Tomografi keselarasan optik: Perbedaan antara revisi
Konten dihapus Konten ditambahkan
k Bot: Menambahkan tag <references /> yang hilang |
Tidak ada ringkasan suntingan |
||
| (11 revisi perantara oleh 6 pengguna tidak ditampilkan) | |||
Baris 1:
{{Infobox interventions|Name=
|OPS301={{OPS301|3-300}}
}}
'''
Tergantung pada sifat dari sumber cahaya (
== Pendahuluan ==
[[Berkas:HautFingerspitzeOCT.gif|jmpl|218x218px|Optical coherence tomogram dari ujung jari.
Mulai dari cahaya putih interferometri untuk ''in vivo'' okular mata pengukuran pencitraan dari jaringan biologis, terutama dari mata manusia, diselidiki oleh beberapa kelompok di seluruh dunia. Pertama dua dimensi ''di vivo'' penggambaran
OCT juga telah digunakan untuk berbagai proyek pelestarian barang seni, di mana ia digunakan untuk menganalisis lapisan yang berbeda dalam sebuah lukisan. OCT telah menarik keuntungan lain dari sistem pencitraan medis.
<!--
Baris 37:
OCT delivers high resolution because it is based on light, rather than sound or radio frequency. An optical beam is directed at the tissue, and a small portion of this light that reflects from sub-surface features is collected. Note that most light is not reflected but, rather, scatters off at large angles. In conventional imaging, this diffusely scattered light contributes background that obscures an image. However, in OCT, a technique called interferometry is used to record the optical path length of received photons allowing rejection of most photons that scatter multiple times before detection. Thus OCT can build up clear 3D images of thick samples by rejecting background signal while collecting light directly reflected from surfaces of interest.
Within the range of noninvasive three-dimensional imaging techniques that have been introduced to the medical research community, OCT as an echo technique is similar to [[ultrasound imaging]]. Other medical imaging techniques such as computerized axial tomography, magnetic resonance imaging, or positron emission tomography do not use the echo-location principle.
The technique is limited to imaging 1 to 2 mm below the surface in biological tissue, because at greater depths the proportion of light that escapes without scattering is too small to be detected. No special preparation of a biological specimen is required, and images can be obtained ‘non-contact’ or through a transparent window or membrane. It is also important to note that the laser output from the instruments is low – eye-safe near-infra-red light is used – and no damage to the sample is therefore likely.
Baris 44:
The principle of OCT is white light or low coherence interferometry. The optical setup typically consists of an interferometer (Fig. 1, typically [[Michelson interferometer|Michelson]] type) with a low coherence, broad bandwidth light source. Light is split into and recombined from reference and sample arm, respectively.
-->
{|
[[Berkas:OCT B-Scan Setup.GIF|jmpl|375px|Fig. 2 Typical optical setup of single point OCT. Scanning the light beam on the sample enables non-invasive cross-sectional imaging up to 3 mm in depth with micrometer resolution.]]
Baris 84 ⟶ 85:
|}
where <math> \lambda_0 </math> and <math> \Delta\lambda</math> are respectively the central wavelength and the spectral width of the light source -->.<ref name="hasilan otomatis1">{{cite book| title= Anterior & Posterior Segment OCT: Current Technology & Future Applications, 1st edition |year=2014|last1=Garg|first1=A. }}</ref>
<!--
===Frequency domain===
Baris 91 ⟶ 92:
====Spatially encoded====
Spatially encoded frequency domain OCT (SEFD-OCT, spectral domain or Fourier domain OCT) extracts spectral information by distributing different optical frequencies onto a detector stripe (line-array CCD or CMOS) via a dispersive element (see Fig. 4). Thereby the information of the full depth scan can be acquired within a single exposure. However, the large signal to noise advantage of FD-OCT is reduced due to the lower dynamic range of stripe detectors with respect to single photosensitive diodes, resulting in an SNR ([[signal to noise ratio]]) advantage of ~10 [[decibel|dB]] at much higher speeds. This is not much of a problem when working at 1300 nm, however, since dynamic range is not a serious problem at this wavelength range.
The drawbacks of this technology are found in a strong fall-off of the SNR, which is proportional to the distance from the zero delay and a sinc-type reduction of the depth dependent sensitivity because of limited detection linewidth. (One pixel detects a quasi-rectangular portion of an optical frequency range instead of a single frequency, the Fourier-transform leads to the sinc(z) behavior). Additionally the dispersive elements in the spectroscopic detector usually do not distribute the light equally spaced in frequency on the detector, but mostly have an inverse dependence. Therefore, the signal has to be resampled before processing, which can not take care of the difference in local (pixelwise) bandwidth, which results in further reduction of the signal quality. However, the fall-off is not a serious problem with the development of new generation CCD or photodiode array with a larger number of pixels.
Baris 148 ⟶ 149:
{{reflist}}
{{Authority control}}
[[Kategori:Peralatan medis]]
| |||