefore, from V=Q/C, the output V of the integrator 8 is 2
Therefore, the quantization error during A/D conversion by the ADC 12 can be reduced without increasing the noise component of the integrator 8.
【0020】更にX線検出器の出力が小さいときは、ス
イッチS2に加えてスイッチS3をもOFFすることに
より、積分コンデンサの全容量はC1となり、初期状態
に比べて4倍の出力が積分器8から得られる。Furthermore, when the output of the X-ray detector is small, by turning off switch S3 in addition to switch S2, the total capacitance of the integrating capacitor becomes C1, and the output of the integrator is four times that of the initial state. Obtained from 8.
【0021】積分器8からの出力はADC12によって
ディジタルデータに変換され、断層像を再構成する画像
処理装置13に送られるが、本発明では、X線検出器の
出力の大きさに応じて積分器8の増幅率を変更している
ので、画像処理装置13に送られるまでの間に、上記変
更に応じて信号の大きさが修正される。The output from the integrator 8 is converted into digital data by the ADC 12 and sent to the image processing device 13 that reconstructs the tomographic image. Since the amplification factor of the signal generator 8 is changed, the magnitude of the signal is modified in accordance with the change before being sent to the image processing device 13.
【0022】なお、スイッチS1,S2のON,OFF
選択操作は、操作者が被検体をみて手動で行うように構
成してもよく、あるいは操作者が設定した撮影条件、例
えば管電流設定値などに応じて制御回路(図示せず)に
より自動的に行われるように構成してもよい。[0022] Note that the ON/OFF of switches S1 and S2
The selection operation may be configured to be performed manually by the operator while looking at the subject, or may be performed automatically by a control circuit (not shown) according to the imaging conditions set by the operator, such as the tube current setting value. It may also be configured so that it is carried out separately.
【0023】[0023]
【発明の効果】以上説明したように本発明によれば、X
線検出器出力の大きさに応じて最適な積分器出力が得ら
れ、しかも、X線検出器出力が小さく、これを増幅する
場合、積分器に起因するノイズを増幅することなく、X
線検出器出力信号のみを増幅できるため、高ダイナミッ
クレンジで、測定精度の高いX線CT装置を提供するこ
とができるという効果がある。[Effects of the Invention] As explained above, according to the present invention,
The optimal integrator output can be obtained depending on the magnitude of the X-ray detector output.Moreover, when the X-ray detector output is small and it is amplified, the X-ray detector output can be obtained without amplifying the noise caused by the integrator.
Since only the radiation detector output signal can be amplified, it is possible to provide an X-ray CT apparatus with a high dynamic range and high measurement accuracy.
【図1】本発明装置の一実施例の要部を示す回路図であ
る。FIG. 1 is a circuit diagram showing a main part of an embodiment of the device of the present invention.
【図2】従来装置の概略構成を示す回路図である。FIG. 2 is a circuit diagram showing a schematic configuration of a conventional device.
3 X線検出器 4 コンデンサ 5 スイッチ 6 オペアンプ 7 積分コンデンサ 8 積分器 12 ADC 13 画像処理装置 21 増幅率切換回路 22 積分コンデンサ 23 スイッチ 24 直列回路 3. X-ray detector 4 Capacitor 5 Switch 6 Operational amplifier 7 Integrating capacitor 8 Integrator 12 ADC 13 Image processing device 21 Amplification factor switching circuit 22 Integrating capacitor 23 Switch 24 Series circuit
Claims (1)
検出器とA/D変換器との間に積分器を備えたX線CT
装置において、前記積分器は、それに備わる積分コンデ
ンサの全容量を外部よりスイッチ操作で複数段階に選択
可能に、積分コンデンサ及びスイッチの直列回路からな
る増幅率切換回路を具備することを特徴とするX線CT
装置。Claim 1: An X-ray CT equipped with an integrator between an X-ray detector that detects transmitted X-rays from a subject and an A/D converter.
In the device, the integrator is equipped with an amplification factor switching circuit consisting of a series circuit of an integrating capacitor and a switch so that the total capacity of the integrating capacitor provided therein can be selected in multiple stages by operating a switch from the outside. line CT
Device.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP3057066A JPH04292145A (en) | 1991-03-20 | 1991-03-20 | X-ray ct device |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP3057066A JPH04292145A (en) | 1991-03-20 | 1991-03-20 | X-ray ct device |
Publications (1)
Publication Number | Publication Date |
---|---|
JPH04292145A true JPH04292145A (en) | 1992-10-16 |
Family
ID=13045076
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP3057066A Pending JPH04292145A (en) | 1991-03-20 | 1991-03-20 | X-ray ct device |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPH04292145A (en) |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2001190543A (en) * | 2000-01-13 | 2001-07-17 | Ge Yokogawa Medical Systems Ltd | Method for detecting x-ray beam quantity and x-ray ct apparatus |
JP2015158501A (en) * | 2009-03-26 | 2015-09-03 | コーニンクレッカ フィリップス エヌ ヴェ | data acquisition |
JP2016178432A (en) * | 2015-03-19 | 2016-10-06 | 株式会社東芝 | Integrated circuit, photon detection device and radiation analyzer |
-
1991
- 1991-03-20 JP JP3057066A patent/JPH04292145A/en active Pending
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2001190543A (en) * | 2000-01-13 | 2001-07-17 | Ge Yokogawa Medical Systems Ltd | Method for detecting x-ray beam quantity and x-ray ct apparatus |
JP4597299B2 (en) * | 2000-01-13 | 2010-12-15 | Geヘルスケア・ジャパン株式会社 | X-ray beam amount detection method and X-ray CT apparatus |
JP2015158501A (en) * | 2009-03-26 | 2015-09-03 | コーニンクレッカ フィリップス エヌ ヴェ | data acquisition |
JP2016178432A (en) * | 2015-03-19 | 2016-10-06 | 株式会社東芝 | Integrated circuit, photon detection device and radiation analyzer |
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